TW588158B - Systems and methods for providing information concerning chromophores in physiological media - Google Patents

Abstract

The present invention generally relates to systems and methods for providing information about chromophores in physiological media. More particularly, the invention relates to non-invasive systems and methods for determining absolute values of oxygenated and/or deoxygenated hemoglobins and their ratios in a physiological medium. The system in a preferred embodiment generally includes a portable probe having a source module for irradiating into the medium electromagnetic radiation, a detector module detecting radiation from a target area in the medium, and a processing module determining the absolute values of the chromophore concentrations and their ratios thereof based on input and output parameters of the source and detector modules. In one aspect, the invention provides a solution for unknown parameters of the chromophores in a medium using a novel processing algorithm. In another aspect, the invention concerns a portable unit for performing the requisite measurements, which unit includes a movable member having one or more radiation sources and one or more radiation detectors, and an actuator designed to cause the member to move along predetermined curvilinear paths. Properties of the chromophores are measured for individual voxels defined along each motion path, and/or cross-voxels defined at the intersection of voxels along different motion paths. These measured values are then used in a preferred embodiment to generate two- or three-dimensional images of the distribution of chromophores or their properties. In other aspects, the invention includes various patterns for the optimal distribution of sources and detectors for the optical probe, and self-calibrating operation of the probe substantially in real-time.

Description

588158

Scope of the invention The present invention is generally related to the following systems and methods: (i) providing negative information about chromophores or their properties in space and / or time distribution in various physiological media 'and / or (ii) determining various The various properties of different physiological media are absolutely rampant, such as the concentration of oxygen and deoxyhemoglobin (and their ratios). More specifically, the present invention relates to a non-invasive self-calibrating optical imaging system, an optical probe with a movable sensor component, and a real-time image structure algorithm and method. The sensor assembly includes symmetrically configured optical sensors, such as a wave source and / or a detector. The present invention can be applied to optical imaging systems and / or optical probes that operate according to a wave equation, such as the Beer · Lambert equation, the modified Beer-Lambert equation, the photon diffusion equation, and their correlations. The present invention also relates to a device and method for obtaining the above-mentioned absolute chirp by solving the aforementioned waveform equation. BACKGROUND OF THE INVENTION Mathematical basis Near-infrared spectroscopy has been used for non-invasive measurement of various physiological properties in animals and humans. The basic principle in near-infrared spectroscopy is, for example, a physiological medium for tissues, and cells include a variety of light-absorbing and / or light-expanding chromophores that can interact with the electromagnetic waves transmitted and traveled by them. Physiological tissues include various highly diffuse chromophores of near-infrared waves with relatively low absorption. Many substances in a physiological medium can interact or interfere with the transmitted near-infrared light waves. For example, human tissues and cells include many chromophores such as water, cytochromes, lipids, etc. Deoxy and oxyhemoglobin are the most dominant chromophores in the 600 nm to 900 nm spectral range. So nearly

V 588158 A7 B7 V. Description of the invention (2) The infrared spectroscope can be used to measure the oxygen level of physiological media from the viewpoint of tissue hemoglobin oxygen saturation (hereinafter referred to as "oxygen saturation"). Near-infrared spectroscopy and diffusion optical images have been published in Adv. Exp. Med. Biol. Vol. 220, pp. 135-144 in 1987, published by Neuman, MR under the name " Pulse Oximetry: Physical Principles, Technical Realization and Present Limitations " And was discussed in 1993 by Scan. J Clin. And Lab. Investigations, Volume 53, pages 105-111 under the name `` History and Recent Developments in Pulse Oximetry ". Various technologies related to near infrared spectroscopy have been developed, such as time-determined spectroscopy (TRS), phase modulation spectroscopy (PMS), and continuous wave spectroscopy (CWS).

TRS TRS technology is based on operating principles such as pulse time measurement and pulse code modulation. In particular, it measures a delay time between the entry and departure of electromagnetic waves back and forth from the physiological media. Typically, TRS applies an electromagnetic wave pulsation or pulse sequence with a duration of a few picoseconds to the media. Photons can encode not only tissue characteristics in the timing of the delayed pulses received by a detector, but also tissue characteristics in the time profile of the received intensity. Therefore, the returned signal is spread across the bees, rather than a "pure" copy of the received transmission pulse, and the amplitude can be significantly reduced. Therefore, TRS can measure the strength of the returned signal over a limited time period, and the The finite time period is long enough to detect the entire portion of the delayed return signal. Depending on the input pulse or pulse shape change and amplitude reduction, the different time and average time delay of the photon arrival between the light (or wave) source and the detector can be returned, for example, by a letter-5-This paper is for China National Standard (CNS) A4 (210X297 mm) 588158 A7 _B7______ V. The unwinding of invention note (3) is used to obtain tissue absorption and tissue distribution. Information on traversing tissues (such as optical path lengths and their variations) is then available. The details of the TRS technique are, for example, in DA Boas et al., Proc. ., Vol. 158, p. 3631 (1996); and J. Sipior et al., Rev. Sci. Instnxm., Vol. 68, p. 2666 (1997), which are listed here for reference only . ·

PMS PMS technology uses phase-modulated electromagnetic waves irradiated through a wave source and transmitted through a physiological medium. Typical examples of PMS include homodyne systems, heterodyne systems, single-ended band systems, and other systems and phase correction algorithms based on transmitter-receiver cross coupling. Like TRS, the PMS system monitors the strength of the attenuated electromagnetic waves. In addition, PMS systems are required to measure frequency domain parameters, such as phase shifts of electromagnetic waves that are independent of wave intensity. Based on the time domain and frequency domain information, the PMS system can determine the spectrum of the absorption coefficient and / or dispersion coefficient of the chromophore in the media, and calculate the absolute chirp of the heme concentration. Details of the PMS technique are provided, for example, in US Patent No. 5,820,558 and B. Chance et al. In the technical literature of Rev. Sci. Instmm, Vol. 69, p. 3457 (1998), which is listed here for reference only.

In contrast to CWS, the CWS system uses non-pulsating and non-pulsing modulated electromagnetic waves. That is, the CWS system can be applied to media electromagnetic waves with substantially at least the same amplitude over the measured time period. On the detection side, the CWS system only measures the intensity of the irradiated and detected electromagnetic waves, and does not evaluate any frequency domain parameters. -6- This paper size applies to China National Standards (CNS) A4 specifications (210 X 297 mm) 588158 A7 B7 V. Description of invention (4) In homogeneous, semi-infinite models, TRS and PMS can usually The photon diffusion equation is used to obtain a spectrum of absorption coefficients and reduced dispersion coefficients of physiological media, and oxygen and deoxyhemoglobin concentrations and tissue oxygen saturation. Conversely, CWS is often used to solve the modified Beer-Lambert equation and to calculate the relative magnitude of changes in oxygen and deoxyhemoglobin concentrations. Although they can provide erythropoietin concentration and oxygen saturation capacity, the main disadvantage of TRS and PMS is that the equipment must be bulky and ST is expensive. For example, TRS equipment requires a pulse generator and detector, and PMS requires additional hardware. And signal processing capabilities to determine frequency domain parameters. CWS can be manufactured at a lower cost because all it needs to do is to perform intensity measurement, but its utility is usually limited. It can only evaluate changes in the concentration of erythropoietin, but it cannot evaluate its absolute 値, nor can it evaluate Oxygen saturation in tissues with varying concentrations. Therefore, CWS cannot provide oxygen saturation. Prior art techniques also required calibration of optical probes by, for example, measuring the baseline in a homogeneous area of a reference medium or a test subject medium. In addition, all prior art techniques required sophisticated image reconstruction algorithms to produce chromophore-like second or third degree distribution images. Therefore, there is a need for an optical imaging system that can be more efficient, reliable, miniaturized, and relatively inexpensive. It can be self-calibrated without relying on external measurements or data, and can be combined with more effective image construction algorithms. Provide second-degree and / or three-dimensional images of the chromophore and / or its property distribution on a substantially instant basis. In addition, there is a need for an absolute probe that the optical probe can measure the chromophore and / or its properties, and a larger target area that can be devoid of body in a single measurement. For measuring the hemoglobin concentration and absolute oxygen saturation of physiological media. This paper size applies the Chinese National Standard (CNS) A4 specification (210X 297 mm).

Line 588158 A7

Lambert equations, modified Beer-Lambert equations, photon diffusion equations, and their associated waveform equations for optical imaging systems and / or optical probes. The present invention also relates to a device and method for obtaining the above-mentioned absolute chirp by solving the aforementioned waveform equation. A new CWS system and method are needed. The present invention is generally related to the following systems and methods: (1) providing information about chromophores or their properties in space and / or time t in different physiological media, and / or (ii) determining the Absolute properties of various binary properties, such as the concentration of oxygen and deoxyhemoglobin (and their ratios): More specifically, the present invention relates to non-invasive self-calibrating optical imaging systems, and Probe and real-time image structure algorithms and methods. The present invention can be applied to operations based on, for example, Bee. In an aspect of the present invention 'a system can determine the chromophore concentration of a physiological medium. The system may include a wave source module for irradiating at least two sets of electromagnetic radiation with different wave characteristics to the medium; a detector module for detecting electromagnetic radiation transmitted through the medium; and a processing Module for determining the absolute radon from one of the chromophore concentrations of electromagnetic radiation irradiated by the wave source module and detected by the detector module, where the decision is based on the continuous wave from the wave source module _ Intensity measurement of electromagnetic radiation. The invention also provides the system with the ability to generate images representing the distribution of one or more chromophores and their properties in a target area of a physiological media. This system includes an optical probe with at least one wave source and at least one waveform detector. The configuration of the wave source can irradiate electromagnetic radiation to a first target of physiological media. The paper size is applicable to China National Standard (CNS) A4 Specifications (210X 297 mm)

Order

Line A7

And the configuration of the waveform detector can detect the electromagnetic light emission from the first target area of the media and generate a first output in response to the electromagnetic radiation. The system also includes a signal analyzer configured to receive and sample the first output signal to obtain a plurality of amplitude chirps. The analysis of such amplitude chirps may determine at least one set of samples of the first output signal having substantially similar amplitudes. The system may further include a signal processor configured to calculate a first baseline from the first output, where the first baseline is representative of a similar amplitude substantially determined by the analyzer. The signal processor may also provide a self-calibrated first output signal by processing the first output signal and its first baseline, where the first baseline 疋 represents an amplitude similar to the amplitude. The invention also provides a method for determining the chromophore concentration of a physiological medium. In another aspect of the present invention, a system can provide information on red blood cells and their property distribution in a target area of a physiological medium. This system includes a movable component having at least one wave source and at least one waveform detector. The configuration of the at least one wave source can irradiate near-infrared electromagnetic radiation to the target area, and the configuration of at least one waveform detector can detect the target The near-infrared light emission of the area, and an output signal is generated in response thereto. The system further includes an exciter. The gray exciter is turned with at least one movable component, which can move the movable component along the target area along at least one curved path; and a processor, which can be moved along the path according to the transmission. The output signal from at least one wave detector of at least one curved path determines the distribution of chromophores or properties. In another aspect of the present invention, a target area for a physiological medium is provided.

588158 A7 B7 V. Description of the invention The system providing information about chromophore and property distribution includes an optical probe with a wave source and a waveform detector. The configuration of the wave source can illuminate near-infrared electromagnetic light. A first target area of physiological media, and the configuration of the waveform detector can detect the near-infrared radiation from the media and generate a first output signal in response to it. The system further includes an analyzer for receiving and Sampling the first output signal to obtain a plurality of amplitudes. Analysis of the amplitudes may determine at least one set of samples having substantially similar first output numbers of amplitude. The system may further include a signal processor, the configuration of which may be The output signal calculates a first baseline, where the first baseline represents a similar amplitude substantially determined by the analyzer. The signal processor can also provide a self-calibrated first output signal by processing the first output signal and its first baseline. In still another aspect of the present invention, the provided method is obtainable from an optical imaging system having an optical probe. A calibrated output signal. The method has at least one wave source configured to irradiate near-infrared electromagnetic radiation to a target area of a physiological medium, and at least one waveform detector that can be generated in response to generating the detected near-infrared electromagnetic radiation. Output signal. Another aspect of the present invention includes an optical probe that can produce an image representing the distribution of erythroglobin or its properties in a target area of a physiological media. The optical probe includes a plurality of wave sources and waveform-detection The configuration of these wave sources can irradiate near-infrared electromagnetic radiation to the media, and the configuration of the waveform detector can detect near-infrared electromagnetic radiation and generate an output signal in response to this detection. ^ Specific embodiments of the invention include One or more of the following characteristics: -10- This paper size applies to China National Standard (CNS) A4 (210 X 297 mm)

Binding

Line 588158

The plurality of symmetrically arranged physical scanning units each have a first wave source, a second wave source, a first waveform detector, and a second waveform detector. The configuration of the first wave source is closer to the first waveform detector than the second waveform detector. The configuration of the second wave source is closer to the second waveform detector than the first waveform detector. The first proximity distance between the first wave source and the first waveform detector is substantially similar to the second proximity distance between the second wave source and the second waveform detector. The first long distance between the first wave source and the second waveform detector is substantially similar to the second long distance between the second wave source and the first waveform detector. The first and second wave sources are configured to generate an output signal in response to detection of near-infrared electromagnetic radiation irradiated by at least one of the first and second wave sources. The output k is the interaction between near-infrared electromagnetic radiation and erythropoietin that is not in the target area of the media. Order

In an additional embodiment, the optical probe includes 4 symmetrical scanning units', wherein a first scanning unit is the same as a fourth scanning unit, and a second scanning unit is the same as a third scanning unit. Each scanning unit has a first wave source, a second wave source, a first waveform detector, and a second waveform detector. The configuration of the first and second wave sources can be synchronized with the first and second waveform detectors to generate an output signal indicative of the interaction between the near-infrared electromagnetic radiation and the hemagglutinin in the media target area. In an additional specific embodiment, the optical probe includes at least a first wave source and at least a first waveform detector defining a first scanning element, and at least a second wave source and at least a second waveform detector A second scanning element is defined. The first and second scanning elements define a scanning unit, wherein the first and second wave sources are symmetrically matched with one of a symmetrical line and a symmetrical point. -11-

588158 A7 B7 V. Description of the invention (9). In each of the scanning elements, the first and second waveform detectors are also arranged symmetrically with respect to a line of symmetry and a point of symmetry. The present invention also includes a method of generating a two-dimensional or three-dimensional image of a target area of a physiological medium through an optical imaging system having an optical probe. These images represent the spatial or temporal distribution of erythroglobin or its properties in the media. The optical probe includes a plurality of wave sources and a plurality of waveform detectors. The configuration of these wave sources can irradiate near-infrared electromagnetic radiation to the media, and the configuration of the waveform detector can generate output in response to the detection of near-infrared electromagnetic radiation signal. The method includes the steps of providing a plurality of scanning elements, each of which includes at least two of the child scanning elements, and scanning the target area using one or more scanning units. The method further includes the steps of: aggregating the output signals generated by each of the scanning elements, and obtaining a set of waveform equation solutions for the input and output parameters of the scanning unit. The method further comprises the steps of: deciding the distribution of at least one of erythroglobin and its properties from the solved group, and providing one or more images of the distribution. In another aspect of the present invention, a system for generating an image representing one or more erythropoietin properties in a target area of a physiological media includes at least two T-movement supports coupled to an exciter, and the configuration can be along the At least; _ curved paths and support moves with the target area. The system further includes one or more wave sources and one or more waveform detectors mounted on the support to form a scanning unit with a vertical axis matching, a scanning area, and a scanning volume. These wave source configurations can irradiate near-infrared electromagnetic radiation to the target area of the media, and the configuration of the waveform detector can detect from the target ____ -12- This paper is suitable for standard SCN Standard (CNS) A4 ( 2l〇x 297 public love)

The near-infrared electromagnetic radiation of the target area and an output signal are generated in response to the detection. The system further includes a processor for receiving an output signal and a plurality of voxels defined in the target area. Plural individual vowels have a characteristic size and an integral prime axis. The processor can determine the color development properties and generate images based on the output signals of the plurality of voxels. In an additional embodiment of the present invention, a system for generating an image representing the distribution of at least one hemoglobin property in a physiological media target region includes a sensor component having at least one wave source and at least one waveform detector. The system further includes a processor for receiving an output signal from the sensor component, and the processor is configured with a plurality of voxels defined in the target area. To determine the properties of red blood cells, the processor can solve a plurality of waveform equations applied to the input radiation from at least one wave source and the radiation detected by at least one detector. The processor may further generate an image of the hematocrit-based distribution in the target area. An additional specific embodiment of the present invention includes a system for generating at least one property distribution image representing at least one chromophore in a physiological target region, wherein the system includes at least one wave source, at least one waveform detector, and has: A portable probe with at least one movable component and at least one actuator. The at least one movable component has a primary wave source and at least one detector, and the at least one actuator element is configured to be coupled to the at least one movable component so as to move it along one or more curved paths. Another aspect of the present invention is a system for generating information on at least one property distribution of at least one chromophore in a physiological target area including at least one wave source, at least one waveform detector, and at least one movable component: optical

11. The at least one wave source and a waveform detector are arranged therein. The system can be further G. A monitor coupled with a human optical probe, and includes a processor for accessing the number K. The system may further include an actuator configured to be coupled to the movable component so as to move it along at least one curved path; and a connector for at least one of the optical probe, the monitor, and the actuator element. At least one of electrical communication, optical communication, power transmission, mechanical force transmission, and data transmission is provided between the two. Additional specific embodiments include using a system to generate a target area related to a physiological medium m. The at least one property distribution information of at least one chromophore in the system includes a processor, at least two wave sources, and at least two wave detection devices. At least two of the child wave sources and at least two of the waveform detectors are arranged substantially along a line. Another aspect of the present invention includes a method for generating an image representing the distribution of red blood cells through a portable measurement system in a physiological target area. The system includes a movable component having at least one wave source and at least one waveform detector to define a scanning unit having a vertical axis. A scanning area is smaller than a target area and a scanning volume. The at least one wave source can direct near-infrared electromagnetic radiation. When the target area is irradiated, the configuration of the at least one waveform detector can detect radon infrared electromagnetic radiation in the target area, which generates an output signal in response to the target area. The system further includes an exciter element coupled to the movable component. So as to move it along at least one curved path to scan the target area. The method includes the following steps: placing a movable component on a target area of the media 'and positioning the imaging element in a first area of the target. The method further includes scanning the target by irradiating near-infrared electromagnetic radiation. Zhang scale is applicable to China National Standard (CNS) A4 specification (210X297 mm) 588158

A7 B7 5. Description of the Invention (12) The first area of the area, and the output signal is obtained through the waveform detector. The method may further include the steps of processing the exciter element to move the movable component, and the scanning unit may follow a curved path from the first region toward another region of the target region. The method further includes the steps of defining a first set of voxels from the output signal in at least one of the regions of the target region, and determining a voxel 値 corresponding to the group of voxels, each voxel 値 being The properties on Integrins are average. The method further comprises the step of generating, from the first set of voxels, a representation of the red blood cell distribution images. An additional aspect of the present invention includes a method for generating at least one property distribution image representing at least one chromophore through a portable system in a target area of a physiological medium. The system includes at least one wave source configured to irradiate electromagnetic radiation to the medium; and at least one waveform detector configured to detect electromagnetic radiation and generate an output signal in response thereto. The method includes the following steps: positioning a wave source and a detector in the target area, defining a second set of voxels from the output signals, determining a series of voxels 该等 of the second voxels, and constructing a definition as A second group of intersecting voxels of the at least two intersecting voxels, which belong to one of the first and second groups of voxels, respectively. The method further includes the following steps: calculating the intersecting voxels 第一 of the first group of intersecting voxels from the voxels 値 of the intersecting voxels; and generating a chromophore property distribution image from the first intersecting voxels 第一 of the first sequence. An additional aspect of the present invention includes a method for generating an image of at least one property distribution representing at least one chromophore through a measurement system in a target area of a physiological medium. The system includes at least one wave source and at least one waveform. -15- This paper size applies to China National Standard (CNS) A4 specification (210 X 297 mm)

Order

Line 588158 A7 B7 V. Description of the invention (13) Detector, a movable assembly, and an actuator element. The configuration of the movable component includes one of the wave source and the detector, and an exciter element with the movable component. The configuration of the wave source and the detector can form a movable scanning unit, which includes a vertical axis for connecting the wave source and the detector, and defines at least one of a scanning area and a scanning volume. The configuration of the exciter element can cause at least one movement of at least one of the movable component and the scanning unit along at least one curved path. The method includes the following steps: placing a movable component on a target area of the media, 'positioning the scanning unit in a first area of the target area, and processing the exciter element to follow a first curved path from the target A first area of the area to a second area generates a first movement of one of the movable component and the scanning unit. The method further includes the steps of defining a first group of first voxels from the output signals in at least a portion of the target region, determining a first sequence of first voxels 値 of the first voxels' Each first voxel 値 represents a first average 値 of the property averaged over the first voxel. The method further includes the steps of defining a second set of second voxels from the output signals in at least a portion of the target region, and determining a second set of second voxels 値 of the second voxels. Sequence, each second voxel 値 represents the average value of the property ¥ —the second average 値 on the second voxel. The method further comprises the steps of constructing a set of intersected voxels, each of which is at least two intersected bodies defined as one of the first and second groups belonging to the first and second voxels, respectively. Intersecting one of the primes. The method further comprises calculating a series of intersecting voxels 値 of the intersecting voxels 来自 directly from the intersecting voxels 値, and generating the property -16- directly from the intersecting voxels 该 of the sequence. This paper size applies to China National Standard (CNS) A4 (210 X 297 mm)

Order

Line 588158 A7

The images of the distribution. Other features and advantages of the present invention will be apparent from the following detailed description and the scope of patent applications. Brief description of the drawings FIG. 1 is a diagram of an optical imaging system according to the present invention; FIG. 2A is an optical probe diagram of an optical imaging system defining a multiple scanning unit according to the present invention, and FIG. 2B is according to the present invention An optical probe diagram of an optical imaging system defining multiple scanning units having a wave source-detector configuration opposite to that of FIG. 2A. FIG. 3A is a diagram of a sampling optical system with two wave sources and two waveform detectors having the same near and long distances according to the present invention; FIG. 3B is a diagram of another sampling optical system according to the present invention, which has a short distance and Long-distance two-wave source and two-waveform detector; FIG. 3C is still another sampling optical system diagram according to the present invention, which has two-wave source and two-waveform detector; FIG. 4 is a cross-section of a scanning unit according to the present invention Top view. 5 is a cross-sectional top view of another scanning unit according to the present invention. FIG. 6A is a linear scanning unit diagram according to the present invention; FIG. 6B is another linear scanning unit diagram having a wave source_detector configuration opposite to FIG. 6A according to the present invention; FIG. 6C is a diagram of a linear scanning unit according to the present invention; Figure of a square scanning unit; Figure 6D is another square scanning unit with a wave source · detector configuration opposite to that of Figure 6C according to the present invention; ____ -17 · This paper size applies to China National Standard (CNS) A4 specifications ( 210X297 public address) 588158 A7 B7 V. Description of the invention (15) Figure 6E is a rectangular scanning unit according to the present invention; Figure 6F is a trapezoidal scanning unit according to the present invention; and Figure 6G is according to the present invention. 6F is another trapezoidal scanning unit diagram of an opposite wave source-detector configuration; FIG. 6H is another trapezoidal scanning unit diagram having an opposite wave source-detector configuration according to the present invention; and FIG. 7A is a diagram according to the present invention Fig. 7B is a diagram of a rectangular scanning unit according to the present invention; Fig. 7C is a diagram of a parallelogram scanning unit according to the present invention; and Fig. 8A is a first group of optics according to Fig. 2A of the present invention Explore Scanning unit diagram; FIG. 8B is a voxel and intersected voxel generated by the scanning unit of FIG. 8A, and the resulting voxel and intersected voxel diagrams according to the present invention; FIG. 9A is a diagram of FIG. 2A A second group of optical probe scanning unit diagrams; FIG. 9B is a voxel and intersected voxel diagram generated by the scanning unit of FIG. 9A according to the present invention; FIG. 9C is a result voxel 値 and FIG. Figure of intersecting voxels; Figure 10A is a diagram of a unit of three sets of optical probe scanning units of Figure 2 according to the present invention; Figure 10B is a voxel and intersected voxels generated by the scanning unit of Figure 10A according to the present invention Fig. 10C is the voxel and intersecting voxel of Fig. 10B according to the present invention. Fig. 18- This paper size applies Chinese National Standard (CNS) A4 specification (210 X 297 mm). Explanation (Figure 11A is based on the present invention; Figure 2A is a group of four optical probes scanning single element maps and inventions generated through the scanning unit of Figure 11A. Figure 11C is based on the same formula according to the present invention; 々Figure 11B Fig. 12 is a unit diagram according to the present invention Through the voxels and intersecting voxels of Figs. 8 to 11 in Fig. 1, Fig. A is an asymmetric scanning scan according to the present invention, which can satisfy the symmetrical demand. Scanning: FIG. 13C is still another asymmetric scanning unit diagram that can satisfy the symmetrical requirements according to the present invention; FIG. 14 is a circular diagram of the optical imaging system according to the present invention; and FIG. 14B is an optical diagram according to the present invention. Fig. 15 is a triangular optical probe diagram of an imaging system; Fig. 15 is a simulation diagram of an oxygen saturation function g (that is, the ratio of 卩 1 to 卩 2) at different wavelengths according to the present invention; Fig. 17 is still based on the present invention and is used at different wavelengths-oxygen saturation function-19-SS Home Standard (CNS) A4 specification (21GX 297 public love)-binding line 588158 A7 B7 V. Description of the invention (another diagram of the 17 G simulation 图; Figure 18 is according to the present invention in media with different background diffusion coefficients and total red blood cell concentration Comparison of calculated oxygen concentration with actual oxygen saturation A diagram; FIG. 19 is a time course diagram of total red blood cell (HbT) concentration, oxyhemoglobin (HbO) concentration, and deoxyhemoglobin (Hb) concentration according to the present invention; FIG. 20 is an oxygen-saturated Time course diagram; Figure 21 is a diagram of an optical imaging system according to the present invention; Figures 22A and 22B are normal and abnormal chest blood volume images respectively measured through the optical imaging system of Figure 21 according to the present invention; and Figures 23A and 23B is an oxygen saturation image of a normal and abnormal chest measured respectively through the optical imaging system of FIG. 21 according to the present invention; FIG. 24A is a sampling optical system having two waveform detectors according to the present invention and has the same close range Fig. 24B is a diagram of another sampling optical system with two waveform detectors and two wave source detectors having the same close and long distances according to the present invention; 24C is still another sampling optical system diagram with 2 wave sources and 4 waveform detectors according to the present invention; FIG. 25 is 0 (that is, the F # F2 ratio) at different wavelengths as oxygen saturation function according to the present invention ) Mode diagram; Figure 26 is another G simulation diagram at different wavelengths as oxygen saturation function according to the present invention; Figure 27 is still another G at different wavelengths as oxygen saturation function according to the present invention Figure 値 diagram; Figure 28 is based on the present invention with different background diffusion coefficients and total red blood cells • 20- This paper size applies Chinese National Standard (CNS) A4 specifications (210X297 mm) 588158 A7 B7 V. Description of the invention ( 18 Another graph comparing the calculated oxygen concentration with the actual oxygen saturation in the concentration medium; Figure 29 shows the total red blood cell (HbT) concentration, oxyhemoglobin (HbO) concentration, and deoxyhemoglobin (Hb) concentration according to the present invention Fig. 30 is a time chart of oxygen saturation according to the present invention; Fig. 31 is a diagram of an optical imaging system according to the present invention; and Figs. 32A and 32B are respectively measured through the optical imaging system of Fig. 31 according to the present invention. Normal and abnormal chest blood volume images; and Figs. 33A and 33B are normal and abnormal oxygen saturation images respectively measured through the optical imaging system of Fig. 31 according to the present invention; and Fig. 34 is a linear image according to the present invention. A scanning unit diagram configured instead; FIG. 35 is another scanning unit diagram configured for rotation or rotation according to the present invention; FIG. 36 is another scanning unit arranged for simultaneous X conversion and Y reciprocating motion according to the present invention Figure 37 is a diagram of another scanning unit configured for generating intersected voxels or cross-measurement elements according to the present invention; Figure 38 is a diagram of an optical imaging system according to the present invention; Figure 39 is an optical imaging system according to the present invention FIGS. 40A and 40B are normal and abnormal chest blood volume images and images measured through the optical imaging system of FIG. 39 without being invented; and FIGS. 41A and 41B are optical imaging systems through FIG. 39 according to the present invention. The normal and abnormal oxygen saturation images measured respectively 'Fig. 42A to 42D are examples of wave source and detector configuration of an optical imaging system according to the present invention; -21-This paper size is in accordance with China National Standard (CNS) A4 (210X297) (Centimeter)

Order

Line 588158 A7 B7 V. Description of the invention (19) Figures 43A and 43B are output signals generated by a waveform detector according to the present invention; Figure 44 is a diagram of a typical self-calibrating optical imaging system according to the present invention; Figures 45A to 45C Is a further output signal generated by a waveform detector according to the present invention; FIG. 46 is a diagram of another optical imaging system according to the present invention; and FIGS. 47A and 47B are respectively transmitted through the optical imaging system of FIG. 46 according to the present invention. Measured images of normal and abnormal chest blood volume changes; and FIGS. 48A and 48B are normal and abnormal oxygen saturation images respectively measured by the optical imaging system of FIG. 46 according to the present invention; and FIG. 49 is an optical imaging system according to the present invention Fig. 50 is a cross-sectional top view of a scanning unit according to the present invention; Fig. 51 is a cross-sectional top view of another scanning unit according to the present invention; Fig. 52 is a scanning unit view of Fig. 5 configured for linear conversion according to the present invention; Fig. 53 is an image obtained by the scanning unit of Fig. 52 according to the present invention [21, garden, Fig. 54 is produced by a waveform detector of Fig. 52 according to the present invention An example diagram of a two-dimensional splitting bed of output signals; Fig. 55 is another diagram of the scanning unit of Fig. 51 configured for rotation according to the present invention; Fig. 56A is a diagram of the arrangement for linear transformation along the X axis according to the present invention 51 tracing unit diagram; FIG. 56B is a scanning unit diagram of FIG. 51 configured for rotation according to the present invention;

Order

Green -22-

Fig. 51 is a scan of 7L according to the present invention, which is configured for linear conversion along the Y axis. Fig. 57 is obtained from the scanning unit of Figs. 56A to 56C according to the present invention. Image view; Fig. 5 is an additional form of the scanning unit of Fig. 51 which is configured for simultaneous X conversion and Y reciprocating motion at the same time according to the present invention; Fig. 9 is an & scanning unit according to the present invention. Fig. 60 is a diagram of a moving optical imaging system according to the present invention; Fig. 61 is a diagram of an optical imaging system according to the present invention; and Figs. 62A and 62B are respectively measured by an optical imaging system transmitted through the present invention Normal and abnormal chest blood volume images; and Figs. 63A and 63B are normal and abnormal oxygen saturation images respectively measured by the optical imaging system of Fig. 61 according to the present invention. DETAILED DESCRIPTION OF THE INVENTION The following description provides various configurations of optical imaging systems to provide a more specific two-dimensional or three-dimensional or time-distributed image of dystrophic properties in a physiological medium. 5 'The following description provides optical imaging systems with movable scanning. The unit's optical probe, mobile wave source_detector component, self-calibration algorithm for calibrating output signals, and real-time image construction algorithms and methods are preferred viewpoints and specific embodiments. I. General device A. General structure In the viewpoint of the present invention, the provision of an optical imaging system can be achieved in a lifetime by using a scanning unit having a scanning area smaller than the visual area.

This paper size applies Chinese National Standard (CNS) A4 specification (210 X 297 mm) 588158 A7 _____ B7 V. Description of the invention ^-One or more properties of chromophores in the target area of Physics Media are spatially distributed and temporarily changed image. FIG. 1 is a diagram of an optical imaging system according to the present invention. An optical imaging system 100 includes a main body 110, a movable unit 120, which has two wave sources 122 and two waveform detectors 124, and an exciter element 13, which can be arranged along one or Multiple curved paths to move the movable component 120 with the main body 110; and an image element 14 configured to receive signals from the sensors (ie, the wave source 122 and the detector 124), and generate chromophores and / Or a spatial or temporal distribution of its nature. By arranging a predetermined number of wave sources 122 and detectors 124, they can define a scanning unit 125 to form a basic wave source-detector for scanning media configuration. The body 110 is typically made of a hard or semi-rigid material such as plastic. As described below, the shape and size of the main body 110 may be determined according to various design standards, including, for example, a media area (ie, a target area) for scanning and inspection, the shape and size of the movable component 120, and transmission The moving characteristics of the movable component 120 generated by the exciter element 130 and the curved path of the movable component 1 are constructed.

Ir

The main body 110 includes a substantially rectangular package 112, and is configured to receive the movable assembly 120. Generally, the shape and size of the package 112 is substantially larger than the movable component 120, so the movable component 120 can move along different parts of the package 112. As described below, the area of the package 112 is generally a "target area" corresponding to the media scanned through the sensors 122, 124 placed on the movable body (or sensor assembly) 120. The body 110 is usually constructed according Various design criteria, such as the shape of the scanned media area

588158 A7

588158 A7 B7 V. Description of the invention (23 characteristics of electromagnetic waves, such as wavelengths of approximately 68 nm to 700 μm and approximately 820 nm to 84 nm. ≫ Wang Yi'wave source included in the movable component The correct number is not decisive in the invention described here. For example, the movable component includes only a single wave source that can illuminate multiple recombined private magnetic waves, and these electromagnetic waves have different waveform characteristics, the same or different signal waveforms, or different or identical carrier waves, etc. The configuration of this wave source can irradiate electromagnetic waves continuously, periodically, or intermittently. Similarly, the movable component only includes a single waveform detector for continuous, periodic, or intermittent detection of previous electromagnetic waves. The waveform detector requires movable components It includes at least one waveform detector, which is preferably configured to detect electromagnetic waves and generate an output signal in response to it. As long as the waveform detector exhibits appropriate sensitivity to electromagnetic waves in the aforementioned range of wavelengths, any waveform detector can In the present invention, the configuration of the waveform detector or the multiple waveform detector can detect multiple recombined electromagnetic waves, Each group has the aforementioned different waveform characteristics. The configuration of the waveform detector or multiple waveform detector can also detect multiple recombined electromagnetic waves illuminated by multiple wave sources, so it can generate multiple recombined output signals. Or the 'movable component also includes a single The waveform detector is configured to detect multiple recombined electromagnetic waves emitted by a multi-wave source fish. FIG. 2A is an optical probe diagram of an optical imaging system having multiple scanning units according to the present invention. An optical imaging system includes an optical detector Stick 120A, which includes 8 wave sources 122 (e.g., Sad, Sbb, Sbc, Scb,

Scc, Sda, and Sdd); and eight fluctuation detectors 124 (e.g. Dab,

Dba, Dbd, Dca, Ddb, Dcb, and Ddc), among which optical sensors (that is, Wave -26- This paper size applies to China National Standard (CNS) A4 specifications (210X 297 mm)

Binding

Line 588158

The source 122 and the detector 124) are placed on a scanning surface. Generally, each pair of the wave source 122 and the waveform detector 124 can form a scanning element, which is a basic functional unit constituting the optical probe 120A. In each scanning element, the wave source 122 can irradiate electromagnetic waves to the target area of the media, and the waveform detector 124 can detect the electromagnetic waves irradiated (eg, absorbed and / or diffused) and radiated from the target area of the media, and then generate a representative An output signal of the amplitude of the electromagnetic wave is detected on the scanning element. · The composition of one or more wave sources 122 and / or detectors 124 may further define a sensor component ",,, sensor array", or "scanning unit" 125, where each of the scanning units The configuration of one or more waveform detectors 24 can pass the electromagnetic waves irradiated by one or more wave sources 122 of the same scanning unit 125, so a media area (hereinafter referred to as " target area ") can pass through the scanning unit 125 scanning. Therefore, 'each scanning unit 125 can generate an output number of multiple outputs', and each of its output # numbers can be generated by multiple scanning elements of the same scanning unit. Each scanning unit 125 is usually defined near its optical sensors 122, 124, and its configuration can form an interrupted scanning area, so the optical properties of a special target area can be borrowed through the optical probe 1208. The intention is obtained by a single scan of the media. In the figure, the end portion of the scanning unit 125 is extended for illustration. The configuration of the scanning unit 125 and its scanning area can usually be determined by the configuration of the wave source and detector, for example, the number of the wave source 122 and the detector 124 per scanning early element 125, the wave source 122 and the detector of each scanning element 124 groups or pairs, each scanning element group or pair of each scanning unit ι25, geometric configuration between sensors 122, 124,

588158 A7

The scanning unit 7L 125 is between the scanning elements, between the scanning unit i25 of the optical probe, the irradiation ability or transmitting power of the wave source 122, the detection sensitivity of the waveform detector 124, and the like.

For reference, referring to FIG. 1, the movable assembly 120 is generally extendable and includes a longitudinal axis 127. The movable component 120 also includes optical sensors, such as a wave source 122 and a detector 124, each of which is aligned along a longitudinal axis 127. The configuration of the wave source 122 is usually at each end of the movable component 12 and the detector 124 which are inserted at equal distances from each other. 124 detections. Therefore, the functions of the wave source 122 and the detector 124 can be formed along a longitudinal axis 127 of the movable component 120 to form a scanning unit 125 (ie, a wave source-detector configuration) extending near the wave source 122 and the detector 124. And define the area (or scan volume) that should be scanned once. The movable component 120 can also be made of semi-rigid or elastic material, so the sensors 122, 124 can form optical coupling, and the surface contour 0 conforming to the target area. The movable component 120 also includes a scanning unit 125 extending along the longitudinal axis 127. The scanning unit 125 is generally regarded as a functional unit in which electromagnetic waves can be irradiated to the medium, and electromagnetic waves interacting with the medium can be detected. Therefore, the scanning area of the scanning unit I25 structure can be determined by the corresponding structure of the sensor component and / or the wave source-detector configuration, which can then be determined by the number of wave sources or detectors, the geometric configuration therebetween, and the wave source. · Calling ability or transmitting power, detection sensitivity of the waveform detector, etc. In the specific embodiment shown in FIG. 1, the wave source 122 and the detector 124 are scanning units 125 that substantially define extensions. The wave detector 124 is along the vertical axis 127 at two wave sources ____- 28.-This paper The dimensions are applicable to the Chinese National Standard (CNS) A4 specifications (210X297 mm) A7 --------- B7 V. Description of the invention (26) The units between 122 and 125 have various different sizes (such as length, Width, or height) feature ', but the size of the scanning unit 125 is usually orthogonal to the vertical axis 127 (the direction in which the scanning unit 125 and the movable component 12 () move over the exciter element 130). Therefore, as described later, the characteristic size of the scanning unit 125 of FIG. 1 is its width. It can be understood that the scanning unit 125 may constitute a part of the movable unit 120, and the scanning unit 125 is preferably movable with the movable unit 12o through the actuator element 13o. Therefore, unless otherwise specified, the terms " scanning unit ", " movable components " are used interchangeably herein. It can be understood that the scanning unit preferably defines the scanning area that can continuously scan the entire part of the unit, so a single measurement through the scanning unit can generate an output signal that covers the entire scanning area without interrupting the unscanned area. For this purpose, the wave source and the detector are preferably placed at a position not greater than a critical distance. An optimal separation between the source and the detector is usually chosen by the skilled person in the art and can be determined by (but not limited to) several factors: physiological media (for example, absorption coefficient , Diffusion coefficient, etc.), the optical source's irradiation capability, the detection capability of the waveform detector, the number of wave sources and / or waveform detectors, the geometric configuration therebetween, and / or the exciter elements described later Operating characteristics. Still referring to FIG. 2A, the previous configuration of the optical sensors 122, 124 can form a 4 × 4 sensor array on the scanning surface of the optical probe 120A. Each column of the sensor array typically includes at least two wave sources. 122 and at least two waveform detectors 124, and forms a horizontally extending scanning unit (e.g., Ha, Hb, Hc, and Hd). Similarly, each column of the detector array includes two wave sources 122 and two -29- This paper size applies to China National Standard (CNS) A4 specifications (210X297 mm) ______B7 V. Description of the invention (27) Waveform detector 124, and Define a vertically extending scanning unit (eg, Va, Vb, V., and Vd). For example, in the first and fourth horizontal scanning units (Ha, 仏), two waveform detectors Dab-Dac ^ Ddb-Dd. It is inserted between the two wave sources 8 ^ -3 and Sda-Sddi. However, in the second and third horizontal scanning units (Hb, Η.), The two wave sources Sbb-Sb. With Seb_s. . It is inserted between the two waveform detectors Dba-Dbd and Dca-Dcdi. In addition, in the first and fourth vertical scanning units (va, vd), two waveform detectors ^^. "And Dbd_ Dcd are inserted between the two wave sources Saa-Sda and Sda-Sdd. However, in the second and third vertical scanning units (Vb, Vc), the two wave sources Sbb-Scl ^ Sbc-Scc are The two waveform detectors Dab_Ddb and Dae-Dde are inserted. The optical probe of the present invention can provide a wave source · detector configuration different from that shown in FIG. 2A. For example, FIG. 2B is another optical imaging system according to the present invention. Optical probe diagram. Similar to Figure 2A, this optical probe 130A also includes eight wave sources 122 (such as sab, Sac, Sba, Sbd, Sca, Scd, Sdb, and Sdc) and eight waveform detectors 124 (such as, Daa, Dad, Dbb, Dbc, Dcb, ο ..., Dda, and Ddd) to form another 4 x 4 sensor array. However, the optical sensors 122, 124 are completely opposite to FIG. 2A A configuration is provided. That is, the waveform source of FIG. 2A is replaced by the waveform detector of FIG. 2B, and the waveform detector of FIG. 2A is replaced by the waveform detector of FIG. 2B. As detailed below, two The optical probes 120A, 130A can provide the same, or at least substantially compatible performance characteristics. Each scan of the optical probes 120A, 130A In element 125, it is preferable that the configuration of a first wave source is closer to a first waveform detector than a second waveform detector, and the configuration of a second wave source is closer than a first waveform detector. 30- This paper size is in accordance with Chinese National Standard (CNS) A4 (210X297 mm) B7 V. Description of the invention (28 is closer to a second waveform detector. In addition, the best configuration of this wave source and detector is A first close distance between the first wave source and the first waveform detector is the same or substantially similar to a second close distance between the second wave source and the second waveform detector, and A long distance between the second waveform detectors is the same or substantially similar to a long distance between the second wave source and the first waveform detector. In the second horizontal scanning unit, for example, the first wave source (Sbb) The configuration of Hb is closer to the first waveform detector (Dba ·), and the configuration of the second wave source (sbc) is closer to the second waveform detector (Dbd). In addition, the first wave source (sbb) and the The first close-range configuration between the first waveform detector (Dba) may be the same as that at the second wave source Sbc) and the second close distance between the second waveform debt detector (Dbd). In addition, the first long-distance configuration between the first wave source (Sbb) and the second waveform detector (Dbd) may be the same For the second long distance between the second wave source (s ^) and the first waveform detector (Dba). D. Exciter element Please refer to FIG. 1. The exciter element 13 is oriented in at least one curve. The movement of the wave source 122 and / or the detector 124 is coupled and generated along at least one curved path. In a specific embodiment, the operation of the exciter element 13 () is to match the movable component 120, and move the movable component (together with the wave source I22 and the detector 1 in the direction of the longitudinal axis 127 of the movable component 120); 24) Linearly transition from one end of the main body 110 to the other end. In this embodiment, the width of the movable component 120 is substantially similar to the width of the package 112. Therefore, when the linear transformation is performed on the target area, the scanning element 125 can know to trace at least a substantial part of the target area. Any excitation device can be combined with the optical imaging system for generating the previous movement. For example, a motor gear assembly may be used to generate rotations near the center of rotation at a preselected angle, or to generate a predetermined number of rotations. Alternatively, a stepped motor can be used along selective guides to produce curve transformations, reciprocating motions, and combinations thereof, where examples of such curve transformations are linear displacements along a linear path, or non-linear transformations along a curve . The 7L exciter can also generate various pulses by generating pulses (ie, functions of d⑴), steps (ie, functions of U (t)), pulses, pulse sequences, sine curves, and combinations thereof. Features are added to this move. In addition, the exciter element can produce continuous, periodic, and / or intermittent movements. The exciter element can sequentially or simultaneously generate at least two movements of the wave source and / or the detector along at least two curved paths in at least two curved directions. This movement may follow a curved path aligned substantially orthogonal to each other, as in the Cartesian orthogonal axis, cylindrical example of a sphere coordinate system. Alternatively, the aforementioned movement may be an example of a reciprocating movement, and may occur along the same or parallel curved path in opposite directions. Arrangement of the movable body, the scanning unit, and the exciter element can provide a variety of different geometries between the longitudinal axis of the scanning unit and the curved path of the movable body. For example, the scanning unit can be aligned with the exciter element in such a way that the scanning unit moves along the ^ axis orthogonal to the longitudinal axis of the scanning unit π to provide the scanning unit and / or the movable unit substantially orthogonal to the axis of the scanning unit The curvilinear path of the component. Similarly, the exciter element may move the scanning unit and / or the movable component along a substantially parallel path with the longitudinal direction of the scanning unit, or along another yttrium forming a preselected angle with the scanning unit. The latter option 具体 During the movement of the movable component, the latter embodiment enables the scanning unit -32 ·

A7 B7 V. Invention description (30) The effective scanning area is maximized. In addition, the exciter element can produce a previous movement at a fixed speed or a rate of change over time or position (eg, continuous, periodic, and / or intermittent). A selective motion controller can provide this, so this movement speed can be based on— Pre-selected modes are properly controlled. Alternatively, the movement can be controlled and can be adapted to various parameters, such as the optical characteristics of the media, and / or, for example, whether abnormal areas appear in the target area with abnormally high or low absorption or diffusion of transmitted electromagnetic waves. In addition, details of the exciter elements are provided below in conjunction with specific embodiments of the scanning unit described in Figs. 52 to 60. E · Image element is shown in Figure 1. The operation of the image element 14 is coupled with the wave source 122 and / or the detector 124, and its configuration can generate a spatial or temporal distribution in the medium that represents the chromophore or its properties. Two- or three-dimensional images. As shown, the image το 140 typically includes a data acquisition unit 142 (ie, a signal acquisition unit or signal processor), an algorithm unit 144, and an image structure or image generation unit το 146 (i.e., image processing Device). The configuration of the data acquisition unit 142 can sample optical or electrical data or signals, and these are related to the intensity, magnitude, amplitude, or other characteristics of the electromagnetic wave irradiated by the wave source 122 and detected by the waveform detector 124. The data acquisition unit 142 may also monitor other system variables or parameters related to the operation of the actuator elements and each element used to control the imaging system 100. The algorithm unit 144 may receive various signals or data from the data acquisition unit 142, and obtain multiple waveform equation solutions for the wave source 122 and / or the detector 124. Traditional analysis or mathematical methods can be used in the algorithm unit 144 to solve a set of waveform equations, such as photon -33-

588158 A7 ________B7 ____ 5. Description of the invention (31) Diffusion equation, Beer-Lambert equation, modified Beer-Lambert equation 'and related. The algorithmic unit 144 may then resolve from this, or through further mathematical processing or signal processing, to determine the absolute or relative unity of the chromophore or its properties. The image constructing unit 146 can process a previous absolute or relative tadpole of a chromophore or its properties, and provide an image of a second-degree or three-dimensional distribution pattern of the chromophore or its properties in the space and / or time domain. F. Benefits of the Invention · The optical imaging system of the present invention can provide several advantages over previous technologies, such as traditional near-infrared beam splitters, diffused optical beam splitters, and the like. Traditional optical sensors usually define scanning units, each of which allows only a single measurement at each measurement location. Therefore, when the target area is larger than the scanning area of the scanning unit, the sensor probe must be manually moved to a different area of the target area, and multiple measurements must be achieved. This procedure will increase the length of the inspection cycle, rather than mentioning poor resolution due to incorrect and / or inconsistent sensor probes at different measurement positions in the media, or inconsistent optical coupling at different measurement positions Unreliable images. To correct this, larger sensor assemblies with a large number of wave sources and detectors can be developed, so they can cover a larger target area in each measurement. However, this sensor assembly is usually large and expensive. In addition, peculiar changes in the sensor can compromise the quality of the optical and / or electrical output signals, thereby reducing the quality of the resulting image. In addition, traditional optical imaging technology requires a baseline evaluation of the output signal before scanning the target area of the media. In fact, baseline assessment is the main source of measurement errors, and traditional optical imaging systems cannot be reliably used to obtain high-resolution images of relatively large target areas. -34-This paper is suitable for financial standards (CNS) M specifications (规格 x tear public love) ---- 588158

The optical imaging system of the present invention can overcome the defects of the prior art by using only a small number of wave sources and detectors of a movable scanning unit. These wave sources and detectors are placed in an area (such as an edge) of a target area and can scan relatively Large areas of different target areas without having to move and relocate other components of the system (such as moving components of the imaging system and / or optical probes) to another area of the target area. Therefore, previous optical imaging systems required fewer sensors (less wave sources or detectors) than traditional optical imaging systems. Therefore, the optical probe of the present invention can be constituted by a small and lightweight object. In addition, with fewer sensors, the noise of special component changes in each of these wave sources and detectors can also be reduced, thereby improving the signal-to-noise ratio of the output signal and providing high quality and high quality. Resolution image. The further configuration of the optical imaging system of the present invention can ensure that substantially the same optical coupling can be formed between the medium and the movable wave source and / or the detector during the movement of the movable component. As described below, this specific embodiment allows the previous optical imaging system to establish a single baseline and apply the same baseline to multiple output signals measured at different target areas throughout the media. This specific embodiment can further allow the use of a simpler and more efficient use of the image builder, so that when scanning the target area of the test object ', a real-time image of the chromophore nature of the media can be provided. Although any analysis or exhaustion method can be used by the algorithm unit or image construction unit of the image element ', the algorithm or image construction unit of the present invention preferably adopts the solution disclosed in the following method and discussed in Patent No. · 972. π. Method A. Mathematical basis -35. I paper size applies Chinese National Standard (CNS) A4 specification (210X 297 mm)-person

Reservation 588158 A7 B7 V. Description of the invention (33) Detailed description of the system and method for measuring absolute oxygen saturation The present invention relates to an optical system and method for determining the properties and / or conditions of a physiological medium. In particular, the following describes various specific embodiments that can provide optical systems and / or methods for determining the concentration of erythropoietin (deoxyhemoglobin and oxyhemoglobin) and oxygen saturation (oxyhemoglobin concentration and The ratio of phenylhemoglobin to the sum of oxyhemoglobin concentrations). For these purposes, the following description may provide new methods for solving Beer-Lambert equations, diffusion equations, and / or modified versions. In addition, the description discloses various specific embodiments of an optical imaging system incorporating this method. It will be appreciated that the following methods and systems based on these can be used to determine the absolute concentration of other chromophore concentrations, ratios, and / or amounts of physiological media tissue and cells. In an aspect of the present invention, the provision of a new method can solve a modified Beer-Lambert equation and / or a photon diffusion equation applied to an optical system including a wave source module and a detector module. Wave source module and detector Module usually includes at least one wave source and at least one waveform detector. However, the wave source and detector modules preferably include at least two wave sources and two waveform detectors, respectively. As mentioned above, equation (Γ) is a general control equation, which is used to describe the drift of photons in a medium or the image transfer of electromagnetic waves. It can be understood that the system parameters " r '' and `` β '' have 1 · 〇値, and " ο * " is 〇 · 〇. When the parameters "r" and "quote" are approximately 1, a modified version of equation (1) • 36- This paper standard applies to China National Standard (CNS) Α4 Specifications (210 X 297 mm) Staple

Line 588158 5. Description of the invention (34 can be obtained: (¾) The same type of traditional "photon diffusion equation" has the same phase as equation (3a): • * / = ^ 25 · / 0 · βι JJ · where " S is the "from" of equation (3a), and usually describes the characteristics of the wave source such as radiated power and geometry, optical coupling between the wave source and the medium, and / or the associated optical coupling loss between them, "D " Is the corresponding equation of “'0”, and usually describes the characteristics of the waveform detector, such as detecting the sensitivity and range, the optical coupling mode between the waveform detector and the medium, and / or the associated optical coupling loss, and "A " corresponds to equation (3a) ,, y, and can be a proportional constant or a parameter related to the wave source, the waveform detector, and / or the media. Note also" 1. "and" ; I ”is only a function of time, and preferably has nothing to do with, for example, the frequency domain parameters of the frequency and phase angle of this waveform. It can also be generally understood that the wave source and the detector are preferably operated in CWS mode, that is, the wave source Irradiation over a measurement period has Less non-pulsed electromagnetic waves with substantially the same amplitude. Therefore, the optimal profile of the electromagnetic wave irradiated through the gray source is a step function (that is, 1.11 (〇), which is characterized by only its intensity (that is,).), Rather than through Frequency domain parameters. However, as long as the radiating wave is not a pulse, this waveform can take the form of a single step (for example, I.u (t) _ I〇u ... t〇)), where it represents a temporary The duration of the critical threshold =. = The radiation wave can be a series of ^ (3b) gutters with at least substantially the same amplitude-37 SS 豕 standard (CNS) A4 specification (21 () > < 297 public love) 588158 order

Line A7 B7 V. Description of the invention (35) · The ladder sequence composed of ladders. For the purpose of illustration, the optical system may include, for example, two wave sources ⑶ and SO ′ each of which can emit electromagnetic waves of a wavelength λ !, and two waveform detectors (Di and DO, which are configured to detect at least a part of the scattering equation of this electromagnetic wave ( 3b) Each pair of wave source applied to the optical system is combined with the following equations: — * • 1 Oil Σ e | J | ^ 1 ^. ^ Ci ^^ iSAe L,:. The photon expander can generate (4a) * 4 * ιλ2 | 2 = I ^ De dagger, (4b) < 4c) SL · = I ^ De J cut S2Dte UJ. ·:! ·; Where the superscript λι table 7F determines the various variables and parameter. A simplified mathematical operation can eliminate at least one system parameter from equations (4a) to (4d). For example, the source and combination factors of 8! And S2 can be deleted by using the first ratio of equations (4a) to (4b) and the fourth ratio of equations (4d) to (4c). The logarithm of the first and second ratios can then be used to produce what is traditionally called "Optical Density" (that is, OD / 1 is a pair defined as IMS1D1 / IX1S1D2 is a pair defined as IUS2D2 / IX1S2D1): 'And 〇D2 ~ 2 QDli = ln ^ SL = 131 ^-+ (^; μΑιμ- ^ ι4ιρ ») Σ •:: (5a) ·. ·. ·: · 1 :: .. 1 '» st -38- Paper size applies Chinese National Standard (CNS) A4 specification (210 X 297 mm) 588158 A7 B7 V. Description of invention (36) It can be understood that the optical density is generally not affected by the correct mode of optical coupling between the wave source and the physiological medium influences. It is further understood that the optical density is only determined by the intensity of the detected electromagnetic waves. Therefore, optical density is only a function of time and is generally independent of, or at least substantially unaffected by, frequency-domain parameters. Other system parameters can also be eliminated by reformulating equations (5a) and (5b) above. For example, items including the detector attachment factors Di and D2 can be canceled by adding equations (5a) to (5b): ·: 〇Dh = ODlxXJtOD ^ =: (6a) where jpS⑻ Coffee 邱-Qiu Jian) + ( Gong Shangqing-Ground! ⑽ ... · (你) .- · 'In equation (6b) it is clear that FX1 mainly passes through the wave source and the detector (that is, "L's" is mainly related to " geometry The structure of " and the distance between a wave source and a detector in each pair, and the path length factor (i.e., " BV is mainly "media related", and can be transmitted through physiological media And / or the optical properties of electromagnetic waves). Equations (6A) and (6b) are applied to physiological media in order to obtain quantitative physiological information such as chromophore and / or its ratio concentration. The media contains or Most substances temporarily interact or interfere with photons or electromagnetic waves that strike or pass. However, in many physiological media, such as deoxy and oxyhemoglobin (Hb) and oxygen or oxyhemoglobin (HbO), erythropoietin is Most physiologically desired chromophores. Equations (6a) and (6 b) Applied to this physiological media can produce: .. = Σ β < [ϋΒ] + 丨 (7a). ·· i -39-

Binding

Line This paper size is applicable to China National Standard (CNS) A4 (210X 297mm) 588158

Line A7 B7 V. Description of the invention (37) where [Hb] and [HbO] represent the concentrations of Hb and HbO, respectively. By configuring the wave source Si * s2, or additional wave sources such as s3 and s4 to irradiate a second set of electromagnetic waves having a wavelength λ2 different from the wavelength, a compensation equation of equation (7a) can be obtained as follows: 1 j (7b ) :; 1 Therefore, the mathematical representation of the two system variables [Hb] yun [HbO] can be derived from the algebraic systems of equations (7a) and (7b). These mathematical representations are as follows: u ODli, ODh SHbO ~ SHbO ph. [Hb] .- 11,.! '· 丨 (8a) Ί 乂 ::;'. · 1 j. \ M,! * Ί • i · i ^:; where household * = (万 念 贝AiDi-Bs1diAsidi) + i. * · M;: l (8d) 1 i Other physiological properties or indicators can be derived from the above equation. For example, oxygen saturation (so2) is a diagnostic indicator often used for the symptoms of local anemia, and is usually defined as the ratio of the concentration of oxygen hemoglobin to the total hemoglobin concentration (ie, [HbT] = [Hb] + [HbO]): -[S〇 = _ = just! 2 [HbT] [HbMHbO] 丨 4 '; ~, ㈣: ··. Combining equations (8a) and (8b) into equation (9a) can produce the following as the dissipation coefficient (s's ), Optical density (0D4), media / geometry-related factors FX1 and -40- The paper size of this paper applies the Chinese National Standard (CNS) A4 specification (210 x 297 mm) 588158 A7 B7 V. Description of the invention (38) F The oxygen saturation formula of the function 2: inverse £ 1: this 〇 · f \ ODi2 Flt (5 \ ⑼): ·.,:; · The oxygen and deoxyhemoglobin measured at different embryo lengths λ! And λ2 Dissipation coefficients can be obtained from the literature or from a separate source! As described in detail later, media / geometry-related factors Fu * FX2 can also be obtained from experience, part of experience, or theory. Therefore, the absolute 値 of the [Hb] and [HbO] concentrations of deoxygen and oxyhemoglobin can be obtained by: adding the known 値 of the dissipation factor (s, s) to the equation; the optical density (OD) measured experimentally , S); and the media / geometry-related factors Fu * FX2 obtained 値. In addition, the absolute 値 of tissue oxygen saturation (s02) can also be determined directly from the absolute 値 of [Hb] and [HbO]. All in all, the optical system and method of the present invention allows the absolute value of the concentration of red blood cells (and other chromophores) and / or its properties to be determined by measuring the intensity of electromagnetic waves irradiated by the wave source and the intensity of the electromagnetic waves detected by the waveform detector value. Note that the evaluation of FX1 and FX2 is simple because the path length factor including this term is often determined by the particular type of physiological media and the optical or energy characteristics of electromagnetic waves or photons. One way to evaluate or take an approximation to FX2 is to assume that Fu, FX2, or its ratio depends only on the optical properties of the background and the structure of the source and detector. It is generally believed that these assumptions are completely correct in linear optical processing of physiological media such as photons of electromagnetic waves or transfer drift. As long as the ratio of Fu to FX2 related to oxygen saturation is only measured through optical properties -41-This paper size applies Chinese National Standard (CNS) A4 specifications (210 X 297 mm)

Binding

Line 588158 A7 B7 V. Description of the invention

Obtained from different physiological media, this relationship can be combined with equations (8a), (8b), and (9b), and the absolute 値 of [Hb], [HbO], and / or oxygen saturation can be obtained in particular : The ratio can be approximated by the oxygen saturation polynomial shown below: m G = IhSOi = + a'soja, SC ^ ten aiS〇3 ten ...: (J (j〇)

The coefficients of each of them (that is, a0, ai, k, as, ...) can be optimally experimentally obtained through, for example, theoretical derivation, semi-theoretical judgment, or numerical methods obtained between G 値 and oxygen saturation. And get. By merging equation (10) with equation (9b), the absolute value of oxygen saturation can be measured from the dissipation factor (ie, si * sn) and the optical density (ie, " 〇D) measured experimentally. , S ") is obtained as follows:

Order

Line fa-^-^;) :)-:; ..V; By dissipating 値 of the dissipation coefficient (s's), such as the correlation coefficient of equation (10), and the experimentally measured optical density (〇D, s) Equation (u) is added, and the equation *--Equation (11) can usually be solved by counting. However, when only some polynomials of the first term are applicable, is it desirable? When the ratio of ^ to 1 ^ 2 is approximately G 値, the analytical formula for oxygen saturation can also be obtained. Other methods can also be used to get the approximate 値 of G. For example 'Although it is noted that the correctness of this evaluation is due to the one-to-one correspondence between G and [Hb] and / or [HbO], the evaluation of g is like [Hb] and / or [HbO] The function. Alternatively, 〇 can be further fixed as the same -42- This paper size applies the Chinese National Standard (CNS) A4 specification (210X 297 Public Manager 1- 588158 A7 B7 V. Approximation of the invention description (40). According to [Hb], [HbO] different 値, and / or oxygen saturation, when FX2 is quite fixed, or changes in proportion to each other, this approximation 合理 can be reasonably assumed. Or, " Lmm " 値 can be processed by processing the source and detector The geometry changes, so that G can be fixed or changed in a predetermined way. Similarly, each can approximate the function of [Hb], [HbO], and / or oxygen saturation. Alternatively, FX1 * FX2 can also Special gold is specified, which is most suitable for the desired optical system and / or physiological media. By the simple method of Fu * FX2 approximation 1, [Hb], [HbO], and absolute 値 saturated with oxygen can be obtained as follows: 1 · · ^ Hb ^ HbO .Hb.HbO. · ≫ • Ί ··: fe • ·. ·: · J {HbO} ir;-s ^ OD ^ i1 ··· * I. · F: · :: & 2b) Ί:,. · • ·· •! · .S02 ^.. · SHh QjyXi " Sfib «. · * 'I * * * ^ #. i:: :( 12c); J; • 1 • · · • • 5 : {^ Hb " auto] qjt ^ s + {£ mo ^ fwi) In this specific embodiment, the oxygen saturation (S02) can only be determined by the known 値 of the dissipation factor O's and experimentally measured optical density (OD's). . Note that the [Hb], [HbO], and oxygen saturation obtained from equations (12a) to (12c) (and / or the approximate martingale method described above) are lower than from equations (8a), (8b), and (9b ) The correctness obtained. Nonetheless, as long as the previous assumptions remain valid, the one-to-one relationship can be expected to be actual in [Hb], [HbO] -43- This paper size applies the Chinese National Standard (CNS) A4 specification (210 X 297 mm) 588158 A7 _____ B7 V. Description of the invention (41) 値, and oxygen saturation and those obtained from approximate 値 equations (12a) to (12c). This relationship can be determined as long as the optical properties of the physiological media are known. For example, the dissipation coefficient, absorption coefficient, and / or the diffusion coefficient of the physiological medium (or the nature of the chromophore) can be determined by [HbT] and oxygen saturation. With known optical properties, oxygen saturation can be evaluated at different levels through simulations of diffusion equations and / or through experiments. Equations G2a) and (12b) can then be used to calculate [HbT], and a correction function can be calculated, which is related to the calculation [HbT] with inter-member [HbT]. Similar or identical methods can be used to calculate the correction function of [Hb] and / or [HbO]. Note that these methods can be applied to different physiological media (for example, different humans or animals) to evaluate different optical characteristics, so different correction functions can be obtained. It can be understood that the previous method can be applied to any optical system and physiological media, in which the drift of photons or the transmission of electromagnetic waves can be reasonably described by the general control equation (1). Note that parameters exempting previous method steps are applied regardless of the special numbers assigned to parameters " r " and " β ". For example, r can be eliminated by using the ratio of equations (4a) to (4b), and Θ can be eliminated by using the ratio of FX2. In addition, the aforementioned method can also be applied to any modified version of control equation (1), in which the optical interaction or interference of the media can pass through the chromophore, and / or the absorption coefficient, diffusion coefficient, and / or reduced diffusion coefficient of the medium And description. For example, by assigning an appropriate unit to the parameter " γ. " This modified equation can be converted into a ~ equation that is substantially similar or identical to the governing equation (1). Therefore, it is clear that the previous method can be regarded as the generality of the control equation (1) for solving the chromophore concentration and / or its ratio. -44- This paper size applies to SS Home Standard (CNS) A4 specification (210 X 297 public love) '-A7 B7 V. Description of the invention (42) You can further understand the absolute chromophore concentration (or its ratio) 値It can be obtained through different previous methods. For example, the detector coupling factors Di and D2 can be first shifted from equations (4a) to (4d) by using a third ratio of equations (4a) to (4c) and a fourth ratio of equations (4d) to (4b), It is as follows: 〇Dlx = In /: also = ten In ++ (々 “km * " (5c) —: · · 02¾1 = lir ^ + lnf + ⑻⑽! ⑽-5, plus: (5d) Similar equations ( 5a) and (5b), this different method can produce optical densities 0Du3 and 0Du4, which are not substantially affected by the coupling mode between the waveform detector and the medium. By increasing equations (5c) to (5d), the logarithmic ratio ( That is, a ratio of the intensity of the electromagnetic wave irradiated through the wave source and another ratio of the wave source coupling factor Si * S2) can also be cancelled each other to generate: 〇D ^ = OD ^ + ODx ^ = ^ {C (: ( 6c) where A 5 ". :) + (Unload 022 ^ 11 > 2-· (6d) · · · By applying equations (6c) and (6d) to physiological media including oxygen and deoxyred hemoglobin, the following Equation (7c) can be obtained: * I = si [Hb] ^ sUp〇). (7c) Similarly, a correlation equation of equation (7c) can be applied by applying a second set of electromagnetic waves with a wavelength of 2 Obtained: Police = $ 4 Gang Shi 4〇 [Procedure: (7d) -45- This paper size applies Chinese National Standard (CNS) A4 specification (21〇x 297 mm) 588158 A7 B7 V. Description of the invention (43) Therefore By solving equations (7c) and (7d), the mathematical representations of the two system variables [Hb] and [HbO] can be obtained as follows:. Also shoot-also learn [Desc] =: (8e).: · Ι ;; (30: · (8h) oxygen saturation can then be expressed by the following formula: Sot fei- · o ^ L ^ L \ 〇A; K: ^ OD ^ F ^ [ε ^ 〇- είί) (9c) The aforementioned method Equations (9b) and (9c) derived from other variables can be used to set parameters to reduce the system, and can finally represent [Hb], [HbO], and known or measured system variables from, for example, experimental measurement of optical density, or Parametric viewpoints of oxygen saturation, known 値 of the dissipation factor, and / or other geometry-related parameters determined by the actual geometry of the wave source-detector configuration. It is further understood that the previous method of the present invention allows the wave source to be implemented in different specific ways For example, irradiate multiple recombined electromagnetic waves with different waveform characteristics. The simplest configuration can provide two wave sources (such as Si and S2), each of which Source 46 can shine

It emits electromagnetic waves with different wavelengths, phase angles, and harmonics. For example, an optical surveillance and / or imaging system operating in CWS mode preferably includes a wave source that can irradiate non-impulsive and non-phase-modulated electromagnetic waves with at least substantially the same amplitude at a minimum measurement period. Similarly, the wave detector of the cws system can only perform electromagnetic wave intensity measurements in a continuous manner. It can be understood that as long as the waveform detector can detect the waveform in a sufficient period of time, this intensity ′ can also be performed intermittently in order to detect its strength. Therefore, the wave source of the cws system need not irradiate continuous electromagnetic waves. Alternatively, the configuration of each wave source may irradiate substantially the same signal wave, however, these same signal waves may overlap on different carriers. In still another specific embodiment, as long as different sets of electromagnetic waves can be identified by one or more waveform detections, the configuration of a single or each wave source can illuminate multiple reconstituted electromagnetic waves intermittently, continuously, or simultaneously. Similar configurations can also be applied to waveform detectors. For example, the two waveform detectors (01 and D2) are provided so that each detector can detect only a single set of electromagnetic waves. Alternatively, a single or each waveform detector can detect multiple recombined electromagnetic waves with different waveform characteristics in an intermittent, continuous, or simultaneous mode. Because the previous systems and methods of the present invention allow these various variables, they can be combined in any conventional spectrum such as TRS, PMS, and CWS. In another aspect of the present invention, the provision of an excessively arbitrary number method can solve the modified Beer-Lambert equation and / or photon diffusion equation. These equations are applied to include a wave source module and a detector module. The optical system of the group, wherein the configuration of at least one of the wave source module and the detector module can irradiate or detect more than two groups of electromagnetic waves. Provided through the configuration of the optical system -47- This paper size is suitable for domestic standards (CNS) M specifications (21GX297 public copy) 588158 A7 _______ B7 ^ ______ 5. Description of the invention (45) " '-比 " System Variables " " More equations, and, as a result, additional equations can be used for other purposes, for example, (1) improve the accuracy of the evaluation of the system variables (such as chromophore concentration or its ratio); (ii) determine System parameters (for example, " with /, /? Η,, " Bmn ", " Lmn", " dport ", or other parameters such as the absorption coefficient and diffusion coefficient of the media and / or chromophore ) Or (hi) Provide the relationship between the media and / or geometric related parameters and system variables and / or other system parameters in the private mode (1) or (3b). • In the first embodiment, additional equations can be used to obtain multiple chirps of chromophore concentration (and / or its ratio). Inconsistencies can be expected to occur at least to some extent in the assessment of concentration (and / or its ratio). This inconsistency is the essence of each pair of source and detector. Alternatively, the non-coercion can also occur in a non-homogeneous medium with regional variation in optical properties. A method using different concentrations of chromophores (and / or their ratios) can average this variable to obtain an arithmetic, geometric, or logarithmic average to reduce any or systematic errors and improve correctness. Alternatively, each measurement frame can be averaged by an appropriate weighting function, such as the geometry of the wave source and detector module. In a second embodiment, the relationship between the media and / or geometrically related parameters of the media and / or equations (1) or (31)) and the chromophore concentration (or ratio thereof) can be obtained by an additional equation. For example, when G (that is, the ratio of Pλ1 and ρλ2) is approximately an oxygen saturation polynomial according to equation (10), each coefficient of the polynomial is specified by an initial value, which can then be adapted by using a conventional number. Improved by iterative techniques. In addition, additional equations can also be used to find the relationship between the approximate oxygen saturation [Hb] and / or [HbO] and the actual _ __ -48- ΐ paper size suitable financial @ s 家 标准 (CNS) A4 specifications (21GX297 (Public love) " I --- 588158 A7 B7 V. Description of invention (46)

Department function. In addition, 'extra equations can also be used to evaluate system parameters (e.g.,', ',,'. Or the absorption and diffusion coefficients of the chromophore). For example, a forward counting method can be used to evaluate the absorption and reduced diffusion coefficients of physiological media. As mentioned above, media photon drift and electromagnetic wave transmission can be described by diffusion or transmission equations. Assume that the media is semi-infinite and homogeneous. 'The following equation describes the electromagnetic waves detected by a j-th detector:' Bu (13) where Si usually represents a wave source consolidation parameter that describes the characteristics of a wave source. Radiated power and structure, optical coupling mode between the i-th source and the medium, and / or the Korean loss between them, and Dj is a detector coupling factor commonly used to describe the characteristics of a j-th waveform detector, The optical nucleation mode between the j-th waveform detector and the medium, and the associated optical loss between them. A pair of numbers π φ " indicates the forward simulation of a pair of wave source and detector. The parameters " μ3 " and " " represent an absorption coefficient and (reduced) diffusion coefficient, respectively. When the optical system includes, for example, the total number of Ns sources and ND waveform detectors, equation (13) can be expressed in the following matrix form:

: ·· Persistent. Yong ~. , / ^;) ·. (14) • · · • *…, skDk · μ, in order to understand all system variables Iij (i = l,… team and J = 1, ..., Ns) is time -49 -This paper size applies to China National Standard (CNS) A4 (210X297mm) —_ 丨 丨 丨 588158

Function, and preferably independent of, or at least substantially unaffected by, frequency domain parameters. Each end of equation (14) is divided by the first block of each matrix: · «. 1… ~ — _ 1 · Zhan · 骞 · · Sickle * ZS; Na ten, μ» L j -1 * 1

Each column of the matrix of equation (15) is then divided by the first column of each matrix to produce the matrices A and B:: Λ = 5 :: gull 1 1… 1 • · 9% · · • · t 1 7 ~ 1 Μ J S3;.!: 1 · _ ·. 丨 1: ί * · · |; 1 φ [η ^ > μα9μ) -10,000: :( 16): ... LJ ^ s. \ J. Φ { νηΜΛ > μ]} φ (^ 19μβ9μ ^ *. '': ··. _ * a According to the expression of formula (16), the matrices a and B are functions of absorption and reduction of diffusion coefficients, and are not affected by, for example, & And Dj depend on the coupling parameters of the source and the detector. Therefore, 'By reducing the difference between A and B (ie, || AB ||), the best estimate of the absorption coefficient and (reduction) diffusion coefficient can be transmitted through The habitual curve is obtained from several figures as appropriate to the method. After evaluation, the absorption and reduction diffusion coefficients [Hb], [HbO], and oxygen saturation can be obtained by the following formula: [册]-K 乂 4; •.; • 1 i (17a) \ HbO \ L ：： 1 «〇« 0 ·: ··. _ * «(17b): ·. -50- This paper size applies to China National Standard (CNS) A4 (210 X 297 mm) ) 588158 A7

_ + [m〇] Xinxin :,): (i7c) Note that the previously too arbitrary method can be used for the optical system, which can have at least 2 wave sources, 3 wave detectors, and at least 3 wave sources With 2 wave sources, or 3 wave sources and 3 waveform detectors. Alternatively, an overly arbitrary method can irradiate or detect multiple recombined electromagnetic waves separately. It can be understood that the methods previously decided too much by martial arts can be combined with any traditional mathematical method. For example, the use of a forward, backward, or hybrid model may determine, for example, the coefficient of dissipation, the coefficient of absorption, or the coefficient of diffusion of, for example, a physiological medium (or including a chromophore). This model can also be used to evaluate the absolute value of chromophore (and / or its ratio) / degree. However, the results obtained through this mathematical model can only erode the errors associated with it. This essential error can be reduced by using a mathematical model with a second or highest order error term. However, this model has one major disadvantage that requires strict mathematical calculations. Therefore, the correctness and efficiency of each mathematical model must be considered in selecting the appropriate model. In still another aspect of the present invention, the provision of an optical system can solve a set of waveform equations and determine the absolute chromophore (and / or its ratio) concentration contained or temporarily discontinued in physiological media. . An optical system may include a royal body, a wave source module including at least one wave source, a detector module having at least a waveform detector, and a processing module. The wave source module is supported by the royal body, is optically coupled to the physiological medium, and irradiates at least two sets of electromagnetic waves with different wave characteristics to the medium. The detector module is also supported by the main a and is light-settled with the media, and can detect electromagnetic waves transmitted through the media. The operation of the processing module is coupled with the detector module, which can solve the problem -51-

Binding

Line 588158 A7 B7

A set of multiple waveform equations that determine the absolute chirp of the chromophore concentration and / or its ratio. In general, processing groups include an algorithm that solves the previous equations (1) or (313), or a modified version thereof. For example, one or more of the previous methods may be incorporated in hardware or software, or implemented in a microprocessor. Therefore, the absolute concentration of chromophores (and / or their ratios) can be measured from, for example, the electromagnetic slope radiated through the wave source, the intensity of the platinum test by the wave detector, and the description in the electromagnetic wave and media. Between at least one system parameter of an optical interaction or interference. The algorithm of the processing module includes one or more functions or correlations to represent the media and / or geometry related items of the previous waveform equation as a function of the chromophore concentration (and / or its ratio) function ^. The team can perform the above-mentioned overly arbitrary method. In addition, processing modules and algorithms can be modified to operate in TRS and PMS modes. The wave source module includes at least one wave source, and the detector module includes at least two waveform detectors. Alternatively, the wave source module may include at least two wave sources, and the detector module may include at least one waveform detector. However, it is preferable that the wave source and the detector module include at least two wave sources and at least two wave detectors, respectively. Specific embodiments using the above method As described above, the previous method of the present invention is not affected by the actual structure of the wave source and the detector. therefore. The light lift monitoring and imaging system of the present invention includes any wave source and the number of detectors that are arranged only on any structured object with patent case number '972 "Symmetry needs". However, some wave source_detector structures can be The accuracy, reliability, and concentration of renewable chromophores (and ^ or its ratio) are absolutely unacceptable.

Order

Line -52-

B7 V. Description of the Invention (50) In a specific embodiment, the multiple wave source and the waveform detector can be configured, so the close distance between each pair of wave source and the detector is at least substantially the same. For example, for a wave source module including a first and a second wave source, and a detector module including a first and a first waveform detector, The first close range configuration may be substantially similar to the second close range between the second wave source and the second waveform detector. In addition, a first long-distance configuration between the second wave source and the second waveform detector may be substantially similar to a second long-distance between the second wave source and the first waveform detector. It can be understood that this specific embodiment is not necessary for each individual pair of wave source and detector. For example, when the wave source module has M wave sources and the detector module has N waveform detectors ("and ν are integers greater than 1), at least two of the μ wave sources and N waveform detectors The two are configurable, so the distance between a first wave source and an Nl detector is substantially similar to the distance between an M2 wave source and an N2 wave detector, and at the% wave source The distance from the A waveform detector is substantially similar to the distance between the m2 wave source and the second wave detector, where Ml * m2 is a two integer between 1 and ", and where ^ and N2 are Two integers between 1 and N. Such a specific embodiment can typically be implemented, for example, by arranging the wave sources and detections substantially linearly symmetrically along a straight line. FIG. 3A is a diagram of a sampling optical system having two wave sources and two waveform detectors with the same near and long distances according to the present invention. It can be understood first that the wave source-detector configuration of FIG. 3A can satisfy the same near-distance and long-distance structure. The second short distance from the detector D2. In addition, the paper size applies to the Chinese National Standard (CNS) A4 (210 X 297 mm) 588158 A7 B7 between the wave source 31 and the detector 02-53- 5. The long distance between the invention description (51) It is the same or substantially similar distance between the source S2 and the detector D !. The advantage of meeting this structural limitation can be observed that electromagnetic waves 实质 are transmitted, absorbed, or diffused substantially uniformly over the entire target area or target volume of the medium (refer to the caraway path of the electromagnetic wave in the figure). Therefore, photon or electromagnetic wave radiation can uniformly cover all areas of the target area of the media, thereby improving the accuracy and credibility of the output signal (eg, an improved signal-to-noise ratio) produced by the waveform detector. As illustrated in the following example, the previous linear configuration of the wave source and detector provides absolute accuracy of oxygen and deoxyhemoglobin concentration and oxygen saturation with higher accuracy. It is also understood that not all wave sources and / or detectors must be configured linearly. For example, the wave source and the waveform detector can be configured not only linearly, but also with substantially symmetrical lines and / or symmetrical points. As long as this symmetrical structure is maintained by the wave source and the waveform detector, the same close and long distance requirements can be automatically met. In another specific embodiment, the multiple wave source and the detector can be configured in an asymmetric structure that does not meet the requirements of near and long distances. Fig. 3] 8 is a diagram of another sampling optical system which can have two wave sources and two waveform detectors with different near and far distances according to the present invention. As shown, the near and long distances of the wave source-detector pair are different. In addition, the banana-shaped path of the electromagnetic wave (reference picture) shows each wave source-detector pair covering different parts of the target area at different depths. The configuration of the " dagger wave source detector " allows detection of electromagnetic waves absorbed or diffused by different parts of the target area at different depths. In still other embodiments, the previous symmetric and asymmetric embodiments can be implemented in a single wave source-detector configuration. Figure buckle is still another sample of this paper. Standards for Financial Standards (CNS) • 54 588158 A7 B7 V. Description of the invention (52) Optical system diagram, which can have 2 wave sources and 4 waveform detection according to the present invention. Tester. It can be understood that not every wave source-detector pair can satisfy the same near and long distance structure of Fig. 3A. For example, although the first and fourth waveform detectors are printed! And DO and the second and third waveform detectors (〇2 and 〇3) have the same near and long distances from the wave sources (Si and SO, but this near and long distance is related to the The first and third waveform detectors (〇1 and d3) or the second and fourth waveform detectors (1), 2 and D4) are different. Therefore, by selectively coupling the wave source with the waveform detector and By irradiating and detecting electromagnetic waves, a symmetrical or asymmetric wave source-detector configuration can be achieved. Another advantage of this specific embodiment is that this wave source-detector configuration allows multiple scans of a specific target area of the media. For example The area placed under the second waveform detector (d2) can pass through 6 different wave sources such as Si-DrDySa, Si-Di-DrSs, Si-DyDrS], Si-DyDcSs, and Si-DrD ^ rSs- Detector pair scan. Therefore, the result of chromophore concentration (and ratio) can definitely be improved. It can be understood that the actual structure of the wave source and detector assembly will not affect the chromophore concentration and its ratio. For example, in all previous equations, the Structure-dependent item L'L " or `` LsiDj '', which represents a linear distance between the i-th source (Si) and a matching j-th waveform detector (Dj). The j-th waveform is detected. The operation of the detector is coupled with the first wave source, so that the electromagnetic waves irradiated by it can be detected. Because L 値 is determined by the design of the wave source-detector assembly, and because other system variables or parameters are not determined by L 値, Therefore, the previous method of the present invention can be used regardless of the symmetry between the wave source and the waveform detector. _ -55- This paper size is in accordance with the Chinese National Standard (CNS) A4 specification (210X297 mm) 588158 A7 B7 V. Invention Explanation (53) The previous application of the symmetric waveform-sacral detector structure can construct a two-dimensional optical probe of the cws optical monitoring and imaging system. In a specific embodiment, the symmetrical wave source-detector configuration of FIG. Stacked in a way to form a 4 x 4 square or rectangular optical probe. For example, the first and fourth columns have two waveform detectors inserted between the two wave sources, and the second and third columns have two waveform detectors. Two wave sources inserted between detectors. In a specific embodiment, the configuration of the optical probe has different numbers of wave sources and / or detectors in the horizontal and vertical directions. For example, the configuration of FIG. 3A can be repeated twice to form a 4x 2 probe, which can be repeated 6 Then a 4 X 6 probe is formed, etc. In still another specific embodiment, this symmetrical wave source-detector configuration can also be repeated in an angular manner to form a circular or arcuate optical probe. In addition, the waveform The repeating rows (or bars) with the waveform detector can be extended to form trapezoidal optical probes, or stacked to form optical probes with parallelograms. This symmetrical waveform-detector structure and the further development of optical probes with various geometries A specific example is US Patent Application No. op / 778, filed February 6, 2001. 4. Provided in the name " Optical Imaging System with Symmetric Optical Probe ", which is only listed here for reference. It can be further understood that the two-dimensional optical probe of the CWS optical surveillance and imaging system can also be constructed based on the previous asymmetric wave source, detector, and detector. For example, asymmetric wave source-detector configurations can be repeated at any distance and / or in any order or pattern to form a square, rectangular, bow, or circular optical probe. Note that this asymmetric wave source detector configuration can be repeated at a predetermined distance (for example, stacked on top of other columns), so repeated wave sources and detectors (for example, a block source and detector) can satisfy the previous Near and long distance requirements. -56 · This paper size applies to Chinese National Standard (CNS) A4 (210X297 mm) 588158

The previous wave source-detector structure and optical probe thus constructed can also be achieved by linear substitution, and / or rotating one or more sensors (ie, wave source and detector), and here the sensor Maintain optical coupling with the media. This specific embodiment allows more than one scan of a particular target area, and provides more measurement data along multiple scan paths and / or different scan angles at multiple speeds, such as through a source and detector. This optical probe using a moving sensor element allows the measurement of absolute chromophore and / or scene > image structure by using fewer wave sources and detectors, regardless of the actual structure of the wave source_detector. In addition, the optical probe of the mobile sensor and the optical probe from which the image is directly obtained are filed in U.S. Patent No. 09 / 778,617, entitled " Optical Imaging System for Direct,

Image Construction ", which is listed here for reference only. In practice, a wave source module with at least one wave source and a detector module with at least one wave debt detector can be provided to the scanning surface of the optical probe , Its operation is connected to the main body of an optical system. Or, the wave source and / or the detector module can be arranged on the main body 'and the optical fiber is provided to connect the wave source and the detector module to the surface of the optical probe. Any conventional wave source and detector can be used with the optical probe. However, it is preferred that the wave source can be irradiated between 500 nm and 1,200 μm, or especially between 600 nm and 900 nm. Electromagnetic waves in the near-infrared range between 耄 micrometers, and the waveform detector has appropriate sensitivity to previous electromagnetic waves. The optical probe is placed in a target area of physiological media, and its scanning surface is in the target area so that there is An optical coupling is formed. The wave source module can be excited, so at least two sets of electromagnetic waves with different waveform characteristics can be irradiated to the media. Detective • 57 · This paper standard is applicable to China Home Standard (CNS) A4 specification (210 X 297 mm) 588158 _ A7 ______B7 V. Description of the invention (55) "-The detector module can then obtain illumination from the wave source, transmission through the media, and guided waveform detection The electromagnetic wave of the detector. The waveform detector can generate an electrical signal for transmission to the processing module of the main body of the optical system. Experimentally measure the intensity based on electromagnetic waves and at least one system parameter such as the dissipation or diffusion coefficient of the chromophore. The management group can calculate the absolute 値 of oxygen and deoxyhemoglobin or oxygen saturation concentration. Note that the optical system according to the present invention includes a formula for solving the module opened from the processing component. This formula of the module is solved. Various mathematical models are included to perform one or more of the foregoing methods of the present invention. Although the previous disclosure is directed to obtaining absolute concentrations of oxygen and deoxyhemoglobin (and / or its ratio), previous optical systems and methods The application can obtain the absolute content of other substances in the media or properties. For example, the system and method of the present invention can be directly applied or modified to determine, for example, lipids, cells Absolute 値 of other chromophore concentrations (or ratios) of pigments, water, etc. The wavelength of electromagnetic waves can be adjusted to a higher resolution, which is determined by the absorption or diffusion coefficient. In addition, chemical components can be added to the media, In order to improve the optical interaction or chromophore interference in the media, or to convert a non-staining substance of the media into a chromophore. As mentioned above, the previous optical system and method of the present invention 69 is the most incorporated technology in a continuous wave dichroic mirror. However, this system and method can also be combined with time resolution and phase modulation spectroscopy technology. The optical system and method according to the present invention can find various medical applications. As mentioned above, the use of this optical monitoring and / or image and method can be Measure the absolute radon of oxygen and deoxyhemoglobin, and / or its ratio concentration. -58- of this optical system This paper size is applicable to China National Standard (CNS) A4 specification (210 X 297 mm) 588158 A7

The benefit is a non-trivial diagnosis of local anemia and / or local anemia in various organs and tissues. These organs and tissues can be, for example, brain (stroke), ~ (local anemia), or originated from abnormal hypoxic red blood cells. Other physiological abnormalities characteristic of vegetative concentration. In addition, tumors can be easily detected in various internal tissues, chest, and skin. This optical and method can also be used to diagnose vascular occlusion during or after a surgical procedure involving tissue, skin, and organ transplants such as heart, lung, liver, and kidney. · Combining any previous solution with an optical probe with a previous symmetrical wave source-detector configuration of the present invention can provide further benefits over previous techniques compared to CWS technology that allows measuring changes in red blood cell concentration, here The described symmetrical wave source-detector configuration can provide a direct device to evaluate the various chromophore properties of physiological media " absolutely, spatially, or temporally, including 'hemoglobin. This also allows physicians to assess oxygen concentration and oxygen saturation directly in the tissues, cells, organs, muscles or blood of animals and / or humans. The previous symmetrical wave source-detector configuration also allows physicians to make direct-tested diagnostic compliances based on the chromophore properties of the media "absolutely,". The optical probe selection unit of the present invention can adopt various wave source detector configurations satisfying the patent, 972 claim requirements. Figures 4 and 5 are examples of this symmetrical scanning unit. The symmetrical configuration of the wave source ridge detector in Figures 6 to 6 is related to a symmetrical line 127. However, these symmetrical configurations are related to the symmetrical points 128 of Figures 7A to 7C. related. It can be seen in the previous figure that the shape and size of the wave source and detector can be simplified and easy to explain without drawing to scale. 7A and 7B are linear scanning unit diagrams according to the present invention. The scanning units (1 and Hf) in Figures 6A and 6B are the same or similar to Figures 2A and 2B, so they can be used from -59- This paper size applies the Chinese National Standard (CNS) A4 specification (210X297 mm)

Binding

Line 5. The invention description (57) can satisfy the symmetrical requirement of the same near and long distance between the wave source 122 and the detector 124. It can be understood that each scanning unit can be modified without meeting the previous corresponding requirements of patent * 972. For example, in the scanning unit, as long as the distance does not exceed the critical range of the wave detector's critical range, such as a few centimeters to 0 centimeters, especially about 5 centimeters in human and / or animal tissues, the detection and detection in adjacent wave sources The distance of the device can be lengthened or shortened. In addition, as long as the symmetry related to the symmetry line 127 can be maintained, the waveform detector and the chirp. The distance between them can also be adjusted to be the same or different from the close distance between the adjacent wave source and the detector pair, for example, < 1_ £ ^ and. 6C and 6D are diagrams of a square scanning unit according to the present invention. In each of these regular gimbal scanning units, two wave sources and two waveform detectors are arranged on the four vertices of a square. In particular, as shown by the center of the scanning unit, the two wave sources Saa and Sab are arranged on the top apex of the square, and the two waveform back-testers Dba and Dbb are arranged on the bottom and pass vertically through the center of the square. Therefore, the close distance between the Zheng wave source and the two t corresponds to the vertical distance between the wave source Saa (or Sab) and the detector Dba (or Da), and the long distance is connected to the wave source s "(or D detector, (Or Dab) diagonal length. The same can be applied to the scanning unit core of FIG. 6D with a wave source-detector configuration opposite to 6c. As mentioned above, as long as the above-mentioned sensitivity limit can meet the waveform detectors D aa and D ab The near or long distance between adjacent sensors can also be adjusted. Figure 6E is a diagram of a rectangular scanning unit according to the present invention, in which two wave sources and two waveform detectors are placed in four of the rectangular scanning unit & Vertex configuration. Similar to the previous scanning unit, the wave source_detector configuration of the previous scanning unit is also available.

The paper size is suitable for SS Home Standard (CNS) A4 (2ΐ〇ί 297 mm) 5. Description of the invention (58) Conversely, the wave source can be arranged on the top vertex of the rectangle; however, the waveform detector can be arranged on Vertex below. As long as the previous sensitivity limit of the waveform detector meets the 'horizontal and vertical distance between adjacent optical sensors, it can be further increased or decreased. 6F and 6G are diagrams showing a trapezoidal scanning unit according to the present invention. In the trapezoidal scanning unit Ta shown in the figure, the two wave sources Saa and Sab are arranged on the upper vertex of the trapezoid, and the two waveform detectors Dba and Dbb are arranged on the lower vertex, so the symmetry line 127 can pass through the center of the trapezoid. More specifically, the configuration of the two opposite ends of the trapezoid is preferably the same length to meet the previously symmetrical needs of the patent, 972. Therefore, the short distance is the distance between the wave source Saa (or Sab) and the detector D heart (or Dbb) l, and the long distance is between the wave source 3 ^ (or I. and the detector Dbb (or Dba)). 6G is the same as the scanning unit Db of FIG. 6G except that the sensor is the opposite configuration. FIG. 6H is still another trapezoidal scanning unit according to the present invention, wherein the top vertex of the trapezoid is larger than the bottom Except for the separation of the vertices, the tracing unit Tc 疋 is substantially similar to Tuhao and 6G. As mentioned above, as long as the two opposite ends of the trapezoid have the same length, and the previous sensitivity limit can meet the waveform detector 'in the adjacent sensor The distance between them can also be adjusted. Fig. 7A is a diagram of a similar linear scanning unit according to the present invention, in which the scanning unit Pa includes two waveform detectors Dba and Dbb, and is arranged in the central portion, where the first wave source Saa is configured In the upper right corner of the scanning unit, and the second wave source sca is arranged in the lower left corner. In particular, the wave sources sca and Saa are arranged at the same angle as the waveform detectors Dba and Dbb, respectively, and they can be arranged at the same distance. , Symmetrical wave source and detector configuration is -61 Ben paper scale applicable national standards Choi States (CNS) A4 size (210X297 mm) 588158 A7

Order

Line A7

DESCRIPTION OF THE INVENTION The horizontal distance between the B7-shaped debt detectors Dab may be a short distance (for example, when the appearance ratio is less than 1.0) or a long distance (for example, when the appearance ratio is greater than 10). When the appearance ratio of this scanning unit is approximately 1.0, the distance between a wave source and two adjacent waveform detectors becomes the same, and the patented, 972 symmetry requirement cannot be met. This is in contrast to the wave source-detector configuration of FIG. 6 (: and, where the previous symmetrical requirements meet the square scanning units 1 and Sb. Due to the irradiation and / or sensitivity limitations of the wave source and the detector, among the previous scanning units Each one covers only a small scanning area. Thus, as shown in FIGS. 2A and 2B, the optical probe 120A of the optical imaging system of the present invention typically includes multiple scanning units on the scanning surface, so that the optical probe 120A can scan Target area, which is usually larger than the scanning area of individual scanning units. Although this scanning unit can be configured in a symmetrical or asymmetrical manner, and in any combination and / or exchange manner, the configuration of multiple scanning units may preferably share one Or multiple wave sources and / or detectors, in order to increase the efficiency of using a limited scanning area and improve the resolution of the resulting image. In other words, when combining some or all wave sources and / or detectors in more than one scan When the component and / or the scanning unit, the optical probe or optical imaging system includes an image component, the image component defines a multi-scan component and a multi-component This view of the present month will be discussed using the optical probe 120A of 2A as a specific embodiment. Fig. 8A is a first set of scanning unit diagrams of the optical probe of Fig. 2A, and Fig. 8B is a diagram of The voxel and intersected voxel maps generated by the scanning unit of 8A, and the resulting voxel 値 and intersected voxel 値 according to the present invention. The optical probe 120A includes 4 horizontal scanning units (Ha, Hb, He, and Hd) With 4 verticals

Na 158 V. Description of the invention (61: Tracing early (va, vb, Vc, and Vd), where each scanning unit 125 can generate-or multiple output signals, these output signals are corresponding to each scanning order: 125 Representatives of chromophores or their properties in the target area of the scanned media. "/ Π Figure 8B tf, each scanning unit 125 is a" · voxel "that defines an image field 200, which is 200 in the image field Each voxel is a small area corresponding to the target area of the media. One or more of the wave sources 122 can radiate electric and magnetic waves to this area, and one or more waveform detectors 124 can detect this electromagnetic wave and respond to The output signal is then generated. Subsequently, the image element or optical image system of the optical probe ιαα can sample the output signal generated by the waveform detector ΐ24, and solve the wave source 122 and the detector 124 applied to the same scanning unit 125 A set of waveform equations, and a representative of the chromophore or its properties. That is, the image element defines a scanning element based on a predetermined composition of the wave source 122 and detection = 124, and the space consists of two or more overlapping or non- Overlapping scanning element This can constitute the scanning unit 125, sample the output signal generated by the waveform detector 124 of each scanning unit, obtain the previous set of solutions from the waveform equation, and calculate the integral voxel 每个 for each voxel. Each voxel 値 is usually A region or volume average of the chromophore or its properties, the average is usually related to each scanning region or volume of the sweep unit 125 or to each voxel region or volume formed in the imaging field 200. It can be understood By the time the wave detector 124 has a sensitive range of substantially the same thickness or depth of the media covering the entire target area, the area average voxel 値 is substantially similar or the same as the volume average voxel 値. In the specific embodiment shown in FIG. 8A The horizontal scanning and binding of the image field 20a 64-588158 A7 B7 V. Description of the invention (62) The units Ha, Hb, H. and Hd define four parallel horizontal voxels 204a, each of which is in the X direction Extended, and stacked on top of each other in a continuous pattern. According to the output signal 14 produced by each of the horizontal scanning units Ha, Hb, Hc and Hd, the image elements can be solved separately. The waveform equation of each horizontal scanning unit and the voxels 値 ha, hc, and hd that determine each horizontal voxel 204a. For simplicity, FIG. 8B shows only one horizontal voxel 204a (from the top Third person.) Similarly, the four vertical and straight scanning units Va, Vb, Vc, and Vd are four vertical voxels 204b that define continuous and side-by-side extensions in the γ direction, and have Va, Vb, and Vc, respectively. , And Vd voxels 値. For simplicity, FIG. 8B shows again only a vertical voxel 204b with voxels 値 Vd. As shown, each horizontal scanning unit can be shared with one of the scanning units An ordinary optical sensor, by which the intersecting voxels are defined as the overlapping areas where horizontal and vertical voxels cross. Therefore, the optical probe i20A of FIG. 8A can define 16 intersecting voxels in a 4 X 4 matrix in the imaging field 200, each of which has two intersecting voxels that are permeable to intersecting voxels. One separates the intersecting voxels. For example, although two intersecting voxels 214a, 214b are voxels Ha that are generally defined at the top level and have a voxel 値 of ha, the intersecting voxels 214ag and fine voxels 値 can be calculated from ^ and ha. The intersecting voxels 値 can be obtained from v. And] ^ obtained. Generally, the intersecting voxels 値 can be calculated by, for example, arithmetically, geometrically, and weighting the individual voxels 相 of the intersected voxels. Or ~, one of the constituent voxels 値 can also be selected as an intersected voxel 値. Note that, similarly, the evaluation of the chromophore and / or its properties, the correctness and the resolution of the distribution image are due to voxels --- 65. This paper ruler is in use S _ quasi-specification (21G X (297 mm) ---

Order

Line 588158 A7 B7 V. Description of the invention (63) The size, the size of the intersected voxels, and the output signals or the number of voxels 用来 used to calculate the voxels 値 or intersected voxels 分别, respectively. In this perspective, each of the square-intersecting voxels of FIG. 8B has substantially the same resolution in the entire imaging field of 2000. The optical probe of the present invention with previous embodiments provides several advantages. By configuring the scanning unit to share one or more common optical sensors, the optical probe requires a smaller number of wave sources and detectors. Therefore, previous optical probes can be provided as small and lightweight objects. In addition, the nature of the variation of the components belonging to one of these optical sensors can be reduced, thereby improving accuracy, improving print quality and resolution of the resulting image. In addition, the optical probe of the present invention does not require baseline measurement, which is usually required in prior art optical systems. Therefore, the optical probe of the present invention can effectively construct an image, and can provide a real-time image property of the chromophore or its property distribution in a substantially real-time manner during the scanning of the target area of the test object. In implementation terms, the optical probe 120A is placed in a media target area of each of the optical sensors forming the appropriate optical coupling. The wave source 122 can be excited to irradiate the electromagnetic wave to the medium, and the waveform detector 124 is also activated to measure the electromagnetic wave transmitted through the medium. In order to interfere with the noise 'wave source I24, it is best to synchronize so that only one wave source can irradiate electromagnetic waves with a preselected waveform characteristic in a preselected period during which other wave sources are turned off. The waveform detector 124 can also be synchronized so that only these waveform detectors that form a scanning element using an excitation wave source can detect electromagnetic waves and generate an output signal in response thereto. After the selected wave source is irradiated, the same or another wave source can then start to radiate electromagnetic waves having the same or different waveform characteristics. -66- This paper size is applicable to China Standards (CNS) M specifications _297297 A5. 588158 A7 B7 V. Description of the invention (64) All sources in the first scanning unit of the optical probe 120A-detector pair are completed After the aforementioned electromagnetic wave is irradiated and detected, similar or identical operations can be repeated in the next scanning unit of the optical probe 120A. This sequence of illumination and / or detection usually does not affect the operating characteristics of the optical probe 120A and the final image representing the chromophore or its property distribution. An optimal sequence selection is usually a matter of choice in the art. The imaging element of the optical probe or optical imaging system can sample and obtain this output signal at a preselection rate and / or duration of each element of each scanning unit. The image element can then process the output signal and solve a set of waveform equations that are applied to the wave source in and detector 124 of each scanning element of the scanning unit of the optical probe 120A. The solution of the result is the absolute or relative chromophore or its properties reflected in each voxel of the imaging field 2000. The image element may then, by identifying, for example, the intersection and / or overlap of two or more previous voxels, the intersecting voxels corresponding to this intersecting or overlapping voxel, and the remnants of the remainder of the corresponding voxel after being carved into the intersecting voxels Voxels, and the intersecting voxels 每个 of each intersected voxel, and another group of voxels 应用 are applied. Previously voxels 値 and intersected voxels 値 could be recombined so that chromophores or their property distribution images could be represented by voxels 値 and intersected voxels 値. Alternatively, the output signals of voxels can be averaged to produce the output signal of each intersecting body, and then processed by the image element to generate intersecting voxels 値, instead of calculating · voxels 値 and then averaging this to obtain each intersecting body Intersecting voxels of voxels. In general, the structure of a voxel can be determined by various factors, such as the number of wave sources and detectors defining each scanning element and / or scanning unit, and the generality of the wave source and detector of each scanning element and / or scanning unit. Configuration, _ -67- This paper size applies to China National Standard (CNS) A4 (210 X 297 mm)

Binding

Line 588158 V. Description of the invention (65 The geometric configuration of the scanning file in each scanning wave source, the transmission power of the wave source or the ',', the shooting force, the detection sensitivity of the waveform detector, etc. Therefore, when the wave sources have the same When the transmission power and the wave detector can provide the same sensitivity, the equidistant source and detector configuration of Fig. 8A defines horizontal and vertical voxels, and has substantially the same structure and the same intersected voxels in the imaging field. It is suitable for Wang to pass the voxel structure determined by, for example, the structure, configuration, and direction of the voxels, and the shape and size of their overlapping parts. Although the actual structure of the previous voxels has a fixed wave source and debt detector Large shape '] and operating characteristics and geometric configuration, but the structure of intersecting voxels can be processed by groups of wave sources and detectors (ie, defining scanning elements and / or units) and groups of scanning elements (ie, defining scanning units) In other words, the shape and size of the intersecting voxels can be adjusted, and the resulting image resolution can be applied to the output signal group according to the selected pattern, and applied to the solution. Scanning element and / or scanning unit waveform equation processing without changing the actual configuration of the wave source and detector. Because & the optical probe can define the main scanning unit 70 and the auxiliary scanning unit, and generate the main and Auxiliary output of k number without the need to implement additional optical sensors to optical probes, and without actually changing the existing source-detector configuration. Figures 9 to n show additional definitions in the optical probe 120A example of Figure 2A Different scanning units, and FIG. 12 shows the result voxels, intersected voxels, and intersected voxels 获得 obtained from the voxels 値 described in FIGS. 8 to 11. FIG. Scanning unit diagram of the second group of optical probes. Fig. 9B shows the voxels and intersected voxels generated by the scanning unit, and Fig. 9C shows the voxels and intersected voxels according to the present invention. Shicai S @ 家 standard (CNS) A4 specification (2ι〇χ 297 public director) 588158

value. In this specific embodiment, the optical sensors arranged in the middle area of the optical probe can be regrouped to form four rectangular or square scanning units la, Ib, and I. , And Id. Similar to the display of Figs. 6C to 6E, the optical sensors of each of these intermediate scanning units ia, ib, ic * id can satisfy the previous symmetrical requirements of 9-2 applications. Therefore, rectangular or square voxels 205a_205d can be defined in the imaging field 200, each of which has voxels 値, ,, ", and l respectively. Because the previous intermediate voxels 205a-205d were in the imaging field 200 The middle parts intersect each other, so the image element can also define multiple rectangular or square intersected voxels 215a, leaving behind the residual truncated voxels 215b. For example, each span voxel 215a is a rectangular or square voxel 205a-205d A quarter size 'and the residual truncated voxel 215b has a half size. In addition, similar to the specific embodiment shown in Figs. 8A and 8B, the intersecting voxels 矩形 of a rectangular or square intersecting voxel 215 are permeable to both voxels. Decided, that is, their original voxel 値 and an adjacent voxel 値. Therefore, the optical probe 120A of FIG. 9A can provide a higher-resolution image in the middle part of the image field 200. It can be understood that the image field 200 The four corners 215c cannot pass voxels 値 or intersected voxels 値, because the scanning units 204d_205d do not cover this area. Fig. 10A is a third group of optical probe scanning unit diagrams of Fig. 2A according to the present invention. Fig. 10B is a perspective view l〇 The voxel and intersected voxel 値 schema generated by the A scanning unit, and FIG. 10C is another diagram showing the voxel and intersected voxel results 图 of FIG. 10B according to the present invention. In this specific embodiment, optical Probe 120A (or its imaging element) can be synchronized with the wave source and detector, and defines 4 diamond-shaped units Ca, Cb, C., and Cd. Note that these diamond-shaped scanning units are tilted 45 corresponding to Figures 6C to 6E 。Rectangle or square scan sheet ___- 69- This paper size applies to Chinese National Standard (CNS) A4 specification (210X 297 mm) 588158 A7 ____ _B7 V. Description of the invention (67) yuan. Although each diamond scan unit only Including optical sensors arranged in the four corners of the diamond area, and its middle part does not include any wave source or detector, but the media target area of this middle part corresponding to the image area 200 can still be illuminated by the wave source 122, And scan through each scan element of each rhombus: Therefore, the rhombus scan units Ca, G, and Cd can define a cross-shaped voxel 206a-206d, each of which has 4 tips connected to a central area ,and· Each voxel 値 that can pass Ca ·,%, h, and Cd, respectively. Each of these rhombic scanning units is a step closer and two adjacent scanning units, thereby forming an intersected voxel 216a, and as Figures 10b and 10C leave the residual, non-intersecting tip of the original voxel 216b. It can be understood that, compared to those of Figures 8 and 9, the intersecting voxels 216a of all intersecting voxels 216a of this embodiment 値It can be determined by the voxels of three crossed cross-shaped voxels, that is, his own body voxel plus two additional voxels of adjacent cross-shaped voxels. As a result, the intersected voxel 216a of FIG. 10C can provide higher than the figure 80 and 9 (: resolution images. In addition, similar to the rectangular or square scanning units Ia, lb, Ic, and Id of FIG. 9A, the diamond scanning units ca, Cb, Cc, and Cd will not scan the four corners 216c of the image area 200, so this area is not provided Voxels 値 or intersected voxels 値. In this article, the diamond scan units Dk, 4, cc, and cd are defined as intersecting voxels 216a with the same definition as the -intermediate scanning units Ia, Ib, Ic, and 14, but the intersecting voxels 値 can pass through three intersecting Voxel 値 decides instead of 2 intersected voxels 値. Fig. 11A shows the scanning unit diagram of the fourth group of optical probes according to the present invention, and Fig. 2 A 0¾-the fourth group. FIG. 11B shows the voxel and intersected voxel patterns generated by the scanning unit of FIG. Ha, and FIG. 11C is a graph according to the present invention. ____ -70- This paper is a standard SS Home Standard (CNS) A4 specification (210X 297 mm) 588158 A7 B7 V. Description of the invention (68) Another diagram of the result 値 and intersected voxels 値. In this specific embodiment, the wave source and the detector can be regrouped to define four other diamond-shaped scanning units Da, Db, Dc, and Dd which are the same as Ca, Cb, Cc, and Cd in FIG. 10A. However, the configuration of the imaging element of the optical probe 120A or the optical imaging system is to define diamond voxels 207a-207d, each of which intersects the other three scanning units. Therefore, the diamond scanning units Da, Db, Dc, and Dd define 9 smaller diamond-shaped intersecting voxels 217a-217c in the middle part of the image field 200, and leave 4 near the corner of the image field 200 as shown in FIGS. 11B and 11C. A truncated voxel of 216d. In general, all intersected voxels 217a-217c have the same shape and size. However, it can be understood that the intersecting voxel 値 of the intersecting voxel 217c can be calculated from the voxels 所有 of all four diamond voxels 207a-207d, and the intersecting voxel of the intersecting voxel 217a and the intersecting voxel 217b can be calculated. Determined by 2 and 3 voxels of neighboring voxels, respectively. As such, the optical probe 120A of FIG. 11A can provide an image in which the resolution is gradually increased concentrically from the outside to the middle portion. Like the scanning units of FIGS. 9A and 10A, the diamond scanning units Da, Db, Dc, and Dd do not scan the four triangular corners 217c of the image field 200. As discussed above, the number of wave sources and detectors included in each scanning unit and general configuration does not require the shape and size configuration of the voxels and intersected voxels, and the resulting image resolution. In contrast, the estimation, accuracy, and image resolution of the chromophore properties can be improved by processing the group patterns of the output signal. For example, the imaging element of the optical probe or optical imaging system of the present invention may be combined into one or more of the previous auxiliary scanning units of FIGS. 9 to 11 using the main scanning unit of FIG. 8A. This specific embodiment is usually best when it is desired to obtain a higher resolution which will be discussed in detail below. Figure 12 shows the paper size according to the present invention. -71-This paper size applies the Chinese National Standard (CNS) A4 specification (210X297 mm).

Line 588158 A7 B7 V. Description of the invention (69) The result voxel and intersected voxel patterns obtained by implementing the auxiliary scanning units of FIGS. 9 to 11 into those of FIG. 8. As shown in Figure U, each quadrant of the image field 200 includes 15 intersected voxels and / or residual voxels. Because the symmetrical composition of all previous voxels and intersected voxels is related to the middle of the imaging field 2000, only these images in the imaging field 2000 first quadrant 201 can be analyzed into 200 images in the entire imaging field 200 Representative example. For the purpose of illustration, the first quadrant 201 can be further divided into 4 sub-quadrants 201ae-; 201d, of which a first sub-quadrant 201a has 5 intersecting voxels (A to E);-the second sub-quadrant 201b includes 4 intersecting voxels (Ρ, j, η, and L); a third sub-quadrant 201c has another 4 intersecting voxels (G, I, K, and M); and a fourth sub-quadrant 201d includes 1 intersecting voxel (n) , And a truncated background voxel (0). % Because all 4 sub-quadrants 201a-201d have the same area in the imaging area 200, the image resolution of 20a-20d in each sub-quadrant is expected to be related to the number of intersected voxels and used to determine the intersected voxels. The number of voxels 値 is proportional. Therefore, the sub-quadrant 201a has the highest resolution, and the sub-quadrant 201d has the lowest resolution. This result is on the table! Each of the listed voxels 値 can be used to calculate each intersected voxel of the first quadrant 201. Table 1 Intersecting voxels number 11 10 Voxels 値, A vc, hb, ia, ", ca, cb 'cc, da, db, dc, dd B vc, hb, ia,", ca, cb, cc, da , Db, dc C vc, hb, ia, ", ca, cb, cc, da, db D vc, hb, ia, ib, ca, cb, cc, db, dc

588158 A7 _______B7 V. Description of the invention (70) " " " --- E vc, hb, ia, ib, Ca, &, ^ & 8 F vc, ha, ia, Cb, da, db 6 G Vd, hb, ib, Cb, db, ^ 6 Η vc, ha, ia, Cb, db 5 I Vd, hb, ", cb, db 5 J vc ,, ia, Cb 4 K Vd, hb," , Cb 4 L Vd, ha, ia, cb 4 Μ Vd, hb, ib, cb 4 N Vd, ha, db 3 0 Vd, ha As listed in Table 1, each intersected voxel 値 can be multiplied from 2 Voxels (for pentagons, corner-intersecting voxels, 〇 "), 3 voxels (for adjacent triangle corner-intersecting voxels "N,"), and up to 10 voxels (for diamond-intersecting voxels ”B "), with 11 voxels (for the intersecting voxels of the middle triangle " a "). The results indicate that the estimated accuracy of the chromophore properties and the image resolution can be processed by processing the group pattern of the wave source and the filter and The group pattern generated by this waveform detector is adjusted. Similarly, the estimated accuracy of the chromophore properties and the image resolution can be controlled by controlling the number of auxiliary scanning units combined with the main scanning unit. For example, the auxiliary scanning army element with a preselected group can be compared with the main scanning unit of FIG. 8 and the mouth. This selection can be coded, so an operator can choose one of these predetermined combinations to Generates various image resolutions and / or adjusts the image resolution near the special area of the target area. It can be understood that at -73- this paper size is suitable for 8 S household materials (CNS) M specifications (inflated 297 public love y 588158 A7 B7 V. Description of the invention (71) All intersecting voxels a to e in the first sub-quadrant 201a can be estimated by the same number of voxels 値 (ie, 7 voxels), instead of the figure n] B and 11C. The voxels 値 (da, db, dc, and dd) of the diamond voxel, thereby producing the same resolution. The previous scanning elements and scanning units of the optical probe and optical imaging system of the present invention can be modified to provide different sources- Detector configuration and / or construction of the optical probe without departing from the scope of the present invention. As briefly described above, a single wave source may include two or more waveform generators, and therefore includes multiple waveform generators (hereinafter referred to as &Quot; Mixed wave source can be irradiated There are, for example, electromagnetic waves with different waveform characteristics at two different wavelengths. This mixed wave source can be applied to any of the previous source-detector configurations. For example, in FIG. 6B, the wave sources Sab and k of the scanning unit H (can be configured to The irradiator has near-infrared electromagnetic waves with wavelengths of 690 nm and 830 nm, thereby allowing a single scanning unit to generate at least two output signals to represent different optical exposures of chromophores with different electromagnetic waves. This synthetic wave source can also be used to provide a scanning unit that still meets the patented, 972 symmetrical requirements. 13A to 13C are specific embodiments of this scanning unit. Fig. 13A is a symmetrical scan according to the present invention that can satisfy the patent, 972 symmetrical requirements, a specific embodiment of the unit ... Asymmetric scanning single recognition includes two waveform detections Daa, and Dac, and a synthetic wave source Sab is inserted in between . : Skin shape: = a: Da. It is arranged at both ends of the scanning unit ，, and the wave source ab 疋 is arranged at the center, but it is moved away from the central part of the scanning unit \, so that the distance between the waveform detector Daa and the synthetic wave source s: b is one-to-one. —The first distance between the waveform generator and the waveform detector Daa—the short distance and the second distance between a second wave generator and the waveform picker -74- CNS) A4 specification (21GX297 public love) V. Description of the invention (72) The distance between the two-ground two-wave detector Dac and the synthetic waveform source Sab = phase s between the one-waveform generator and the waveform detector Dac One of the first, the distance and-the second between the second waveform generator and the waveform detector ~: two, away. In this way, the asymmetric scanning unit Aa can satisfy the non-description of the patent. 972 = it is another that according to the present invention can meet the needs of symmetry-'where-the second asymmetric scanning unit ~ includes two'ac, and a synthetic waveform detection The Dab is inserted in between. In a specific embodiment, the waveform detector ~ can detect Saa and ja from two wave sources. The emitted electromagnetic waves can meet the needs of symmetry.

As shown in Figures 13A and 13B, the first three sensor $ configurations are not as good as the above 4, and the sensor configuration is valid. For example, a scanning unit configured with 3 sensors can scan the target area without overlapping any areas. Therefore, this unit can be generated in the incorrect evaluation of the chromophore properties and finally a lower resolution image. However, through By combining the wave source and the detector to form a 3 and / or 4 sensor wave source-detector configuration, this disadvantage can be avoided. Figure 13C shows that a variety of different 3 and or 4 sensor wave source-detection can be used. Scanning unit diagram of the detector. The optical probe ⑽ includes 2 wave sources Sab !: i waveform detectors Daa, ~, and, and defines 2 non -... '% early 7L Ac and Ad, Two of the three sensor scanning units can be the ugly waveform detector Dac. It can be understood that the composition of the wave sources ^ and ^ and the wave ㈣ d states Daa and Dae can also define a symmetrical scanning unit. As described above, the optical detection of the present invention Rod and Optical Imaging System-Multipurpose 'to define symmetric or asymmetric primary and secondary scanning units. Configurations of previous scanning units described in Figures 6A to 6H, Figures 7 to 7 (:, and Figures to 2) Optical probes with various shapes and sizes can also be produced. Figure 14A is the root The circular optics of an optical imaging system of the present invention-75- The paper ruler M B g mound material (CNS) A4 "(2iq χ tear public love) 588158 A7 —_________ B7 V. Description of the invention (73) The wave source and the detector are arranged on a circular scanning surface. However, FIG. 14 is another triangular optical probe diagram of the optical imaging system according to the present invention, in which the sensor is disposed on the triangular scanning surface. 14A-the circular% detection probe 14G includes $ wave sources A to S9) and 20 waveform detectors and detectors D1 to Di6) on a circular sweep surface. — The image element can be composed of these sensors, and various scanning units are defined, which are due to the required resolution. For example, the material element & defines a linear scanning unit (such as SrDrDA, S5-D9-D10-S6, Sl-D3-D14-S9, Sl-D5-D12, heart, S ^ Du-D ^ -S7, etc.), Rectangular and / or trapezoidal scanning unit (e.g., S2-D3.S5.D7 > S2.S3.D10.D7 > S ^ D.-D ^ s, > S ^ D ^ -Ss > Sl-D2 -D13-S8, SrDu-DwSg, SrDrDu-S #), etc. In addition, the asymmetric scanning unit can further define the scanning surface. Similarly, a triangular-row optical probe 150 includes 6 wave sources ⑸ to the heart) and 9 waveform detectors (h to D0, except for asymmetric scanning units, which can be composed of linear, similar, spring, rectangular , Square, trapezoid, or parallelogram scanning unit. Through the combination of the main scanning unit and the auxiliary scanning unit, and by processing the output signal generated by the waveform generator of this scanning unit, an optical probe or optical imaging system can provide the necessary 2D and / or 3D distribution of chromophores and / or properties of image resolution. It is clear from Figures 14A and 14B that the additional wave source and detector are arranged inside the scanning unit, where the additional wave source is not illuminated Electromagnetic waves, and the waveform detector does not generate any output signals. Although the previous disclosure of the present invention is mainly directed to the spatial distribution image of chromophore properties, the application of the optical probe and optical imaging system of the present invention can produce • 76 · This paper is compliant with the National Standard (CNS) A4 specification (21GX297 public love) 588158 A7 ----—__ B7 V. Description of the invention (74) Time distribution image For example, the configuration of the optical probe can scan the media for substantially the same target area at a certain time interval. In the same target area, the output signal difference detected at different time intervals is obtained, and the image element can calculate the Chromophore properties change temporarily and produce a time-distributed image of this property. Alternatively, temporary changes in chromophore properties can be determined, and their images can be obtained from the spatial distribution of this chromophore property in different time frames. For example, The scan of the fresh probe ^ can repeat the scan of the target area and calculate the time distribution pattern of the chromophore properties. Note that temporary changes and their sub-books are usually related to relative changes in the chromophore properties. However, as long as this chromophore The absolute value of a property can be determined in any reference time frame, and previous or subsequent changes in this property can be converted into an absolute value, and vice versa. '/ Wang Yi, the configuration of the previous optical probe and optical imaging system of the present invention can also be Temporary changes in blood or water volume in the target area of the media. Calculate the specific changes in blood volume in a human target area. In the case of oxyhemoglobin [HbO]; the degree of concentration and deoxyhemoglobin [Hb] can be calculated through one set of equations (la) and (lb) or through another set of equations (2a) and (2b). Hb] and [HbO] 'total (that is, the total haematocrit concentration [HbT], which is the sum of [Hb] and [HbO]) can be obtained. Obtained from a waveform detector located in the same target area By outputting the signal, the total erythropoietin concentration can be obtained. By assuming that the hematocrit inflow and outflow in the target area (ie, the percentage of red blood cells in the blood) is maintained at a fixed level, the blood volume in the target area is temporarily The change can be calculated directly from the viewpoint of 1HbT] temporary change in the target area. Alternatively, the temporary change of [Hb] and [HbO] can be calculated from equations (6a) and (6b), and the temporary change of [HbT] can then be as In the target-77-i paper scale SS Home Standard (CNS) A4 specification (210X297 public love) '588158 A7 B7 V. Description of the invention (obtained from the sum of [Hb] and [HbO] changes in 75 areas. It can be understood that the optical probe and optical imaging system of the present invention can be used to obtain a three-dimensionally divided image of the chromophore properties in the target area of the media. As mentioned above, the electromagnetic wave can be irradiated to the media through the wave source, and can be transmitted through a target volume defined by a target area and a predetermined thickness (or depth). A set of waveform equations can be formulated in this three-dimensional target volume, and the output signal generated by the waveform detector can be provided to the image element, which can then use the relevant initial and / or boundary conditions to solve the waveform equation. This solution is a two-dimensional distribution of chromophore concentrations representing the target volume of the media. To maintain the pre-selected resolution of the image, the optical image probe and / or system preferably includes a large number of wave sources and detectors to define a large number of voxels in the target area of the media. It is assumed that an optical probe and an optical imaging system include two wave sources and four waveform detectors, and can generate a two-dimensional image of a target area with a preselected resolution. When the definition of a target volume has the same target area and a preselected thickness including N two-dimensional layers stacked on each other, the optical imaging system needs to include about 2N wave sources and 4N waveform detectors. The same resolution for each two-dimensional layer. However, the number of this wave source and detector can be reduced by generating sufficient auxiliary scans in the target area, and it is better to overlap each other. In this way, the optical probe and the optical imaging system define and combine a sufficient number of auxiliary scanning units through configuration and image elements, and a small number of wave sources and detectors may be required. Note, however, that the image resolution from any optical imaging system is essentially limited by the average photon " free walking distance " of a typical physiological medium of about 1 mm. In addition, due to the existence of spirit in almost any optical imaging system -78- This paper size is applicable to China National Standard (CNS) A4 (210 X 297 public love)

Order

Green 588158 5. Description of the invention (76) Sensitivity limitation, or electrical and mechanical noise, the best resolution of the image can be in the range of several millimeters or about 1¾ to 5¾ meters. In this way, the previous voxel and the intersected voxel have a size of less than 1 mm to 5 mm, and more specifically, about 1 mm does not require a final image to improve the resolution. The prior optical imaging system and optical probe of the present invention can be used to determine the intensity properties of the chromophore, such as the concentration, the sum of the concentrations, and / or the concentration ratio. Previous optical imaging systems and optical probes can also be used to estimate chromophore properties, such as volume, mass, weight, volumetric flow rate, and mass flow rate. It can be understood that the adjustment of previous optical imaging systems, optical probes, and methods can provide distribution images of different chromophores or properties. Because different chromophores usually respond to electromagnetic waves with different wavelengths, the wave source processing of this optical imaging system and probe can radiate electromagnetic waves that can interact with a preselected chromophore. For example, a near-infrared wave having a wavelength between 600 nm and 1,000 nm, such as about 690 nm and 8300 μm, may be suitable for measuring the distribution pattern of heme and its properties. However, a near-infrared wave having a wavelength between 800 nm and 1,000 nm, such as about 900 nm, can also be used to measure the moisture distribution pattern of a medium. An ideal wavelength selection for detecting a particular chromophore is usually determined by the optical absorption and / or diffusion properties of the chromophore and the source and / or detector operating characteristics. The previous optical imaging system, optical probe, and method of the present invention can be used clinically to detect tumors and pulsations in the human chest, brain, and any other part of the human body, such as the previous optical images of diffuse optical local x-ray examination The method is applicable. Previous optical imaging systems and methods can also be applied

588158 A7 B7 V. Description of the invention (77) It is used to evaluate the blood flow in or out of the converted organ or limb, and / or automatically recorded or allografted body part or tissue. The configuration of previous optical imaging systems and methods can replace, for example, ultrasound, X-ray, EEG, and laser sound diagnostics. In addition, the modification of this optical imaging system and method can be adapted to physiological media with complex photon diffusion phenomena and / or non-flat outer surfaces. Examples The following examples describe the simulation and ten-point results obtained through optical systems and methods according to the present invention. All simulation and experimental results indicate that the optical system and method can provide correct prediction and / or measurement of heme concentration and oxygen saturation. Example 1 The diffusion equation (3b) can count the optical proof of multiple wave sources and detectors with various configurations. These equations can be applied to a sample of physiological media, such as semi-infinite, homogeneous diffusion media with different background optical properties. The diffuse reflection coefficient can be based on an image source method disclosed by RC Haskell et al. In the name of the Journal of Optical Society of America, Vol. 11, page 2727-2741, 1994 " Boundary conditions for the diffusion equation in radiative transfer " And the calculation. G (that is, sturdy at different wavelengths? ^ And [~ 2 ratio) of 値 are evaluated at different levels of oxygen saturation (S02) and conform to polynomials. G plot of the oxygen saturation (S02) function. As shown in the figure, all simulation results show a one-to-one relationship between G and oxygen saturation (S02). In addition, all the diagrams show that as long as the oxygen saturation is substantially the same for the simulated wave source -G relationship between the detector structure and the background optical properties is not sensitive. -80 · This paper size applies the Chinese National Standard (CNS) A4 specification (21〇 × 297 mm)

Order

Line 588158 A7 B7 V. Description of the invention (78) The traditional curve fitting method such as the least square root method can be used to evaluate the coefficients of the polynomial equation (10) (that is, a0, q, α3 ·). For example, after obtaining the polynomial equation, a system can reduce the spreading coefficient and the total red blood cell concentration of 10-4 mol per liter by irradiating electromagnetic waves with wavelengths of 780 nm and 830 nm with a background of 10 cm · 1. Satisfy the relationship between G and oxygen saturation (S〇2): ph \; G-= ° · 728 + · S02 + 0.Q64 · SO ^ + 〇〇〇〇〇〇〇〇〇 〇 S〇l; (18) A .j • i Example 2! Further simulations can be performed in a system with a background dispersion coefficient of 7 cm · 1 and a total red blood cell concentration of 2 x 10 4 mol per liter. In the simulation, the oxygen saturation (S02) can be changed from 0 to 100%. Fig. 18 is a graph comparing the calculated oxygen saturation with the actual oxygen saturation. Although the background properties used to find the relationship between G and oxygen saturation are quite different, the estimated oxygen concentration is correct with a few percent systematic errors. Example 3 An optical system can be calibrated, and red blood cell concentration and oxygen saturation can be monitored before and after occlusion of a human limb artery. In this example, the optical system of FIG. 3A is used. The two-wave source and two-waveform detectors arranged in a linear manner are used. The two-waveform detectors are linearly arranged and spaced 6 mm apart. The two wave sources are arranged outside each waveform detector, so the left wave source is arranged to the left of the left waveform detector at a distance of 9 mm, and the right wave source is arranged to the right of the right waveform detector at a distance of 9 mm. . Therefore, each pair of wave source and detector have the same close and long distances. _ -81-^ The paper size applies the Zhongguanjia Standard (CNS) A4 specification (21GX 297 mm) — --- 588158 A7 B7 [Hb] 5. Description of the invention (79) The wave source has an external diameter of 2 mm, and Includes laser diodes (models HL6738MG and HL8325G, both available from Thorlabs Inc., Newton, NJ) for irradiating electromagnetic waves with wavelengths of 690 nm and 830 nm, respectively. The light detector (model OPT202, available from Barr-Brown, Tucson, AZ) can be used as waveform detection. A reversed part is placed near the upper arm, and the optical probe is placed on the forearm. After the object stabilizes, the pressure in the reflex section will increase to about 160 mmHg in about 35 seconds, and maintain the same level for about 40 seconds, and then return to the atmospheric pressure level. The absolute concentrations of total heme, oxyhemoglobin, and deoxyhemoglobin can be monitored, and oxygen saturation can be calculated. FIG. 19 is a time curve diagram of total hemoglobin [HbT] concentration, oxyhemoglobin [HbO] concentration, and deoxyhemoglobin [Hb] concentration according to the present invention, and FIG. 20 is a time zone of oxygen saturation according to the present invention Graph. As shown in the figure, erythropoietin concentration and oxygen saturation decrease significantly during the occlusion initiation phase. After release, the concentration and oxygen saturation show a rapid increase. These results indicate that the optical system and method according to the present invention can provide a correct prediction of erythrocyte concentration and oxygen saturation. These results also show that proper response characteristics are held. Further specific embodiments using the above solution method. For example, after the above method, the concentration of deoxyred · hemoglobin [Hb], the concentration of oxyhemoglobin [HbO], and oxygen saturation S02 can be transmitted through the following equations (8a) to (8d) And 9 (b) obtained: ~ • (8a) -82- This paper size applies to China National Standard (CNS) A4 (210 x 297 mm) binding

A7 B7 V. Description of the invention (80) 0Dh II

^ ODM iHb0 > = (5j'lZ) jiiljW-^ s \ d \ ^ sid \ ~ Fk = (Bl ^ DlL ^ Dl-^ l ^ l ^ sipr) ^ (^ ΙϋΐΑνίΙ »! ^ ^ S \ Dl ^ SlD2 ) 〇〇2 h OD ^ FM εια QDXi pM ^ (^ / Λ-€ Hb〇) 0Dh F ^ 〇DXi ~ Gui): _: (8c): (8d) (9b) where the parameters "sHb" and " sHb. " Represents the dissipation coefficients of deoxygenated and oxyhemoglobin concentrations, respectively, and the variable “NOD” is an optical density defined as the logarithmic ratio of the light intensity (ie, the magnitude and amplitude of the electromagnetic wave) detected by a waveform detector. The parameter "B" is traditionally known as a path length factor. The parameter "LsiDj" is a distance between the i-th wave source and the j-th waveform detector, and the superscripts "quote and πλ2" are A system parameter or variable obtained by irradiation with an electromagnetic wave having a wavelength of λ2. Alternatively, the logarithmic unit or image construction unit of the image unit may use an iterative method such as the one disclosed in the previous patent 472, where [Hb], [HbO ], And S02's absolute 値 can be determined by the following equations (17a) to (17c), each of which is the corresponding equation (17a) to (17c) of the patent W72: [Rib 1: (17a) Γ rrun] — ^ «(17b) SO, [HbO] (17c) ㈣ 十 [Remaining Yin '¥:) Shibu > Buru) • 83 · This paper size applies Chinese National Standard (CNS) A4 (210X297 mm) 588158 A7 B7 V. Description of the invention (81 where parameter & qu ot; μ / represents an absorption coefficient of the media. Note that the image element configuration of the present invention can receive the output signal generated by the waveform detector and calculate the optical density to provide the algorithm unit or the image construction unit. As long as the red blood cells The absolute concentration of the element concentration or its change is determinable, and the image element can be discussed in detail by using the following (also applied for US Patent No. (unknown) name of "Optical Imaging Systems for Direct Image Construction" on February 5, 2001) ··, which is only listed here for reference), a real-time image construction technique to generate a two-dimensional or three-dimensional spatial and / or temporal distribution image representing red blood cells. Alternatively, changes in red blood cell distribution can be transmitted through the target area of the media. It is determined by the evaluation of changes in optical properties. For example, the changes in oxygen and deoxyhemoglobin concentrations can be calculated from the apparent coefficient difference measured through electromagnetic waves with two different wavelengths. In a numerical method, the photon diffusion equation can be applied by, for example, applying Keijer and others published the name " Optical Diffusion in Layered Media ··, App Lied Optics, Book 27, pages 1820-1824 (1988) and the names published by Haskell et al. " Boundary Conditions for Diffusion Equation in Radiative Transfer ', Journal of Optical Society of America, A, Book 11, Book 2727 The diffusion approximation disclosed in -2741 (1994) was modified and resolved. Binding

k Zhong Ji (Γ, rov)

(19) where the symbol "〇SC (Isi, Idj)" represents a response to an i-th wave source and passes through a j-84- This paper standard applies the Chinese National Standard (CNS ) A4 specification (210X 297 mm) View 158, invention description (===: quantity—normal optical density, variable, " and points such as in the -shape detection position, the symbol " Δ ~ " is The table shows the optical tissue replacement and the N " of the tissue of the prime factor, which are the number of measurements and the reconstructed voxels, respectively. Second, it represents the weighting of a photon from the first wave source to the media target.器 器 测试。 方 _ ^^ γ:! (2〇) where the parameter "h3" is the volume of an integrin, "Dph_" represents a photon diffusion coefficient and V represents the speed of light of a physiological medium. In addition, the variable " 〇sc (rsi, rdj ·) " is a normal optical density, which is expressed as follows: Λ # ι) where the variable " Γ represents the output signal measured by the sensor component, which is an i-th wave source And j-th waveform detector, and are respectively arranged at the positions " rsi, and " rDj ", and change &Quot; Ib ,, baseline represents a signal output by the waveform detector is determined. For example, various methods of direct matrix inversion and simultaneous iteration and reconstruction techniques can be used to solve the above set of equations (19) to (21). As long as the tissue optical disturbances " Δμ ^ " and " Δμλν, by irradiating electromagnetic waves with two different wavelengths λ2 respectively, the changes in the concentration of oxyhemoglobin and deoxyhemoglobin can be obtained as follows: 85 This paper scale applies Chinese national standards (CNS) Α4 size (210 X 297 mm) 588158 A7

: \ (22a) • · ϋ.: This): ·: ϋ • · ί ·. • • where L is the distance between the wave source and the detector, and the parameters ελ1 λ2 Wb Ν ε 2Hb, SUHb0, and SX1Hb O is the dissipation coefficient of oxyhemoglobin and deoxyhemoglobin at two different wavelengths M and λ2, respectively. Incorporating the previous solution of the patent '972 into the optical imaging system of the present invention provides additional advantages over prior art optical I imaging techniques. Compared to cws, which allows measurement of changes in the concentration of erythrocytes or chromophores, previous optical imaging systems can provide a direct device to evaluate the absolute or spatial distribution of temporary changes in the properties of erythrocytes or chromophores in physiological media Allows physicians to make a direct diagnosis based on the absolute nature of red blood cells or chromophores. In addition, as described in detail below, previous optical imaging systems can be combined with traditional optical imaging systems and their optical probes. The optical imaging system can include any number of wave sources and / or detectors in almost any structure. Therefore, the use of the specific embodiments of the present invention discussed herein can constitute an optical imaging system, and can be adapted for special clinical applications without compromising their efficiency characteristics. The optical imaging system of the present invention can obtain multiple waveform equations by using one of the solutions disclosed in Patent, 972, and can determine the absolute or relative chirp of the chromophore properties. Therefore, in terms of satisfying the patent, 972, the operating characteristics of this optical imaging system are generally not affected by the wave source and / or the detector.

Order

line

V. Description of the invention (84) Influence of actual structure. In this way, the optical imaging system of the present invention can include any number of wave sources and / or detectors configured in almost any structure, and meets the previous symmetrical requirements. However, the sensor assembly or scanning unit of the present invention may be constructed according to some semi-empirical rules that are expected to provide an absolute or relative assessment of the chromophore properties to improve accuracy, credibility, and / or reproducibility. use. The design rules for this example are: (丨) each scanning unit may include at least two wave sources and at least two wave detectors; and (2) the distance between the wave source and the detector will not exceed one face of the wave detector i 'Sensitive range' can range from, for example, a few centimeters to 10 centimeters, or especially about 5 centimeters for human and animal tissues. Figures 4 and 5 illustrate some specific embodiments of the scanning unit according to previous design rules. Fig. 4 is a sectional top view of a movable element and a scanning unit according to the present invention. Compared to a conventional wave source-detector configuration in which each wave source is surrounded by a multiple waveform detector, or vice versa, the scanning unit 125 in FIG. 4 is defined by two wave sources 122 (that is, heart and so, Each of them is configured along the vertical axis 127. The scanning unit 125 may further include two waveform detectors 124 (ie, Di and D2), which are inserted between the two wave sources 122 along the same pumping 127, and are They are separated by substantially equal distances. Therefore, the scanning unit I25 defines a scanning area extending along the same axis 127, and has a characteristic that can pass through, for example, the irradiating ability or radiation power of the wave source 122, the waveform detector 124 A characteristic determined by the sensitivity or detection range, the optical characteristics of the media, etc. It can be understood that 'the scanning unit 125 in FIG. 4 can meet the patent, and the symmetrical requirements of 972', that is, the configuration of the wave source and the detector can be in the movable element And / or the scanning unit maintains substantially the same near and long distances during its movement. For example, at 87- ^ 8158 A7

line

Order

588158 A7 B7 V. Description of the invention (86) Top view. The scanning unit 125 includes two wave sources 122 ^ [and SO, which are arranged along the vertical axis 127, and four waveform detectors 124 (0! To 〇4), each of which is inserted between the two wave sources 122 And are aligned along the same axis 127 at substantially equal distances. An aspect of the embodiment of FIG. 5 is different from that of FIG. 4. First, the scanning unit 125 of FIG. 5 does not necessarily have to satisfy the near and long distance structures of FIG. 4. For example, although the first and fourth waveform detectors (] 〇1 and d4) and the second and second waveform detectors (Da and Ds) can meet the symmetrical requirements of the patent, 972, but near and far The distance is different from the first and third waveform detectors (Di and D3) and the second and fourth waveform detectors ⑺2 and DO. In addition, the banana-shaped path of the electromagnetic wave (refer to the figure) also reveals that each pair of the wave source 122 and the detector 124 cover different parts of the target area. Therefore, the output can be generated by absorbing and diffusing electromagnetic waves on different extensions of different parts of the media signal. However, by inserting all four waveform detectors 124 equidistantly between the two wave sources 122, the entire target area of the media can be substantially consistent by the source-detector component of FIG. 5 along the thickness and / or depth of the media. Covered. Therefore, the scanning unit 125 of FIG. 5 can also provide a fairly consistent coverage of the media over the entire scanning area or scanning volume. In addition, the scanning unit 125 of FIG. 5 can provide a longer scanning area because it includes more waveform detectors 124. Therefore, it can extend beyond the one of FIG. 4 along the axis 127 and can cover a longer , And the target area for each measurement may be wider. Therefore, an abnormality of the media can be more easily detected by using the longer scanning unit 125 by comparing the output signal generated by the waveform detector 124, and the waveform detector can cover a longer or wider Scanning area. As shown in example H, a sudden increase or decrease in the output signal indicates, for example, that there is a larger or smaller dissipation or absorption system.

= The tumor abnormality will exist by extending the scanning area or _ along with a pair of waves that are responsible for outputting the signal. In addition, the output signal generated by the scanning unit 125 covers a longer and wider scanning area, and the image element 14G can provide an output signal-a more reliable baseline. Therefore, a more reliable self-calibration of the output signal can be performed. Details of this self-calibration procedure are provided below in Figure 45C. Changes in Specific Embodiments The modification of the configuration of the mouth wave source-detector can also provide a scanning unit with a different structure without deviating from the present invention. For example, the scanning unit may include three wave sources (or detectors), and at least two or all of the wave sources (or detectors) may be arranged substantially linearly along the longitudinal axis of the scanning unit. The waveform detector (or wave source) can be further inserted between two or more wave sources (or detectors) along the same axis of the scanning unit or along the longitudinal axis of the movable element. Alternatively, the scanning f element may include at least two wave sources (or detectors), where the first wave source (or detection device) is arranged at one end on the axis of the scanning unit, and the second wave source (or detector) is symmetrical The arrangement is related to the axis of the scanning unit or the vertical axis of the movable element, or also to the point of symmetry in the scanning unit. In another aspect of the invention, an optical imaging system includes at least one wave source and at least one waveform detector, each of which is associated with a subject in a fixed or mobile configuration. The configuration of this optical imaging system may be substantially similar to FIG. 1, for example, it includes a previous main body 110, at least one sensor component (corresponding to the figure 丨. Movable element 12) including at least one wave source 122 and at least one waveform detector 124 ); An exciter element 130 for generating at least one of the previous movements of at least one of the subject ι10 and the movable element 120 related to the target area; and -90- this paper size applies Chinese national standards ( CNS) A4 specification (210X 297 mm) 588158 The invention describes an image element 140 for receiving signals from the sensor assembly 120 and for generating chromophore properties and / or distribution images. Excitation In a specific embodiment, the movement of the main body configuration is related to the target area, and the sensor assembly is fixedly coupled to a scanning surface of the main body. Because the wave source and the detector are fixedly coupled to the main body, and a fixed geometric configuration is maintained therebetween, the exciter element can move the main body, so that a single movement of the main body can cause the sensor assembly and the main body to move together. This embodiment is useful for achieving a simple mechanical structure and lifting mechanical support through a fixed coupling between the sensor assembly and the main body. In another specific embodiment, the exciter element can generate individual movements of the sensor assembly and the main body, so when he is moved with the target area, the sensor, the motion and the movement of each of the main body Is related to the other. Despite the complex design and control needs, this embodiment has the advantage of providing a fixed and changeable sensor component that can move along the sensor component and / or the body curve while elastically scanning different parts of the target area. Other specific embodiments of the previous optical imaging system can also be applied to the idea of the present invention of FIG. 4. For example, the exciter element may produce one or more races continuously, intermittently, or periodically. The exciter element can also produce this movement at a fixed or varying speed in time and / or position in the target area. Alternatively, the configuration of the exciter elements may further result in simultaneous or continuous movement. The use of a connector is still another aspect of the present invention. The optical imaging system includes at least one of the previous wave sources, at least one of the previous wave detectors, and a laser-91-t paper scale suitable for money @ 目Home Standard (CNS) A4 Specification (210 X 297 Public Love) '--------

Binding

Line A7

Lai Kung 7C, including at least one movable element (per * turn, a hot rod, a console to sister), and-connector element. In general, the exciter; less: a curved path produces a wave source, a waveform detector, and / or movable: occasionally_moves. The connector element can communicate with the optical probe and the console in various ways. For example, the 'connector element includes a power cord and /-^ in order to transmit power and; or to transmit analog or digital data. The connection 2 includes, for example, an optical link for a fiber optic product to transmit% magnetic waves or optical signals between the probe and the control. In addition, the connector element can provide mechanical support between the probe / felt table, or through a power transmission channel such as a flexible power cord or universal connector, the conversion, rotation, rotation, Or the reciprocating power can be transmitted to the movable element. In a specific embodiment, the movable element of the optical probe includes at least one of a wave source and a detector. Power can be supplied through an internal power mechanism of the optical probe, or from a console via connector components. The exciter element can be implemented or configured in the optical probe to move at least one of the wave source and the detector, or in the console, where the power for conversion, rotation, rotation, or reciprocation is transmitted to the movable through the connector element element. Similarly, some or all of the image elements can be placed on one of the optical probe and the console. In another specific embodiment, the console includes at least one of the wave sources and at least one of the waveform detectors. The movable element of the optical probe includes a minimum of instruments, and only allows the movable element to receive electromagnetic waves from the source of the console, and transmits this electromagnetic wave to the target area of the media, and the movable element can detect the electromagnetic waves from the target area, and the aforementioned Electromagnetic wave-92- This paper size is in accordance with Chinese National Standard (CNS) A4 specification (210X297 mm) 588158 A7 B7 V. Description of the invention (90)-The waveform detector transmitted to the console. In a specific embodiment, the movable element 定义 defines two gaps on its scanning surface. A first optical fiber is disposed between the wave source and the first gap, and a second optical fiber is disposed between the wave detector and the second gap. By arranging the first and second gaps to form an appropriate optical coupling to the media, the target area can be scanned indirectly through a wave source and detector arranged on the console, or through the optical channels of the connector elements. Similar to the previous embodiment, the power can be provided to the optical probe through its own internal power mechanism, or from an external or main power mechanism of the console through a connector element. The exciter element may be configured on the optical probe to move at least one of the first and second gaps on different parts of the target area or on different target areas of the physiological medium. Alternatively, the exciter element can be arranged on the control table, so that a power source for conversion, rotation, rotation, and reciprocation can be generated, thereby mechanically transmitting to the movable element through the connector element. Similarly, the 'image element can be arranged in either the optical probe or the console. Selective user screen In any of the first embodiments, a selective screen can be provided to the optical probe to allow an operator to view the original image (for example, the output signal generated by the waveform detector). System variable distribution pattern image), processed image (for example, distribution pattern image obtained or processed by processing the original image), and / or final image (for example, chromophore properties and distribution image). Alternatively, when the image element is configured-at the console, the optical probe includes a data transmission unit to transmit data to the image element in real time, intermittently, and periodically. The optical probe also includes a memory unit or storage element to store various signals semi-temporally or permanently. -93- This paper size is in accordance with Chinese National Standard (CNS) A4 specification (210 X 297 mm) 588158 V. Description of the invention (91) Advantages of this change The previous embodiment of the concept of the present invention can provide more advantages than previous techniques . First, a large or heavy component such as a power supply, waveform generator (such as a lamp, laser source or driver, etc.), light detector, detector driver, and / or circuit board may be included in the console, Only the necessary components (for example, optical gap and optical fiber) are arranged in the portable probe. In this way, the :: component can maintain a small size and light weight. Second, because previous optical probing required fewer components, errors specific to component variations can also be reduced. Third, previous optical probes could be constructed with half a portable object worn by the patient to continuously or periodically monitor and form a chromophore-like image of the patient's target area. Use of Portable Probes In a further aspect of the invention, an optical imaging system includes at least a portable probe and a console (or body). The portable probe includes at least a movable element and an actuator element, both of which are the same as or substantially similar to those described above. For example, the movable element includes at least one of the previous wave source and the detector, and the exciter element can generate at least one movement of the movable element along at least one curved direction. The console configuration usually includes at least a portion of the imaging element. · '... In a specific embodiment, the operation of the optical probe and the console is connected to each other via a connector element which can provide previous communication therebetween. In another embodiment, the portable probe can be provided as a separate component that is physically separated from the console. The portable probe preferably includes at least one wave source, at least one waveform detector, such as an exciter element of a small motor assembly, and a power supply which can be provided. CNS) A4 specification (2ι〇 × 297 public director)

, ', Σ portable probe, the above-mentioned components, the probe may include an M mechanism. In addition, portable media includes-asset storage units or data ‘q for temporary storage or transfer to the console. Portable ’so it ’s a material element, so m includes — separate images

Only; the hair color 09 of the target area and its characteristic H, the quasi-original image, the processed image, or the last second best are the most powerless MU internal power supply mechanisms, and can be maintained at a predetermined time. With: =: If r is here, the portable probe can be implanted in the patient and used to monitor the images of various targets on a fixed or periodic basis. The linear configuration of the source and the detector is still another aspect of the present invention. The optical image system includes two or more wave sources and two or more waveform detectors, of which at least two wave sources and at least two waveform detectors. The device is arranged substantially linearly with a strict line by, for example, each of the wave source and the sensor. Note that the linear configuration of the wave source and the detector usually causes the scanning unit to extend substantially along a straight line, and has a scanning area that can also be extended and narrower than the target area. By allowing the exciter element to generate the wave source and / or the previous movement of the detector, the optical imaging system of the present invention allows a smaller scanning unit to scan the entire target area. Advantages of the linear configuration The previous point of view of the present invention can provide many additional advantages. Prior art optical imaging machines typically relied on a single, larger probe that could cover a target area design. Therefore, prior art probes must include a large number of wave sources and detectors distributed over the surface of the sensor. By combining a large number of wave sources and detectors, the prior art -95-

588158 A7 ------ —_B7 V. Description of Invention (93) Art and technology suffer from various disadvantages. For example, each probe is usually large and thick. Therefore, unless the configuration of the probe can match the curve of the target area, the wave source and / or detector will cause poor optical coupling with the contour target area. Even if this probe can provide a consistent surface pair, this target is a special probe Limited use can be found. In addition, the resulting output signal and the final image include a significant amount of noise that is a variation of the unique components in the sensor. In contrast, the optical image of the present invention typically includes a scanning unit with fewer sensors, many or all of which can be arranged linearly along the longitudinal axis of the scanning unit. Therefore, a slim scanning unit shaped like a narrow sensor can more easily conform to the contour of the target area. By configuring the exciter element to convert and / or rotate the scanning unit, different parts of the target area's previous optical imaging system can scan the entire scanning area using a smaller scanning unit, while maintaining a good consistent optical coupling with the target area. Previous optical imaging systems also required fewer wave sources or detectors, thereby reducing manufacturing costs and reducing noise from unique component changes. Examples of scanning units are as described above. The exciter element can generate the scanning unit to move to cover the target area of the media. The media target area is substantially larger than the scanning area of the scanning unit. Different moves. For illustrative purposes, the specific embodiment shown in FIG. 5 is the same as the scanning unit selection of FIGS. 52 to 58. Fig. 52 is a diagram of the scanning unit of Fig. 5 configured for careful switching of lines according to the present invention. As described above, the movable assembly 120 includes two wave sources 122 and four equidistant waveform detectors 24 inserted between the wave sources 122. In a preferred embodiment, the wave source 122 and the wave detector 124 are the same. As such, the scanning unit

The meaning of 125- may have a substantially extending shape and may extend along the longitudinal axis. The size of the solid body 110 is preferably slightly larger than the desired target area of the media, so the body 110 can cover the entire target area. In this specific embodiment, the main body 110 has a rectangular shape (or a square shape) and can extend the placement (ie, the length or height of the scanning unit 125) and movement of the scanning unit 125 as appropriate. For example, an exciter element of a stepping motor assembly can linearly transform the scanning unit 125 along a linear path, and the linear transformation is substantially parallel to a top end and a bottom end of the rectangular (or square) main group 110. Note that only a small part of the main body 110 may form a dead-end area or a blind spot where the scanning unit 125 cannot perform any reliable measurement. This dead-end area is usually limited to a portion adjacent to a corner or edge of the main body 11 (). The size (or width) of the dead-end area is determined by the distance between an edge of the subject and the wave source 122. Since the digestion area usually wastes the valuable area of the main body 110, it is better to reduce the size and shape of the scanning unit 125 and the curved path to the scanning unit ι25 by conforming to the shape of the main body ι10. To produce highly accurate movement of the scanning unit, the fixed body 110 may include one or more guide rails 160 defining a linear conversion path. Note that the guide rail 160 is configured in the package of the main body 110, so the provision of the guide rail 160 does not hinder the movement of the scanning unit 125 in different parts of the target area. Alternatively, the fixed body 110 may provide an obstruction 170 along the edge, so the movement of the scanning unit 125 may be limited to the area bounded by this obstruction 170-and the positioning and movement of the scanning unit beyond the obstruction 17Q may be avoided. The exciter element can linearly convert the scanning unit at a preselected speed of the conversion. Alternatively, the exciter element can provide a control characteristic, so one use -97- This paper size applies to China National Standard (CNS) A4 specification (210 X 297 mm) Invention description (95

Five (eg, a physician) can handle the movable element (or scanning unit) to move at an appropriate speed, along a desired guide, and / or to control the different curves in different scanning units. There can be a pause between movements. If other factors are the same, the speed of the scanning unit will usually affect the accuracy of the chromophore property evaluation and the resolution of the final image. Therefore, the configuration of the exciter element allows an operator to select the optimal scanning unit speed that can be determined based on several factors, including (but not limited to) the structure of the scanning unit or the movable element, the resolution of the final image, the optical The frequency response of each element of the imaging system, the optical properties of the media, the size of the target area, etc. Referring to FIG. 1 in detail, in terms of implementation, the movable element 120 is arranged at its starting position, and is usually adjacent to one end of the main body 110, such as a bottom portion 114; and one end of the package 112. The main body 110 of the optical imaging system is placed on the medium, so the scanning unit 125 of the movable element 120 is arranged in a first area of the target area to form optical coupling. The excitation energy of the wave source 122 and the detector 124 can be increased in one direction. The bottom portion H4 of the movable element 120 package 2 is substantially linearly converted to a top portion 116, and the upward direction is normally the vertical axis 127 of the movable 7L member 120. During the linear conversion upward, the scanning unit 125 can scan the target area »one area Moreover, the waveform detector 124 can generate an output bismuth number to represent the optical property, space or time distribution of the chromophore or its properties of each region of the target area. As long as the movable element 120 reaches the top portion 116 of the main body 110, The exciter element 13 can move the movable element 12 back to the starting position (ie, the bottom end portion 114) along the same path in an opposite direction. During the downward linear transition, the scanning unit 125 can pass -98 -Standards of this paper (UNS) A4 specification (2i0x297 gong) 588158 A7 B7 5. Description of the invention (96) Similar or different areas of the same target area and rescan Moreover, the waveform detector 124 can generate an output signal. After the movable element 120 completes the previous reciprocating motion of the target area, the previous scanning process can be completed. Please refer to FIG. 34, the main body 110 also includes an entire length of the package 112. A linear guide 118. The movable element 120 is arranged on the guide rail 118 'and thereby guided during the linear conversion of the movable element 120. Note that the guide rail 118 is arranged in the package 112, so the provision of the guide rail iis will not hinder The scanning unit 12 5 moves in different parts of the target area. For example, an actuator element 13 of a stepping motor can generate a scan along a linear path aligned substantially parallel to a top 116 and a bottom 114 of a rectangular body no. The linear transformation movement of the unit 125. Note that at least a part of the subject J 〇 will form a dead angle area or a hundred points that the scanning unit 125 cannot perform any reliable measurement. In general, this dead angle area is limited to the edge and / Or corner area 'and the size of the dead corner area is usually from an edge or corner of the subject no to the wave source 122 or the detector 124 Depending on the distance. Because the dead-end area usually wastes the valuable area of the main body 110, it is best to reduce it by, for example, matching the shape of the main body 110 to the size and shape of the scanning unit 125 and its curved moving path. As shown in FIG. 52 The movable element 12 is a desired target area placed on the media, and the scanning unit 125 is a first area placed on a target area generally adjacent to the rectangular target area 钿, so the wave source 122 and the detector 124 can communicate with The first area of the target area forms light. The excitation of the exciter element can linearly convert the scanning unit 125 from the first area to the second area of the area, such as an adjacent or opposite end of a rectangular target area. Wave source 122 --- ---__- 99- This paper is suitable for S @ ^ g > (CNS) specifications (Mono Ai_) _ binding line 588158

The processing with the detector 124 can maintain optical coupling with the medium during the linear conversion of the scanning unit 125, so the waveform detector 124 can continuously generate an output signal during the conversion. The image element can receive and sample output signals, and other signals representing system variables or parameters (for example, optical density signals, resolution signals, distribution signals, image signals, etc.). The image element can remove high-frequency noise from the output signal and determine the color development of a series of measurement elements (hereinafter referred to as · ,, voxels, and discussed with reference to Figure 乜 and India) representing a group of measurement elements formed by the scanning unit 125 Mission nature. As long as the scanning unit 125 reaches the relative area of the target area, the scanning unit 125 can switch from the second area back to the first area of the target area. The image element may determine another series of representative chirps of the same or different groups of m-chromophores during this second movement. This conversion can be performed repeatedly at a predetermined time period or at a preselected number of repetitions, depending on the necessary resolution of the final image. After the scanning process is completed, the image element can identify multiple consecutive representative frames, provide a two-dimensional spatial distribution of chromophore properties, and generate a spatially distributed final image of the target area. Fig. 53 is an image obtained by linear conversion of the scanning unit of Fig. 5 according to the present invention. As shown in the figure, the entire target area is divided into a series of elements, that is, "voxels", in which each expanded voxel 51 is expanded along a solid element axis 153 on a substantial or entire high skin of the entire target area. The voxels 151 'are continuously arranged in a one-dimensional voxel direction substantially parallel to the curve and path of the movable element 120. It can be understood that the voxels 151 representing a, _b, c, and h are homogeneous regions covering the target region (ie, no, there are any abnormal regions), while those representing d, e, f, and g The voxel 151 is abnormal. Each voxel 151 is a small area that represents the target area of the media, of which -100-this paper size applies the Chinese National Standard (CNS) A4 specification (210X297 mm) 588158 A7

The image element can sample the output signal generated by the waveform detector 124, and determine a representative chromophore property (hereinafter referred to as "voxel") by using the wave equations that define the wave source of the relative voxel and the detector. value"). For example, the enabling of the previous equations (1), (2), and / or (6) can calculate the absolute or relative radon of the spatially averaged erythropoietin concentration and / or oxygen saturation of each voxel. That is, the image module can spatially compose the output signal generated by the waveform detector 124 of each voxel 151, and calculate the spatial average 値 of this chromophore property of each voxel 151. It can be understood that as long as the waveform detector 124 has substantially the same depth of the media covering the entire target area, the region-averaged voxels 实 are similar or identical to the volume-averaged voxels 实. 'Each voxel 151 usually has the same voxel height throughout the target area. For example, when the scanning unit 125 moves along a linear path (or rotates with a center of rotation with a preselected radius), the voxel height may correspond to the effective height of the scanning unit 125, which is along the movable element. The curved path of 120 is measured in the direction of X. However, by moving the scanning unit 125 along a curved path, or two or more different linear paths, the voxel 15 has various voxel heights. However, it is preferable that the voxels 151 have the same height throughout the target area, so the data acquisition and processing procedures can be performed by simpler circuits and / or algorithms. When the scanning unit 125 moves along a path orthogonal to the vertical axis 127, the scanning list το 125 can provide a maximum scanning height. In this specific embodiment, the voxel height is substantially the same as that of the scanning unit 125. In addition, the voxel axis 153 becomes substantially parallel to the -axis ι27 of the scanning unit ι25. In addition, since the voxels 1 51 are continuously arranged by the scanning unit 1 2 5 during the movement thereof, the multiple voxels 151 are continuously arranged side by side along the curved path of the movable element 110. -101-This paper size applies to China National Standard (CNS) A4 (210X297 public love)

Binding

588158 A7 B7

V. Description of the invention (Compared with voxel 15 1's solid structure, the voxel height and voxel axis' voxel width is the characteristic size of voxel 151, so it can be processed according to various standards , Including (but not limited to) the final image resolution, mechanical and electrical characteristics of various parts of the optical imaging system 100, and so on. It can be understood that the voxel width can be a direct indicator of the final image resolution, because the configuration of the image elements can determine the chromophore properties of each voxel 151 to represent 値, and generate the final image according to it. For example, in a high-resolution image mode, the image element can calculate each previous spatial average voxel 値 at each preselected distance along the curved path of the movable element 110. This distance can be processed to be smaller than the width of the scanning unit 125 by, for example, increasing the sampling rate of the data acquisition unit. In contrast, in a low-resolution image mode, the arrangement of the image elements can determine the above-mentioned spatial average voxel 値 at a large distance along the curved path of the movable element 120. Therefore, each scanning area is only a part of the integral element 125, and conversely, each voxel 151 may have a width sufficient to contain one or more scanning regions of the scanning unit 125. Note that the general structure of the voxel 151 can be operated by a common operation of the scanning unit, the actuator element, and / or the imaging element. Thus, especially the voxel structure, the characteristic size of the voxel 151 can be processed by adjusting the operating characteristics of any one of the scanning unit, the exciter element, and the image element. For example, by selecting the desired number of wave sources and detectors of the scanning unit, and by placing them according to a pre-selected geometric configuration: each and all voxel configurations have a pre-selected shape and size. The adjustment of the exciter element can change the scanning speed and curvilinear path of the early element. Each of them can make voxels and have various sizes and / or directions. The adjustment of the image element can also be adjusted to a fixed, -102. This paper size is applicable to the Chinese National Standard (CNS) A4 specification (210 X 297 mm) 588158 V. Description of the invention (100) Lack, or appropriate sampling rate Receive and sample the output signal. As such, it is common in the art that the skilled person can process and synchronize with the scanning unit, exciter element, and image element in order to produce voxels with the most appropriate shape and size and arranged along a preselected path. Outputs a basis for k number 150. It can be understood that the abnormality has different optical unique names during the segment. FIG. 54 范例 An example of a two-dimensional spatial distribution of an output signal generated by a waveform detector that can be linearly converted in a target area according to the present invention according to the present invention. In the figure, the vertical axis represents the magnitude or amplitude of the output signal produced by the waveform detector 125, and the horizontal axis represents the position of the scan unit 沿着 125 along a linear conversion path or moving distance. The two-dimensional distribution of an output signal 150 indicates that the target area includes at least two distinct parts, each of which can exhibit different photon characteristics. In a first portion 152, for example, the output signal 15o is substantially flat and remains substantially the same size. This section 152 is generally &, b, c, and h corresponding to the rectangular target area of FIG. 53 and represents the start and end positions of the scanning unit 125. In contrast, in a second centroid 154 inserted between the region a, b, c and the region h, the output signal 15 is quite curved and has a smaller size that changes according to the position along the target region. This means that, for example, a tumor abnormality may exist in the second portion 154 of the target area. As described below, the identification of the first and second parts 152, 154 of the output signal 150 may constitute the calculation of the output signal Ϊ50-the baseline and the self-calibrating optical imaging system. When the output signal 150 has the first flat part 152 at various stages of development size. As shown in FIG. 34, when the wave source 122 is of opposite polarity, the curve portion 154 of the output signal 15G is larger than the wave source 122 and the detector 124 and then can be moved to the target area.

588158 A7 B7

V. Description of the invention (101 The starting position of the same part, or moving to a different area adjacent to the target area, and the area can be scanned by radiating electromagnetic waves, detecting electromagnetic waves, and generating another set of output signals. After the scanning process, the image element can remove high-frequency noise from the output signal and recombine the voxels to provide a two-dimensional or three-dimensional space with the time distribution of the chromophore properties, and produce chromic sleep on a substantial part of the target area. A spatial and / or temporal distribution image of nature. When different groups of voxels are formed in different voxel directions, the image elements can constitute intersected voxels, each of which is an overlapping or overlapping portion that defines this voxel. Intersecting voxels are generated in the imaging field, regardless of whether the movable element can only perform forward linear transformation or reciprocating motion. For example, during linear transformation, the image element can be obtained by using a scanning unit composed of ^ 1-0442 and S1_D2_D ^ S2 The output signal is generated, and a series of voxels are continuously defined along the X axis at each measurement position. After the linear transformation is completed, the shadow The image element can also continuously define a series of auxiliary horizontal voxels along the γ axis. In other words, by assuming that the target area is in a stable state during the conversion, the image π component can recombine the wave source and the detector to form an auxiliary scanning unit. For example, the wave source Sl at positions eight and zero is combined with the waveform detector Di at the position to allow the formation of a scan consisting of (in A) -Di (in (in c) -Si (in D)). In addition, other auxiliary scanning units can also be defined, such as 8 丨 (in A) _D2 (in B) -D2 (in C} -Si (in D), S〗 (in a) -D2 (in B)- D3 (in C) -S2 (in D), S! (In A)% (in ~ B) -D3 (in C) -S2 (in D), D4 (in A) -S2 (in B) -S2 (In C) -D4 (in D), etc. It can be understood that the previous auxiliary scanning units can meet the symmetrical requirements of the patent, 972. This symmetry is not needed

Order

Line -104-

588158 A7 B7 5. In the case of the invention description (102), the image element can further define an asymmetric scanning unit, such as Si (in (in (in (C) -S2 (in D), etc.). As long as the previous horizontal and vertical bodies Voxels are defined in the field of imaging, and image elements can also define intersecting voxels by identifying the intersection of vertical voxels and horizontal voxels. This image element can also calculate intersecting voxels from voxels 交叉 that intersect vertical and horizontal voxels. A. In addition, details about voxels and intersecting voxels and their 値 are in the US patent case number (not #) name " Optical Imagirig System for Direct Image Construction " and another US patent case number (unknown) name " The Optical Imaging System with Symmetric Optical Probe " discloses that both were filed on February 5, 2001, and are listed here for reference only. Note that intersecting voxels also move scanning units along at least two non-parallel curved paths Or movable elements. For example, in the specific embodiment shown in FIG. 34, the exciter element is defined as a series of_vertical voxel exciter elements along the X direction. For example, a pre-selected angle of 90 ° clockwise rotates the movable element, and linearly converts the scanning unit or the movable element upward. The image element then defines a continuous_horizontal voxel along the Y direction. Through identifying the vertical in the target area Intersecting areas with horizontal voxels. Image elements can construct intersecting voxels in the imaging field. Rotation transformation Figure 55 is a scanning unit diagram of Figure 5 configured for rotation or rotation according to the present invention. The usual configuration of the exciter element can be The scanning unit 125 rotates with a pre-selected center such as the position of the central point 129. Therefore, the rotation or rotation of the scanning unit 125 can cover an angular or circular scanning unit having a radius substantially equal to the scanning unit 125—a half-length radius. The main body 110 is usually -105- This paper is also suitable for China National Standard (CNS) A4 specification (210 X 297 mm)

Order

Line) 5. Description of the invention (103 The shape and size of the same arc or circle, such as the shape k of the scanning area defined by the scanning unit; the shape and size of the scanning unit I25 q J π, and the reduction of the configuration of the dead exciter element can produce # ^ 二 央 而 将 ::: With the center of rotation provided by the phase of the Zheng Zheng, will be M %%. The redrawing unit has a radius greater than the scanning unit-half the length, or twice the id: angular or A circular scanning area. Alternatively, the configuration of the exciter elements can generate two or more movements, and a scanning unit is provided to define the scanning area. The scanning area is an angled or circular shape with different radii and / or different centers with rotation. It is composed of-combination. In addition, the configuration of the exciter element can also deal with the early π, in order to combine this angular or circular movement with the line-hing conversion. When it wants to provide this scanning area, an optional control The actuator can be provided, so that the movement of the exciter element can be effectively controlled along the pre-selected curved path. Multiple movements of the scanning unit are as described above, the exciter element can follow at least two different curved paths and / or even Two different curve directions resulting in at least two different movements of the movable element. This movement can be adjusted to meet a pre-selected geometric curve direction therebetween. For example, at least a part of a curve (or direction) can substantially cross another curve At least one point of road control (or direction). The configuration of this path is orthogonal to each other as shown by the axis of a traditional Cartesian, cylindrical, or spherical coordinate system. In particular, when the target area has a substantially polygonal shape, the exciter The element can move the movable element from a first end to the opposite end of the target area along a curved path, and move it from the second end to -106 along a second curved path.-This paper size Applicable to China National Standard (CNS) Α4 specification (210X 297 mm)

V. Description of the invention (1104 t. The three-curved path will move it from the third to the first or the other end. In a specific embodiment, the X-axis of the actuator element is linearly or re-defined along another axis along the Y-axis. Placed on the third end, and then moved along the third end to the first of this polygon target area or another embodiment of Figs. 56A to 56C and 57 is placed along the X axis of the Cartesian coordinate system, left transformation The subsequent 90. The clockwise direction causes multiple movements of the scanning unit, such as the linear conversion of the scanning unit (and the movable element). Figs. 56, 56] 6, and 56C are relative circuit diagrams of the scanning unit of Fig. 5 according to the present invention. The configuration can be used for this X transformation, 90. Rotation, γ axis transformation. In addition to the exciter element can move the movable 7L piece 120 (for example, linear transformation), and has nothing to do with the rotation of the main body 110, the specific implementation is combined with FIGS. 56A to 56C. The optical imaging system of the example is substantially the same as that of FIG. 52A. In terms of implementation, the actuator element can be initialized to place the main body 110 in the first structure. The main body 110 is arranged in the medium to cover at least one of the target areas and is exempted. Movable element 1 20 (and its scanning unit 125) is a first area placed on the target area, which is a vertical end adjacent to the rectangular target area. The wave source 122 and the detector 124 are carefully placed to form a first area of the target area. One region is coupled, so the wave source 122 can effectively irradiate the electromagnetic wave to the first region of the target region, and the waveform detector 124 can generate an output signal from the first region. In FIG. 56A, an exciter element (not shown) can follow The X-axis (X transformation) converts the movable element 120 from a first region of the target region to a relatively second region. The wave source 122 and the detector 124 can generate an output signal representing the spatial distribution of the chromophore properties during the -X conversion By properly processing and synchronizing the scanning unit 125 with the exciter element, the image element (not shown) can be

588158 A7 B7

Axis alignment, so a set of horizontally expanded voxels 163 can be formed along the x axis (hence the "" X expanded voxels"). In addition, because the linear transformation path of the scanning unit 125 is aligned with the Y axis, the X expansion The voxels are continuously arranged side by side along the Y axis. By solving the waveform equation based on the spatial average output signal of each of the X-expanded voxels, the image element can calculate the voxel 値 of each X-expanded voxel. The element 12 (and the tracing unit 25) reaches the opposite end of the rectangular scanning area and the scanning process can be terminated. The image element can then recognize the overlap or cross between the Y-expanded voxel 161 and X-expanded voxel 163 A set of intersected voxels 165 is defined, and a series of intersected voxels 165 直接 is directly calculated from the voxels 値 of each pair of Y dilated voxels 161 and X dilated voxels 163 crossing each intersected voxel ι 65. According to the intersected voxels That is, the image element can generate a two-dimensional or three-dimensional spatial distribution image of chromophore properties in at least a substantial portion of the target area. Figure 57 is a continuous X transformation, rotation, and Y transformation on the target area according to the present invention. The image obtained by the scanning unit of 5. As mentioned above, the image elements are two orthogonal groups defining voxels 161, 163 crossing each other, and defining intersecting voxels 165. Because each crossing voxel ι65 is substantially smaller than the gamma extension And X expands voxels 161, 163, so the imaging element can produce high-resolution images with absolute chromophore properties and spatial and / or temporal distribution. Generally 'for example, vertical γ expands voxel-161 width and / or horizontal X The characteristics ~ sizes of the voxels 161 and 163 with the height of the expanded voxel 163 can be adjusted respectively by processing the speed of X conversion and Y conversion, by controlling the sampling rate of the output signal, etc. Therefore, 'the processing is the same during X conversion and γ conversion. Conversion speed _ _ -109- This paper size applies Chinese National Standard (CNS) A4 specification (210X297 mm) 588158 A7 B7 V. Description of the invention (107) The width and height of the intersecting voxel 165 will be the same , Resulting in rectangular intersected voxels. Or, by using different speeds during each of the X and γ transformations, and / or by temporarily changing this speed, the intersected voxels 165 have rectangles of different sizes. Therefore, the image resolution can also be controlled manually or appropriately. For example, the speed of the linear transformation (or any other movement) can be reduced to obtain smaller rectangular or square intersected voxels, where the image element can provide improved correctness and improved The final image of the resolution. The feature size can be adjusted by the sampling rate of the image element processing output signal. Note that various specific embodiments can be used in the target area to provide multiple movements of the movable element. For example, one or more exciter elements For example, by operating each exciter element, different movements of the movable element, the scanning unit, and / or the sensor may be provided in different directions, so as to follow a particular curved path and / or by operating a single exciter element to produce a Special movement, which can guide the movable element along different guides with different curved paths. Although these specific embodiments allow heavy control of the movement of the movable element, they often require more parts and more complex control algorithms. Alternatively, as shown in FIGS. 56A to 56C, the optical imaging system includes a movable body, in which the actuator element and the movable element can be fixedly coupled. By arranging the exciter elements to generate T-moving element movements related to the movable body and generating the movable body movements related to the target area, it is independent of the movement of the movable element, a single actuator element can follow many different curves. This results in different movements of the movable element. In addition, the movable element can be synchronized with the movement of the movable body to generate a preselected movement of the scanning unit on different areas of the target area. Scanning unit / movable element moves differently at the same time -110- This paper size applies the Chinese National Standard (CNS) A4 specification (210X 297 mm) 588158 A7 B7 V. Description of the invention (108) In another aspect of the invention, one The optical imaging system includes an exciter element that is configured to directly establish intersecting voxels by simultaneously generating at least two different movements of a movable element (and its scanning unit). This concept of the present invention is described through a specific embodiment shown in FIG. Fig. 58 shows a scanning unit diagram of Fig. 5 configured for simultaneous χ-? Linear conversion according to the present invention. Generally, in addition to the configuration of the exciter element (not shown) in FIG. 58, the linear and linear conversion of the movable element 120 along the X axis and the reciprocating motion along the Y axis are combined, and the optical imaging system of this embodiment is combined The essence is the same as in Figs. 52 and 56A. In terms of implementation. The fixed (or mobile) body 110 is placed in a target area of the media, and the movable element 120 is placed in a first area. The placement of the wave source 122 and the detector 124 can also form an appropriate optical coupling with the first region of the target region, and can irradiate the electromagnetic wave to the target region and detect the electromagnetic wave therefrom. The exciter element can convert the movable element 120 along the axis, and reciprocate the movable element ι20 along the gamma axis. Therefore, the movable element 120 (and the scanning unit 125) can scan the target area along a substantially sinusoidal path. In a preferred embodiment of the present invention, the scanning unit 125 can scan the target area, and the image element can sample the output signal at a desired time interval and / or at a preselected position of the target area. It can be understood that the detailed structure of this sinusoidal path (ie, amplitude ·, frequency, phase solution, etc.) can be determined by the X conversion speed and the γ reciprocating speed. As long as the movable element 120 reaches the opposite end near the bird in the target area, the scanning process of the target area can be terminated with one operation, and the subject is manually moved to the lower-target area of the media for further scanning. Or, the incentive -111. 588158 A7 --------B7 V. Description of the invention (109) Spare parts or auxiliary motion generating elements can also be used to transform and / or rotate the main body i A target area. Note that the accuracy of the extracted signal can be improved, and the image resolution can be increased by repeating the same scan processing in different target areas or performing different scans. For example, the backward X of the movable element 120 can be achieved by reciprocating the Y axis. Transform and move back to the first area of the start of the target area. The configuration of the exciter element can substantially move the movable element 120 along the same sinusoidal path in opposite directions, and the configuration of the image element can output k at the same or similar measurement position and at the same or similar sampling rate during backward movement No. sampling. By moving forward and backward for each voxel and averaging this signal to obtain multiple output signals, the signal-to-noise ratio of the output signal can be significantly improved. Alternatively, the exciter element may produce different sinusoidal paths, or the imaging element may sample the output signal at different locations and / or at different sampling rates. Therefore, at least two different groups of voxels can be defined at each position of the target area during the forward and backward movement of the movable element 120. In addition, at least one set of intersected voxels can be generated from multiple recombined voxels expanded along different axes to allow for improved resolution images. In still another option ', more groups of voxels and intersecting voxels can also be obtained by configuring the subject 11 to be an animal body related to the target area. If preferred, the movable element can perform a Y reciprocating motion, and the movable element can move at a slower speed or stop at a desired position along the X axis. Coincidentally, after scanning the entire height of the target area through the scanning unit, the movable element can resume normal X transformation. Embodiments provide the advantage of allowing smaller and shorter movable elements to scan the entire target area. -112- This paper size applies to China National Standard (CNS) A4 (210X297 mm)

Hold

Line 588158 A7 B7

V. Description of the invention (More than 110 recombined voxels and intersected voxels can be obtained by adjusting or processing the same pattern of the output signal of the image element. For example, the image element can be synchronized with the exciter element, so the image element can be in advance in the target area. Select the position to sample the output signal. Therefore, the operator can process the exciter element or image element to control the sampling mode of the output signal to adjust the shape of the voxels and / or intersected voxels, thereby improving the resolution of the final image, etc. The main advantage achieved through the optical imaging system of FIG. 58 is that this system only requires a smaller number of wave sources and / or detectors. It is preferable that the scanning unit has substantially the same target area as the scanning unit shown in FIGS. 52 and 56 ( That is, a specific embodiment of the feature size, the optical imaging system of FIG. 58 defines a scanning unit having a height and / or width that is substantially smaller than the target area, and places it on the entire portion of the target area in two directions. The scanning unit can be scanned to transform the scanning unit along the horizontal direction, and the scanning unit can also scan the entire width of the target. In this regard, the previous optical imaging system can even use a single wave source_single detector configuration ... to define a scanning unit with only a small portion of the scanning area of the target area. It can be understood that the moving path characteristics of the movable element (and / or scanning unit) It is not always used to define the shape and / or size configuration of a voxel. For example, a sinusoidal path of a movable element does not need to produce a curved voxel arranged along a sinusoidal path of a movable element. A pre-selected time interval is used to sample the output signal along a sinusoidal path. Voxels may have curved boundaries, varying heights and widths, and are substantial edges; sinusoidal

At least-the substantial part. However, by reciprocating the shorter scanning unit in the vertical direction, the scanning unit can cover the entire height of the target area. Order

Line -113-

588158

Tie-down configuration However, if the image element is synchronized with the exciter element so that the output signal is sampled at certain positions, the resulting voxel can be processed with the same degree and width as the Bebe, and in almost any desired direction Configuration. In addition, when the speed of the movable element γ element (that is, the γ reciprocating speed) is maintained substantially faster than the X element (that is, the X transformation speed), the voxel has an approximately rectangular shape. With the same symbol, the voxels can be configured into a congruent square, for example, by synchronizing the image element with the exciter element, so that the image element can each have the same horizontal and vertical distance (i.e. Space interval) will sample the output signal. Binding

Line A 7L piece of exciter can produce two or more different movements along two or more curved paths, so the image element can define voxels or measure 7L pieces along two or more directions. For example, the specific embodiment of FIG. 58 allows the imaging element to define voxels not only along the X-axis but also along the Υ-axis. That is, the image element can define more than one set of voxels in a direction orthogonal to the line-to-line transformation path. The shape and size of voxels and cross voxels can also be controlled by processing speeds along the X and Y axes, and by synchronizing this movement with sampling positions or intervals. Note that the voxel obtained through two simultaneous movements of the movable element is roughly corresponding to the phase X voxel obtained in FIG. 57 corresponding to two continuous and / or non-parallel movements of the movable element. This cannot accommodate any movement of the movable element along any curved path. For example, when the movable element is linearly transformed (or reciprocated) along a radial direction, an exciter element may rotate the movable element. This configuration can usually be produced along a radial direction-a series of spiral layers, where each rotation of the spiral layer contains multiple arcuate voxels. Therefore, by maintaining a rotation speed that is greater than the radial transformation speed, the spiral layers can approach each concentric spiral that also includes -114- 588158 A7 B7. (112) Multiple arcuate voxels. Further details of this voxel are provided in the US patent names " Optical Imaging System for Direct Image Construction " and " Optical Imaging System with Symmetric Optical ProbeM, filed on February 5, 2001, both of which are listed here only For reference. By generating intersecting voxels from fixed and moving wave sources / detectors is still another aspect of the present invention, the configuration of an optical imaging system can be achieved by combining at least one movable wave source and / or detector at A movable element of the optical imaging system and directly generating intersected voxels by combining at least one fixed waveform detector and / or wave source in one fixed element. Figure 59 is a cross-sectional view of a scanning unit according to the present invention, in which all 4 The wave sources 122 are arranged along the side of a fixed body no. However, all three waveform detectors 124 can be implemented on a movable element 120. An exciter element (not shown) can generate a scan along the X axis of the target area. The linear transformation or reciprocating motion of the unit 125. Therefore, the substantially fixed wave source 122 is related to the target area of the media, and the waveform detector 124 The movement is related to the wave source 122 and the target area. The wave source 122 and the detector 124 define scanning units that are extended at angles related to the linear movement path of the movable element 120 and move at the & element 120 In the meantime, their structures (such as their size, shape, angle, etc.) are under-changed. In terms of implementation, the fixed body 110 and the viable element 120 are placed in the first target area, so the wave source 122 can form the target area. Optical coupling, and the movement of the waveform detector 124 can form the optical coupling of the first area of the target area. The excitation of the wave source 122 and the detector 124 can illuminate and detect electromagnetic waves. Excitation __ · 115 · This paper scale is applicable to China National Standards (CNS) A4 specification (21 × 297 mm) B7 V. Description of the invention (m) The exciter element can move the movable element 120 and its waveform detector 124 from the target area along a linear path. One end is transformed into the other end. Each pair of the wave source 122 and the detector 124 can form an expanded voxel 171 at a change angle related to the linear transition path (or χ axis) of the movable element 120, which is due to the image element ( Display) data acquisition or sampling rate. The waveform detector 124 can generate an output signal representing the spatial average over the entire area or volume of each expanded voxel 171. The image element can receive and sample this output signal and determine The expanded voxel 値 image element of each expanded voxel 171 can also recognize the intersection of two or more voxels and generate an intersected voxel 173. Based on the voxel 値 of the intersected voxel, the imaging element can calculate the The relative voxels of each of them. As soon as the movable element 120 reaches the target area or another neighboring area, the scanning process is terminated, and the subject 11 moves to the next target area of the media for further scanning. Alternatively, the configuration of the exciter elements may repeat the scanning process of the same target area along the same or different curved paths. It can be understood that the geometric relationship between the fixed wave source 122 and the movable waveform detector 124 changes according to the position in the target area. Therefore, the scanning unit 125 usually has dilated voxels 171 of different lines and sizes during the movement. This irregular voxel causes complexity in obtaining the waveform equations applied to the scanning unit 125, so they are usually not the best substantially the same shape and size. The shape and size of the expanded voxel 171 can be reduced through various configurations, such as synchronizing the exciter element with the image element, so data sampling can be performed at a preselected position in the target area, resulting in an intersection with a predetermined structure Voxels. The shape of the intersecting voxels and the distribution pattern -116- This paper size applies the Chinese National Standard (CNS) A4 specification (210X 297 public love ^ 588158 A7 B7 V. Description of the invention (114) " ~ and the size can be adjusted by adjusting the wave source and The geometric configuration and transmission between the detectors; change their speed and shape of the path of movement by processing the curve of the tracing unit; etc. are controlled. Therefore, the skilled person is usually familiar with the technique to choose to find the scan Units, actuator elements, and / or imaging elements are most suitable. Ί configuration. J Note that the scanning unit of FIG. 37 usually defines angular voxels 16ι, ι63, which can change them during the movement of the movable element 120. The shape, shape, and size of the beam are changed because the geometric configuration f between the fixed wave source 122 and the movable waveform detector 124 changes the position of the movable element 120 in the target area. The voxels 161, 163 need more complicated Analytical or digital methods are used to obtain the waveform equations for the fixed wave source 122 and the movable waveform detector 124. Therefore, it is usually not the same to maintain substantially the same shape and size. Smaller. However, the shape and size of the angular voxels and their intersected voxels can also be transmitted through: 丨 Various configuration compensations, such as by synchronizing the exciter element with the image element, so the signal Or the data can be sampled at a preselected position in the target area to define a voxel with a predetermined structure. The structure of the intersecting voxels and the distribution pattern can also be processed by processing the general configuration between the wave source and the detector Controlled by changing the moving speed of the waveform detector, moving the f-path profile through the curve of the processing unit, etc., so that the person skilled in the art is looking for: to the previous specific embodiment Scanning unit, exciter element, and / or shadow: Appropriate configuration of the image element. If it is better, at least one wave source can be arranged in the 丨: movable element and / or at least one waveform detector can be implemented on a fixed body. First :; The front wave source-detector configuration can also be reversed, that is, all wave sources can be configured on: 丨 movable components, and all waveform detectors can be configured on fixed bodies. Ί -117-

588158 A7 B7 V. Description of the invention (115) B.-Specific implementation of 2 / 3-dimensional image generation of distribution. For example, the correctness of the image output signal and resolution can be achieved by repeating the same scanning process or performing different scanning on the same target area. Process and ask questions. The multi-recombined intersected voxels can be formed, for example, by adjusting the image pattern of the image element, or by processing the path and / or path speed of the movement generated by the exciter element. Note that the specific embodiment of FIG. 59 can also combine a small number of wave sources and debt detectors, and the height and width of their scanning unit are substantially smaller than the scanning unit of the target area. It is understood that the prior optical imaging system of the present invention can produce two- and / or three-dimensional distribution images of chromophore properties on a substantially instant basis. Compared to each traditional optical imaging system that requires complex and time-consuming image reconstruction processing, previous optical imaging systems can directly generate this from this voxel and / or expanded voxels 交 and / or phase X voxels 交 of intersecting voxels. image. For example, the optical imaging systems of Figs. 52 to 59 include real-time image construction methods, regardless of the size of the target area, the number of wave sources and detectors, and the detailed structure along the curvilinear path of the movable and scanning unit. Previous optical imaging systems can adjust image resolution. For example, compared to the previous technology that required complex equipment adjustments, the previous optical imaging system only had to adjust the data sampling rate, the moving speed of the movable elements, the wave source and detector groups or sampling patterns, and so on. In another aspect of the present invention, the configuration of an optical imaging system may include a movable body and a movable element, so that the movable element in the target area can be moved by moving, and the movable body can be moved in different target areas of the media. Generates chromophore-like distribution shadows in the target area of a physiological media-118- This paper is suitable for standard paper ® S family standard (CNS) A4 specification (21GX 297 public love)

Binding 588158 116 V. Description of the invention (FIG. 60 is a diagram showing another moving optical imaging system according to the present invention. The optical imaging system 200 typically includes a movable body 21, at least one movable element 220, and an actuator element 23, and An image element 24. The movable body η. Has a fixed shape and size to cover at least a substantial part of a media target area, and a movable element 22 including at least a part is taken. The movable element typically includes at least a mobile unit 212. In order to move the movable body 210 on different target areas of the media reading. Examples of this moving unit include (but not limited to) wheels, rollers, guides, etc. The configuration of the movable element 220 is similar to or the same as that in FIG. 1 to 3 and 52 to 58 are described in the previous specific embodiments. For example, the movable element includes at least a wave source and at least one waveform detector configured according to any previous structure. The operation of the one or more exciter elements 23 is related to the movable The main body 210 is coupled to the movable element 22 so as to generate at least one main movement of the movable main body 210 along at least one main curved path, And at least one secondary movement of the movable element 220 along at least one secondary curvilinear path. The exciter element 23 may also simultaneously or continuously generate a curve transition, rotation, rotation, or reciprocation of the movable body 210 and / or the movable element 22 As shown in FIG. 38, in a specific embodiment similar to FIG. 60, when operating, the movable body 110 and the movable element 120 are placed at their starting positions. The movable body is placed on the medium, and thus the scanning unit 125 is a first area placed in the target area of the media. The wave source 122 and the waveform detector 124 can then be excited 'and the exciter element 130 can substantially linearly move the movable element 120 into an adjacent region of the target region. As long as the movable element 12〇 Reached the target area-119 · This paper size applies Chinese National Standard (CNS) A4 (21〇x 297mm) Gutter 588158 A7

: In addition, the scanning process is terminated, or the movable element 12 can be moved back to the first area of the target area, and the scanning process is continued. After scanning of all the target areas by the movable element 120, the mobile unit 119 can be activated to move the optical probe and / or the entire optical imaging system to the second target area of the media.

Order

It can be understood that an optical guiding element is arranged in the target area of the media, so that the movable element can be moved in multiple target areas. The guide element is preferably made of an elastic material or has a structure whose shape can conform to different contours of different target areas. For example, a ring-shaped guide element may be provided to fit the head end and the bottom of a human chest. The movable element can engage the guide element and move 'along it' to allow the scanning unit to scan the head or chest. By allowing the movable element to move along the curved path of the guide element with a known spatial coordinate at a best or predetermined speed, the optical imaging system can obtain the output signal (or the chromophore nature) of the continuous two near the head or chest. Or three-dimensional distribution. In addition, the two-dimensional pattern can be combined into a three-dimensional distribution pattern without relying on the image symbols required by the traditional optical imaging technology tradition. Therefore, this specific embodiment can also provide a real-time structure of a chromophore-like two- or three-dimensional image in the media. D. Self-Calibration Baseline Method. In a further aspect of the invention, an optical imaging system can calculate the baseline or background size of an output signal generated by a waveform detector (hereinafter referred to as " baseline π). Based on this baseline, previous optical imaging systems can perform this system's waveform detectors, sensor assemblies, optical probes or portable probes -120- This paper is sized for the Chinese National Standard (CNS) Α4 (210 X 297 mm). The self-calibrating optical imaging system includes at least one of the prior wave sources I described herein, at least one of the previous waveform detectors, and an imaging element. The image element may preferably remove high frequency noise from the output signal by, for example, arithmetically, weighting, or averaging the output signal, and / or processing at least a portion of the output signal by a low-pass filter. The configuration of the image element can identify different parts or sections of the output L number, each of which can present a different outline (for example, flat, linear, or curved) and have different sizes (for example, flat or 'culture). When the image element recognizes one or more parts, in which the output k number is substantially flat and has a substantially similar size, this usually indicates that the flat part corresponding to the output signal is a target region composed of the same material, such as normal tissue and cells . The image element can then calculate the baseline of the output signal by arithmetically, geometrically, or weighted averaging the size of the flat or linear portion of the readout signal. The image element can then calculate output signals that are not self-calibrating or positive self-calibrating, such as normalized optical density signals, which are defined as the ratio of the different signals to the baseline between the output signal and the baseline. This optical density signal can be provided to the image element, and then a set of waveform equations applied to the wave source and the detector are solved. These solutions represent the spatially uniform distribution of the chromophore properties in different parts of the media area. It is best to perform the self-calibration loop first, which can be performed substantially instantaneously. This means that before the movable element of the optical imaging system is moved from the first target area to the next, the image element is preferably configured to sample the output signal on different parts of the first target area to generate a normal optical density signal; and Taking this 588158

It is best to display the output signal, optical density signal, and / or chromophore property distribution on each voxel. This aspect of the invention is to provide several advantages over previous techniques. Compared to prior art optical imaging techniques that require a media baseline assessment in a sampled medium or a medium, the optical imaging system of the present invention can evaluate a single baseline of the media 'and use this baseline across the entire target area and / or media. Therefore, each optical imaging system can avoid any need to evaluate multiple baselines' and I need to compromise on efficiency. In addition, the previous optical imaging system can produce images with two chromophore-like distributions in real time. In addition, for example, the wave source of the optical imaging system and the probe of the detector or its sensor need not be moved and placed back and forth between the image and the target area. Therefore, there is no danger in reducing the light coupling between the probe and the target area of the media, so the resolution of the results can be improved. The flat portion of the output signal, or conversely the rest of the output (ie, non-flat or curved) can be identified by a variety of different configurations. First, one or all parts of the output signal (or a filtered output signal with an improved signal-to-noise ratio) can be divided into different points based on a pre-selected threshold value. The selection of this critical chirp can be regarded as a minimum cutoff chirp of the flat part, so all data points in the flat part have a size equal to or greater than the critical chirp. Alternatively, the critical 値 can be a maximum cut-off 非 of the non-planar, curved portion, so the non-flat or curved portion must have a size equal to or smaller than the boundary 値. The output signal can change their size in flat and non-flat parts, regardless of the critical threshold. Therefore, the image element can provide an auxiliary cut-off range or a deviation range in which any data points outside the range are not included in the flat or non-flat portion. Different methods and / or configurations can be used to establish criticality. For example, image element _ -122- This paper size applies to China National Standard (CNS) A4 (210X 297 mm) 588158 A7

It can provide an operator that can have the output signal obtained on different parts of the target area, and the operator can manually select the flat part of the output signal, or the critical part of non-flat or curved points. The critical threshold can also be appropriately determined by identifying a reference threshold, which can be the largest threshold in an area (or global) or the smallest threshold in an area (or global). As long as the reference frame is identifiable, the critical frame can be determined, for example, by multiplying (dividing) the reference frame by a preselection factor, or by subtracting (or adding) a preselection offset from the reference frame. Alternatively, the image element may follow a curved movement path of the movable element to calculate a cumulative average of multiple output signals generated by the waveform detector. The entire accumulated average can then be used to establish one or more critical thresholds, reference thresholds, preselected factors, and / or preselected offsets. Order

The line understands that the image element can calculate the baseline of at least two different target areas of the media. Multiple baselines (called "regional baselines") can be analyzed to determine their effectiveness, and the correct one is not affected by the appearance of abnormal cells or tissues. For example, when the movable element is placed in an area without any abnormal marks, the output signal is flat over the entire portion of the target area. The baseline can be easily calculated as the entire output signal is averaged. t When the target area includes normal and abnormal cells or tissues, the imaging element can divide the output signal into at least two parts, that is, a flat-tan part and another non-flat part, or this flat part or area of the output signal will be found segment. The baseline can then be calculated as a flat part of the output number. However, when most parts or the entire target area ^ is composed of abnormal cells or tissues, the output signal has a size of the maximum cutoff 佶 or less than the minimum cutoff 并且Can even show up = quite flat contour. When this target area is the first one to check, ":

588158 V. Description of the invention (121) ‘When the placement of the image element is based on this target area, the critical frame size is-operator. The average of the number is not the average of the baseline. As long as you can find the baseline between the correct output signal of the target area and the non-soft target area, at least two baselines operating two different target areas can pass through the heavy area baseline or configure image components to prevent Clerk to avoid misdiagnosis. Where 1 interfering Θ When the regional baselines from the multiple target areas are not substantially comparable, or present a large = preselected deviation, the image element can obtain a representative average, or global baseline (hereinafter referred to as " global baseline) through this global baseline "), and normalize the output signal through Wang Yuji. Alternatively, one operator or two images can select a single baseline from different baselines in the target area and use it as a global baseline. Alternatively, a few selected regional baselines or all regional baselines can be averaged to calculate the global baseline, where multiple regional baselines can be arithmetically, geometrically, or weighted averaged to produce a global baseline. When Tian Quanyu or synthetic media images are composed of multiple target scenes with multiple target areas, the image element can generate an image of each area based on the regional baseline of each target area or a single global baseline. For example, the regional image of the regional target region can be constructed from each of their regional baselines obtained in the target region, and a composite media image can be obtained by arranging multiple regional images obtained by arranging multiple regional baselines. Alternatively, the global baseline can be selected or calculated based on all area images. Roughly, each method has its own arguments for and against it. For example, when a composite image near the brain is needed to identify any potential or actual pulsation, the thickness of the heterogeneous organs (such as ears, eyes, etc.) and that of the brain may be different around the brain. The target area produces different regional baselines. If the global baseline can be taken into account from the multi-region baseline to obtain all region images, all pixels have the same brightness ratio and / or color ratio throughout the media. Although this synthetic media image allows the physician to make a comparative diagnosis, he or she cannot find a mild pulsation condition that is hidden in a localized target area and is shadowed by a similar or greater than a mild pulsation condition. In contrast, when the composite image is composed of multiple regional images based on the baselines of individual regions, each regional image can have its own brightness ratio or color ratio. Although previous mild pulsation may not be compromised in the area image, the physician must analyze each area image individually. One way to avoid this inconvenience is to artificially increase the contrast between normal cells and abnormalities in the tissue in each local target area. For example, as long as any potential abnormality is identified, the image element can amplify the signal corresponding to this potential anomaly, so the amplified signal will not cause a shadow from the size of the global baseline: a special symbol or color can be added to improve the image to alert Physician. In another example of a synthetic media image around the chest, some tumors can be the same or larger than the scanning unit of the optical imaging system or the target area defined thereby. As a result, the at least one region image has a region baseline that is substantially larger or smaller than a normal cell or tissue baseline. To avoid passing a global baseline of this abnormal base green bias, the configuration of the image elements can compare the individual regional baselines obtained from multiple local target regions, without considering this bias baseline in the calculation of the global baseline. — 'Although the above disclosure of the present invention is mainly aimed at providing a life-time distribution image of chromophore properties, the present invention can be used to generate a time distribution image: -125 · This paper standard is applicable to the GG Home Standard (CNS) A4 specification (21QX297 & ^) V. Description of the invention (123): The first two can be: the element's scanning unit ... essentially selects the sound image of the same area-: and the output signal difference measured at different times is ~ π. An image of a temporal change in the nature of a chromophore in a region and a temporal distribution pattern. Alternatively, the time distribution can be provided as :: Two or more time distributions of chromophore properties can be obtained from different time frames. For example, the movable element and its scanning unit may repeat the scanning process of the target area, and calculate the time distribution pattern of the chromophore properties at each position of the target area. It can be understood that the temporary change is related to the change in the nature of the chromophore. However, as long as the absolute 値 of the chromophore property can be determined at any reference time frame, previous or subsequent changes in this property can be converted to absolute 値 and vice versa. > Wang Yi, the previous optical imaging system, optical probe, and method of the present invention can provide temporary changes in the amount of blood and water in the target area of the media. In a specific example of obtaining a temporary change in blood volume in a specific target area of a human body, the concentration of oxyhemoglobin [Hb0] and the concentration of deoxyhemoglobin [111?] Can be determined by a set of equations (1 tick and (lb) or Calculated through another set of equations (2a) and (2b). As long as [Hb] and [HbO] are known, their total number (ie, total heme concentration [HbT], which is [Hb] and [HbO] The total number can also be calculated. By obtaining the output signal from a gray-scale waveform detector in the same target area, the total erythropoietin concentration change can be obtained. By assuming a hemocytometer (ie, blood) flowing in and out of the target area The percentage of blood cell volume in the cylinder) can be maintained at a fixed level throughout the time, and the temporary change in blood volume in the target area can be directly calculated from the [HbT] temporary change point of view of the target area. Alternatively, [Hb] and [HbO] Temporary changes can be calculated from equations (6a) and (6b), because 126 paper sizes apply the Chinese National Standard (CNS) A4 specifications (210 X 297 mm) A7 B7 V. [Hb] and [HbO] changed, the temporary change of [HbT] can be as It is obtained by standardizing the sum. It can be understood that the application of the optical shadow m optical probe and the method of the present invention can obtain a three-dimensional distribution image of the color and color properties of the target area of the media. As mentioned above, the electromagnetic wave is irradiated through the wave source, and It is transmitted to the media by pre-selecting the media target volume defined by the ice (or thickness) through a region's area. Therefore, the set of waveform equations can be the formula of the three-dimensional target volume. The output generated by the waveform detector The signal can be passed to the image element =, and then the waveform center-of-squares can be solved using the relevant initial chirps and / or boundary conditions. This solution comes from the wave equation. This solution represents the s-dimensional distribution of the chromophores in the target area of the media To maintain the pre-selected resolution of the image, the optical imaging system or probe preferably includes a sufficient number of configured wave sources and / or detectors to define a large number of scanning units; and the voxels of the target area. Assume, An optical image system includes two wave sources and four waveform detectors and generates a two-dimensional image of a target area with a predetermined resolution. When a The target volume is defined as having the same area as the target area, and when a pre-selected thickness is N two-dimensional layers that overlap each other, this optical imaging system needs to include approximately 2N wave sources and / or 4N waveform detection To maintain the same resolution as each of the three-dimensional layers. However, the number of wave sources and detectors required can be reduced by processing the exciter elements in order to generate sufficient movement of the wave source and the detector in the target area. And it is better to be in multiple different curve directions. However, the number of wave sources and detectors required is usually inversely proportional to the number or complexity of movable elements, or the output signal sampling rate of the image elements. Therefore, optical imaging systems can pass Configuration Incentive • _______ -127- I Paper Ruler ® ® Tsukam Standard (CNS) A4 Gage (297 mm) 588158 A7

Order

Line 588158 A7

The target area of the volume, and the waveform detector 124 can detect electromagnetic waves interacting and emitted from the target area of the media. The waveform detector can generate a corresponding output signal or data point signal to indicate the amount of electromagnetic waves detected by the scanning element. A group of wave sources 122 and a debt detector 124 and a group of scanning elements also define a scanning unit 125, which is usually an effective scanning area forming the optical probe of the present invention. As a result, the groups of sensors 122 and 124 can generate output signals corresponding to a plurality of multiple output chirp signals or data point signals, and each # number is generated at a corresponding scanning element. The structure of the scanning unit 125 and its scanning area can be determined by a general configuration of a sensor component and / or a wave source-detector configuration, for example, the number of the wave source 122 and the detector 124, the general configuration therebetween, and the scanning element The wave source 122 and the detector 124 group with the scanning unit, the irradiation ability or transmission power of the wave source 122, the detection sensitivity of the waveform detector 124, and the like. For example, in the specific embodiment of FIG. 42A, the two waveform detectors 124 are inserted at equal distances between the two wave sources 122. Therefore, on the scanning area 120a, the sensors 122, 124 may define a " linear " scanning unit 125a, which substantially extends along a longitudinal axis 127. In the specific embodiment of FIG. 42B, one column of the wave source 122 is directly arranged on a second column of the waveform detector 124 in a substantially square manner, and a substantially rectangular or square shape is defined on the area 12 of the scanning unit 125b. Area ". The specific embodiment of FIG. 42C includes four parallel columns of sensors, where two waveform detectors 124 (or wave source 122) are inserted between the two wave sources 122 (or detector-124). The sensors 122, 124 are a scanning unit 12 forming a substantially rectangular or square shape, but wider than the scanning unit 125a in FIG. 42A and larger than the scanning unit 125b in FIG. 42B. Note that the scanning unit 125 of the optical probe 120c is fixed -129- This paper size is applicable to the Chinese National Standard (CNS) A4 specification (210 X 297 public love) 5. Description of the invention (127) Multi-scanning unit with different structure 125a, 125b. In contrast, the specific embodiment in FIG. 42D includes a waveform detector 124 arranged near the wave source 122 so as to define a substantially circular scanning unit 125d on the circular scanning area 120d. It can also be understood that the wave source ι22 and the detector 124 of the circular scanning unit 125d can be composed to define the previous " linear " scanning unit 125a and the "air type", and the scanning unit 125b. The general configuration of the wave source of the present invention Coupling with media and irradiating electromagnetic waves. Any wave source can be used in an optical coupling system or optical probe to illuminate with, for example, a range from 1000 nm to 5,000 nm, from 300 nm An electromagnetic wave of a preselected wavelength in the "near infrared" range of 3,000 nanometers, or specifically from 500 nanometers to 2,500 nanometers. However, as described below, a typical wave source configuration may irradiate a near-infrared electromagnetic wave having about 690 nm or about 830 nm. The wave source can also irradiate electromagnetic waves having different waveform characteristics such as different wavelengths, phase angles, frequencies, amplitudes, and harmonics. Alternatively, the wave source may irradiate electromagnetic waves, in which the same, similar, or different signal waves may be superimposed on carrier waves having similar or different mutually different wavelengths, frequencies, phase angles, amplitudes, or harmonics. In the specific embodiment of FIGS. 42 A to 42D, the configuration of each wave source 122 may irradiate electromagnetic waves having two different wavelengths, such as about 660 μm to 720 nm, such as 690 nm, and about 810 μm to 8 5 0 love micrometers, such as 830 nanometers. Similarly, the previous configuration of the waveform detector can detect the aforementioned electromagnetic wave, and can generate an output signal in response to it. As long as the waveform detector has the above-mentioned range of electromagnetic wave detection sensitivity, any waveform detector can be used in an optical imaging system or an optical probe. The construction of the waveform detector can also detect -130- This paper size is applicable to the Chinese National Standard (CNS) A4 specification (210X297mm) 5. Description of the invention (128) Electromagnetic waves with any previous wavelength characteristics. The waveform detector can also detect multiple recombined electromagnetic waves irradiated by multiple wave sources, and thus can generate multiple output signals. Example Output Signals Figures 43A and 43B are output signals generated by a previous waveform detector according to the present invention. In the figure, the horizontal axis is the distance along an optical probe of the optical imaging system or the axis of the physiological media, and the vertical axis is the output signal amplitude measured by the waveform detector in the target area of the media. . Each output k number usually contains multiple output signals or data point signals, each of which corresponds to the electromagnetic wave detected by the waveform detector of each scanning element of each scanning unit. For the purpose of illustration, the target area on the leftmost side of the media (that is, the beginning of the neighboring map) is designated as the first target area, and the target area on the farthest side of the media is, and the last "target area. As shown in Figure 43A The output signal 150 is fairly flat in the first part or region 152a (that is, from the first to the first order 'region) and in the second part or region 152b (that is, from the first to the last% scanned region). The contour is located between the flat regions 152a, 152b and 15 ° (i.e., from the (i + i) to the ο) target region) in which the amplitude of the output signal 15 is changed with the axis The position is related. The output signal 15 of the figure has a similar figure except that an opposite bell-shaped portion ㈣ (that is, from (i + 1) to the ㈣ target area) is inserted between the two flat portions 152a, 152b. A contour of 43A-. In this medium, which is composed of most normal tissues, the connecting blades 152a, 152b that output a signal of 15 are usually corresponding to normal cells or tissues. Therefore, the media (hereinafter referred to as the baseline of the output signal) ") for a background output Letter 588158 V. Description of invention (129) level. In contrast, the upright and opposite bell-shaped portions i54a, ⑽ usually indicate abnormal tissues and cells at various stages of development (for example, fibrocarcinoma, fluid, etc.) Tumor tissue, bad or benign cancer). The curved portions 154a, 154b also represent normal anatomical tissues or units (eg, blood vessels, connected tissues, etc.) with optical properties different from background tissues or cells. In estimating oxygen and In terms of erythropoietin, oxygen saturation, blood volume, and other chromogenic properties, the output signal generated by the waveform detector needs to be calibrated to initialize the sensor and / or account for various differences in the target area of the media. The characteristics of scanning elements are different. In addition, the k-number processing algorithm used in optical imaging systems usually does not require the output signal itself, but the ratio of the output signal (for example, optical density), where the output signal is transparent—the output signal is normal Therefore, the aspect of the present invention is to provide an optical imaging system for outputting signals according to the nature of the output signal itself. Signal self-calibration. Self-calibrating OIS example shadow waveform detector m, power source 102. Optical imaging system ι〇〇〇—two hardware (circuit, processor, or integrated circuit) or software, such as knife analysis 160, No. 17 processor, and image processor, its operation can be coupled with others', and each can include-or more functional units. Signal Analyzer Signal Analyzer 16 can operate with-or more Multi-sensor 122. Figure 44 shows a diagram of a self-calibrating optical imaging system according to the present invention to generate a chromophore or its property distribution image in a physiological target region.-Optical imaging system 100 Typically includes at least one wave source 122, at least the number of the paper ruler s -132- 588158 V. Description of the invention (13) Input and output signals, chromophore (or its properties) One or more receiving single coupling, so the signal The analyzer can monitor a variety of different inputs. These signals can be used to produce a color distribution image in the target area of the media. For example, the signal analyzer 16 includes one unit, and the operation of the receiving units is coupled to the wave source 122 and supervised.

The configuration of the unit can also receive external data, operating parameters, and the first output and signal of the garment body. Receive " numbers, and / or other command or control signals provided by an operator or an encoding thereon. The signal analyzer 160 includes other functional units, such as a sampling unit, a critical unit S, a comparison unit, a selection unit, and the like. The sampling unit can receive the previous input or output signal or data from the receiving unit, and can sample the signal in an analog and / or digital mode at a preselected frequency. The operation of the critical unit is coupled to the sampling unit and can determine a critical or cut-off amplitude (or range) used by subsequent functional units, such as the compare and select unit. The critical amplitude or range can be pre-selected and coded in the critical unit. The critical amplitude (or its range) can be provided to the critical unit manually by the operator. Alternatively, the critical amplitude (or its range) can be calculated from the first output signal itself. For example, the critical unit may identify one or more local maximum or minimum amplitudes of the first output signal measured in the first g-labeled area to calculate a flat amplitude of at least one or the entire portion of the first output signal. The maximum or minimum amplitude of a global output signal measured over multiple target areas of the media. After specifying, for example, the amplitude of a reference amplitude, the critical unit may, for example, multiply the reference amplitude by a pre-selected factor that is usually less than 1 · 0, add or subtract another _ -133. Standard (CNS) Α4 specification (21Gχ tear public love) 588158 A7

V. Description of the invention (131)

Load a preselected factor, calculate the critical amplitude by using a function that produces a critical amplitude, or replace the previous maximum or minimum amplitude of the function. Or 'the critical early element may encode or include a pre-selected critical range, receive the range from the operator, or calculate the range based on the previous maximum or minimum amplitude. The earlier element usually communicates with the critical unit, receives a critical amplitude or range 'from it and compares it to the amplitude of the first output signal. The selection unit may receive the result from the comparison unit and select a point or part of the first output signal having the same or substantially similar amplitude. More specifically, when the configuration of the critical unit can provide a critical amplitude, the selecting unit can select a point or part of the first output signal having a greater (or less than) critical amplitude. However, when the critical range provides a critical range, the selection unit may select a point or part of the first output signal that is within (or outside) the critical range. Signal processor

The operation of the line signal processor 170 is the coupling of the signal analyzer 16 and its position can be self-calibrated " the first output signal through the first baseline. The first line can be obtained from the first output signal itself. Similar to the signal analyzer 16Q, the processor 170 also includes functional units, such as an averaging unit and a calibration unit. The averaging unit may average similar amplitudes of the first output signal or sub-scores selected by the selection unit, and specify, for example, the baseline of the first output signal. For example, the 'averaging unit can perform similar operation, geometry, weighting, or the entire average β of the previous point or part as long as the baseline; ^ from the == calibration unit can pass the first baseline to the second / upper-interval And provide a self-calibrated _th output signal, the first output signal can be the ratio of their amplitudes (that is, the ratio of ^ output '• 134 · to its first baseline), or their amplitude difference from the first baseline The ratio. Image processor The operation of the image processor 180 is coupled to the signal processor 170, and its configuration can construct an image of the chromophore (or its shell) based on the self-calibrated first output signal. Typically, the image processor 180 includes an algorithm unit and an image construction unit. The algorithm unit is coded or includes at least one solution to solve a set of waveform equations applied to the wave source = 2 and the detector 124 according to a pre-selected geometric configuration. By providing an algorithm with a self-calibrated axis number L and other necessary initial drawing and / or boundary conditions, Algorithm 7C can solve this set of waveform equations and provide a set of solutions to represent oxygen, or deoxygenation Erythrocyte concentration, oxygen saturation, blood volume, chromophore strength, or expansion properties. The image construction unit can then receive the triad solution signals and construct a spatial distribution of the previous properties of the chromophore. If preferred, the configuration of the image construction unit may constitute an image related to the distribution pattern of the first output signal number, the self-calibrated first output signal, and the like. Benefits of self-calibration systems The prior optical imaging systems and methods of the present invention can provide several benefits over prior art optical imaging devices. One of the most serious problems with prior art devices is that their optical probes or sensors require an evaluation of their output signal baseline. For example, a probe or sensor is placed on a reference medium (for example, a light and shadow) or a reference area of an object. The output signal can be generated by a waveform detector, and the baseline can be based on the optical properties of the reference medium or area. Evaluation. The probe or sensor can then be moved up over the target area of the object scanned by this -135- This paper is suitable for gs Home materials (CNS) A4 size (21GX297)-588158 A7

ij

588158 A7 B7

5. Description of the invention (134) The self-calibration feature can then be applied to each scanning element formed by each pair of wave source and detector, and can illuminate multiple recombined magnetic waves with different waveform characteristics, for example, or on different or the same carrier Overlapping identical or different signal waves, etc. The configuration of the wave source can also irradiate this electromagnetic wave continuously, periodically, or intermittently. As discussed in patent '972, however, the wave source and detector are usually aligned according to some semi-empirical design rules. These semi-empirical designs are expected to improve the accuracy, reliability, and / or reliability of the baseline. The estimates of regeneration and chromophore quality are absolute. This design rule is: (1) the scanning unit preferably includes at least two wave sources and at least two wave detectors; and (2) any wave source in a scanning unit and The distance between the waveform detectors does not exceed a critical sensitivity range of the waveform debt detector, which can range from, for example, a few centimeters to 10 centimeters, especially about 5 centimeters for human and / or animal tissue. In addition, the wave source and the The configuration of the detector is defined as a scanning unit with a continuous scanning area in the entire area, so a single measurement of the scanning unit can generate an output signal covering the entire scanning area. For this purpose, the wave source and the detector can be no greater than one The critical distance is separated by the distance. The best interval between the source and the detector is usually chosen by a person skilled in the art, and this interval can be determined by many factors For example, the optical properties of the media (for example, absorption coefficient, diffusion coefficient, etc.), the radiation emission capability of the wave source, the detection sensitivity of the waveform detector, the structure of the scanning unit and components, the wave source and / or detection on the optical probe The number of detectors, the geometric configuration between the wave source and the detector, the composition of the wave source and the detector in each of the scanning elements and each of the scanning units, etc. _ -137- Standards apply to China National Standard (CNS) A4 specifications (210X 297 mm)

Order

Line 588158

DESCRIPTION OF THE INVENTION The use of a wave filter The optical imaging system includes a filter unit to improve the signal-to-noise ratio of the output signal and the signal-to-noise ratio including the baseline and the self-calibrated output signal. Therefore, the filter units can be configured to process the output signals before they pass through the analyzer and processor i. When a single output signal is obtained in each target area (or media), the filter unit preferably includes a low-pass filter to remove high frequency noise from the output signal. However, when the configuration of optical probes can produce multiple output signals for a single target area, their signal-to-noise ratio can also be improved by various averaging methods of arithmetically or geometrically averaging the multiple output signals. In addition, the filter unit can weight the average of the previous output signals or the entire average. This filtering can be performed in analog and / or digital mode. The use of a wedge unit The optical imaging system also includes a wedge unit to smooth out sharp changes in the amplitude of the output signal phase or data point or to form a peak. Therefore, the system conversion unit includes an insertion algorithm, or a similar circuit or software. Signal Analyzer / Processor Configuration The previous signal analyzer and signal processor configurations of the present invention can be operated on a real-time basis. For example, as long as the optical probe is placed in the first target area and the waveform detector generates a first output signal, the signal analyzer can identify similar amplitude signals before the optical probe is moved or repositioned in an adjacent target area. The first output signal section, and the signal processor can provide a self-calibrated first output signal. Before moving the optical probe to another target area, the configuration of the image processor can also provide the required image. Due to this paper ruler's wealth (CNS) 588158

Therefore, the A-Learning I system of the present invention can generate two-dimensional and / or three-dimensional images of chromophores or their properties on the basis of essentially the shaw.

The configuration of the signal analyzer of the present invention can also identify different points or portions of the output signal by using various algorithms different from those described above. For example, the signal analyzer can calculate and evaluate other characteristics of the output signal, such as the number of concaves or convexes of the output signal that can be evaluated through their first derivation (or slope), the number of maximum or minimum 値 in the region that can be evaluated through their second derivation The curvature of the output signal represented by the position, etc., instead of focusing only on the amplitude of the output signal. For example, when the output signal shows a slight increase or decrease, this deviation point is indeed recognized by analyzing the first and second derivations of the output signal. In addition, by considering these auxiliary parameters and the amplitude of the output signal, different sections or sections can be identified along the output signal, where each section or section is presented with a different contour (for example, flat, oblique, convex or concave). Order

In general, an output signal portion with a flat upper contour and a similar amplitude is a region representing a target region, which represents that the output signal portion is composed of, for example, a homogenous substance of normal tissues and cells. In contrast, a portion of the output signal having a curved profile and different amplitudes generally indicates that the portion of the target area corresponding to this portion has a media background different from, for example, normal tissues and cells. Therefore, although it may only reflect normal connected structures or Shenjing and vascular tissues, this region may not include abnormal cells. Confirmation of the boundary between this normal and abnormal area can also be achieved by analyzing the first and / or second derivation of the output signal. The signal analyzer of the optical imaging system of the present invention is configured with an identifiable flat (or linear) part, or the rest of the output signal, or -139- 588158 V. Description of the invention (137) Non-flat or curved part. As mentioned above, the signal analyzer can compare the amplitude of each point of the output signal with a critical amplitude or range. Alternatively, the signal analyzer can divide the output signal into multiple shorter sections to obtain the average amplitude of the individual sections, and compare this average amplitude with the critical amplitude or range, followed by the maximum or minimum amplitude of a region or the whole domain. However, the output signal can change its amplitude in flat and non-flat parts, regardless of the critical chirp. Therefore, the signal analyzer can provide a second cut-off amplitude or a cut-off range of the derived 値, so any output signal part that fails to meet the cut-off threshold 不 is not included in the flat or non-flat part. 0 Baseline analysis A specified area of the media obtains a correct baseline of the output signal. Other baselines can be obtained from adjacent target areas and compared with baselines from a particular target area. When the baselines obtained from different target areas are not substantially the same in the media, the self-calibrating optical imaging system of the present invention can achieve this by providing algorithms and methods for determining a composite baseline. 0 Figures 45A to 45C according to the present invention For further examples of output signals generated by the waveform detector, each graph represents output signals obtained from the first, second, and second target regions, respectively, and each target region is composed of multiple scanning elements. Covered with scanning unit. As shown in the figure, the output signals of FIGS. 45A and 45C have different vibrations, but the flat contours are in the first and third target regions, respectively. However, the output signals of FIG. 45B are reduced along the axis of the second target. When the amplitude of the output signal in Figure 45A is not substantially different from that in Figure 45C, or the difference between them is in a pre-selected range • 140- This paper size applies the Chinese National Standard (CNS) A4 specification (210 X 297 mm) 588158 A7

The average of the data points of the output signals of Figs. 45A to 45C can generate a baseline of the media. However, when this difference is negligible, FIGS. 45A and 45 (: show that one of the first and third target regions is mainly composed of normal tissues or cells' and its output signal is a background output signal representing the media, However, 'the other of the two target areas is composed of abnormal tissues or cells, so' its output signal will be upward due to the appearance of abnormal cells with tissues or lumps sufficient to cover the entire size of the first or third target area Skew or deviate downward. In the case where the signal analyzer provides a critical amplitude or range supplied by the operator, the signal analyzer can compare the data points of the target area and locate the selected portion of the output signal for evaluating the baseline. However When the signal analyzer recognizes the selected part from the output signal itself (for example, by identifying the maximum or minimum value of the region or the whole region, and calculating the critical amplitude or range), the signal analyzer must identify which data points can be used to calculate the media baseline. In a specific embodiment, the baseline can be obtained from an adjacent target area, and the baseline can be obtained from the bases obtained from FIGS. 45 A and 45C. In comparison, when regions with higher (or lower) amplitudes are forced into a region, and regions with lower (or more) amplitudes tend to surround forced regions, regions with lower (or higher) amplitudes are more likely to be Background of normal tissue or cells, however, areas with higher (or lower) amplitude are more likely to include normal ridges, weaves, cells, or lumps. Alternatively, the signal analyzer can provide operators with different amplitude ridges and allow manipulation The operator manually selects normal and / or abnormal areas.-In some cases' output signals obtained from multiple different target areas can produce similar but different baselines. The signal analyzer can then be configured to obtain a composite or average from multiple Baseline, and the use of synthetic baselines will be from the media 鳢 -141-this paper size applies Chinese National Standard (CNS) A4 specifications (210 X 297 mm)

Binding

Line A7 B7 V. Description of the invention The output signals obtained for all target regions of 139 are normalized. As mentioned above, this multiple baseline can be arithmetic, geometric, weighted, or entire financial = Allow the operator to select a single-baseline and specify it Synthesizing = analysis, or each output signal (or a group) can be normalized through the calculated baseline. When the signal processor produces ± self-calibrating signals and the image processor constitutes a multi-region image (for example, each scan area or target When there is one area), a composite image can be achieved based on the individual baseline images used in the target area (or a group). When the physiological media includes various anatomical structures with different optical shells, this specific embodiment It can prove to be particularly advantageous. For example, a self-calibrating optical imaging system can scan the brain to detect potential or actual pulsations. Brain tissue and the surrounding cranium normally have at least minimal different optical characteristics, and the thickness of the cranium varies in different parts of the brain. When The synthetic baseline is calculated from multiple baselines and is used to make the output measured from different parts of the brain No. Normalization 'All pixels have normally the same range, that is, the same brightness ratio or color ratio on the entire media. Although the image has a consistent background level, it helps the doctor to make a comparative diagnosis, but when it is in When the target area normalized by a baseline with a higher amplitude is dark, he or she cannot find a slight pulsation. On the contrary, when the image is composed of self-calibrated output signals based on individual baselines. Therefore, Mild pulsation is a compromise between supply and demand in the image, but the physician must analyze each image individually. To avoid this inconvenience-the method is to increase the contrast between the background anatomy and abnormal tissue included in each target area. For example As long as any possible abnormality is identified, the image element can identify the boundary line, and the corresponding boundary line and / or abnormal signal are added, so that the amplified signal will not be able to

Du 158 A7 Invention Description The color or brightness ratio of the transmitted image is dimmed according to the composite baseline. A special symbol or color can also be added to each enhanced signal, and it can also alert the physician. It can be understood that the previous configuration of the optical imaging system of the present invention can be modified without departing from the scope of the present invention. For example, the signal analyzer, signal processor, and previous functional units of the image processor may be further differentiated or combined, or implemented in another part of the optical imaging system. The configuration of this functional unit can also form different operational connections between them. For example, the receiving order 7C of the signal analyzer can be combined with the sampling unit. Similarly, the comparison unit 7L of the signal analyzer and the selection unit can be combined. The configuration operation of the image processor can also communicate with this unit of the signal analyzer. Self-Calibration Application System The previous self-calibration optical imaging systems and methods of the present invention can also be used to provide temporary changes in the amount of blood or fluid in a target area of a media. As discussed in the patent titled Optical Imaging System with Movable Scanning Unit, the oxygen and deoxyhemoglobin concentrations can be calculated based on an algorithm disclosed in Patent, 972. As long as this concentration is obtained, their sum (that is, total erythroglobin / Chen) is also obtained. By sampling the output signal from the waveform detector of the target area, the variation of the total erythrocyte concentration can be obtained. By assuming that the blood cell volume juice (that is, the percentage of blood red blood cell volume) flows through the target area and remains fixed, the temporary change in the blood volume of the target domain can be directly changed from the temporary change of the blood volume meter in the target area. In this case, the photon; iV imaging system can calculate the baseline of the output signal and provide a self-aligned output signal as described above. Alternatively, the optical imaging system can also be used from the same purpose __—___- 143-CNS Standard for this paper ------

Binding

Line 588158

The target area calculates multiple baselines, obtains-temporarily averaged synthetic baselines, and provides an output signal that temporarily compensates for self-calibration. Although the previous disclosure of the present invention is mainly directed to self-calibration of an optical imaging system for providing a chromophore-like spatial distribution image, the present invention can also be applied to an optical imaging system for generating a time distribution image. For example, optical probes can be configured to scan-special target areas. ⑼The target area changes the output signal detected at different time intervals. The signal analyzer and processor can establish a baseline and provide a self-calibrating first output signal. The image processor may then construct an image frame that represents a temporary change in the chromophore properties of the target area. Alternatively, the optical imaging system can also provide a temporary average baseline and a temporary compensation line calibration output signal as described in the previous paragraph. Note that recorded changes in the nature of the chromophore are usually related to the relevant chirp, so no absolute chirp can be provided directly. However, as long as an absolute unit of this property is determined at any reference time frame, previous or subsequent changes in this property can be converted to absolute unitary by continuously calculating the absolute unit forward or backward. The self-calibration configuration and method of the present invention can be used in an optical imaging system to obtain a three-dimensional distribution image of chromophores in a physiological medium. As mentioned above, the electromagnetic wave irradiated through the wave source can pass through an area volume defined by a target volume and a preselected depth or dark gray of the medium. Therefore, a waveform detector can generate multiple output signals, each of which can carry optical information for a particular target layer of the media. As long as this output signal is obtained, a baseline can be evaluated by the previous algorithm described here. For example, a single baseline can be assigned to the entire target volume. Alternatively, multiple baselines can be defined at each depth or layer of the target volume. In the case of multiple baselines, the average of these baselines is -144. This paper size is applicable to the Chinese National Standard (CNS) A4 specification (210 X 297 mm) 588158 A7 _______B7 V. Description of the invention (142) or normalization is related to each other Relevant, so the resulting 3D image can be constructed with consistent gray harmonics or color levels. Although any analysis or mathematical method can be used to obtain a solution to the waveform equation ', the algorithmic unit of the present invention may preferably be combined with the solution disclosed in Patent, 972. For example, the concentration of erythropoietin [Hb], the concentration of oxyhemoglobin [HbO], and the absolute value of oxygen saturation so2 can be obtained from equations (8a) to (8d) of the patent '972, respectively. Alternatively, the algorithmic unit can also adopt an iterative method that is too arbitrary as disclosed in the patent '972, in which the absolute 値 of [Hb], [HbO], and S〇2 can be obtained through the patent, Equation (17a) To (17c). In yet another option, the change in chromophore properties can be changed by evaluating the optical characteristics of the target area of the media. For example, changes in oxygen and deoxyhemoglobin concentrations can be calculated from the difference in their dissipation coefficients, and secondly can be measured by electromagnetic waves with different wavelengths. In a numerical method, the photon diffusion equation can be based on, for example, the optical application of Keijer et al., Pp. 1820_1824 (1988) " Opticai Diffusion in Layered Media " and Haskell et al., Journal of Optical Society of America, 1994 , A, LL ', 2727-2741, name " Boundary Conditions for Diffusion Equation in Radiative Transfer " Details of the previous party 4 'are also provided in patent · 972. In each of these methods, the output signal can be calibrated against a baseline obtained by one of the previous methods. -The configuration of the wave source and the detector of the optical probe of the optical imaging system of the present invention can satisfy a specific embodiment disclosed in the patent '972, that is, the configuration of the wave source and the detector has substantially the same near and far distances. distance. For example, at -145- this paper size applies the Chinese National Standard (CNS) A4 specification (21〇χ 297 mm)

Binding

Line 588158 A7 ------- B7 V. Description of the Invention (143) In the scanning units 125a, 12A of 42A and 42B, a first wave between a first wave source and a first wave detector foot The distance is substantially the same as a second close distance between a second wave source and a second waveform detector. In addition, a first long distance between the first wave source and the second waveform detector is substantially the same as a second long distance between the second wave source and a first waveform detector. The main advantage of this symmetrical configuration is that the electromagnetic waves irradiated through the wave source can be transmitted, absorbed, and / or diffused in the entire area or volume of the medium scanned by the scanning unit. Therefore, the scanning unit can provide consistent coverage of the target area of the media. Therefore, the accuracy and reliability of the output signal (eg, an improved signal-to-noise ratio) generated by the waveform detector can be improved. The prior self-calibrating optical imaging systems, optical probes, and methods of the present invention can be used in non-invasive and invasive procedures. For example, a previously self-calibrating light pre-grabber could be a non-invasive configuration on a target area on the outer surface of the test object. Alternatively, a miniaturized self-calibrating optical probe can be implemented on the tip of a catheter that is invasively disposed on an internal target area with an object. Previous optical imaging systems and optical probes can also be used to determine the intensity properties of chromophores, such as volume, mass, volumetric flow rate, or mass flow rate. As mentioned above, this chromophore includes, for example, media solvents, solutes dissolved in the media, and / or other substances included in the media, each of which interacts with electromagnetic waves transmitted through the media, but is not limited to cytochromes , Hormones, enzymes, spirits and chemical transporters, proteins, gall, sterols, apoproteins, fats, sugars, cytosomes, blood cells, cytosols, oxyhemoglobin, deoxyhemoglobin, and water. Specific examples of chromophore properties may include, but are not limited to, oxygen and deoxyhemoglobin concentrations, oxygen saturation, and blood volume. _ -146- This paper size is in accordance with Chinese National Standard (CNS) A4 (210 X 297 mm). E · Examples can learn that the adjustment of the previous optical imaging system, optical probe, and method can provide different chromophores or properties. Distributing the image. Because different chromophores can often respond to electromagnetic waves with different wavelengths, the processing of this optical imaging system and the probe's wave source can irradiate coercive waves that can interact with preselected chromophores. For example, a near-infrared wave ' having a wavelength between 600 μm and 100,000 nm, such as about 6900 μm and 8300 nm, may be suitable for measuring the distribution pattern of heme and its properties. However, near-infrared waves having a wavelength between 800 nm and 1,000 μm, such as about 900 nm, can be used to measure the water distribution pattern in the media. The optimal wavelength selection for detecting a particular chromophore is usually determined by the optical absorption and / or scannability of the chromophore, the operating characteristics of the wave source and / or the detector, and the like. The clinical application of the previous optical imaging system, optical probe, and method of the present invention can detect tumors or pulsations in the chest, brain, and any other part of the human body. Among them, the previous optical imaging method of a scattering optical local X-ray machine is applicable. . Previous optical imaging systems and methods can also be used to evaluate the written fluid in and out of transplanted organs, limbs and / or autograft, or allograft body parts or tissues. Configurations of previous optical imaging systems and methods can replace, for example, ultraSongram, X-ray, EEG, and laser hearing diagnostics. In addition, the modification of this optical imaging system and method can be applied to a variety of different physiological media with complex photon diffusion and / or non-flat outer-surfaces. It is further noted that previous optical imaging systems, probes, and methods = were applied to traditional optical imaging equipment, where the wave source and detector were quite solidly configured in their probes. field~,

The paper size is generally Chinese National Standard (CNS) A4 (210 X 297 mm) 588158 A7 B7 V. Description of the invention (145 You can understand the optical imaging system, optical probe, and method. The invention can be combined or applied in the United States Patent case number (unknown) name 'f Optical Imaging System with Moveable Scanning Unit " and another US patent case number (unknown) name " Self-Calibrating Optical Imaging System ", another US patent case number (unknown) name " Optical Image System for Direct Image Construction ", and other related inventions and specific embodiments disclosed in another U.S. patent number (unknown) name " Optical Imaging System with Symmetric Optical Probe ", the above patents were issued in 2001 2 It was filed on the 6th, and it is listed here for reference only. The following example describes an optical imaging system, optical probe, and method according to the present invention. As a result, the following optical imaging system can be provided in a target area of human breast tissue Reliable and accurate image of two-dimensional distribution of blood volume and oxygen saturation. The image system 500 is configured to obtain a two-dimensional distribution image of blood volume and oxygen saturation in a target area of a female human chest. FIG. 61 is a diagram of a prototype optical image system according to the present invention. The prototype optical image system 500 typically includes a handle 501 and a Main package 505. The handle 501 is made of polyvinyl chloride (PVC) and acrylic appliances, and two control switches 503a, 503b are provided to control the operation of various components of the system 500. The main package 505 includes a main body 51 〇, a movable component 520, an actuator element 530, an image element (not shown), and a pair of guide rails 560. The shape of the main body 510 is the same substantially square block (3 075 " χ2 8 " χ2 63 „ ) -148- This paper size applies to China National Standard (CNS) Α4 specification (21〇χ 297 mm)

Order

Line 588158 A7 B7 V. Description of the invention (146) and provide a retaining wall along its side. The configuration of the main body 510 can be coupled with the rectangular movable component 520 (1 · 5 " χ2 · 8 " χ1 · 05 "), and its design can be linear along a path defined by the guide 560 and substantially parallel to the end of the main body 510 Conversion. The configuration of the movable unit 120 has a wave source-detector configuration similar to that of Fig. 3 (c). For example, the movable assembly 520 includes two wave sources 522 Si and S2, each of which can irradiate a turtle wave having a different wavelength. In particular, each skin source 522 includes two laser diodes HL8325G and HL6738MG (ThorLabs, Inc, Newton, NJ), where each laser diode can be irradiated with a wavelength of 690 nm and 830 nm, respectively. Electromagnetic waves. The movable component 520 also includes four identical waveform detectors 524, such as photodiodes D !, D2, D3, and D4, (OPT202, Βιπτ-Brown, Tucson, AZ). These are essentially linearly inserted between the wave sources 522 . The wave source 522 and the detector 524 are substantially linearly separated at the same distance, so the scanning unit can pass through the wave source 522 and the detector 524 (for example, a first scanning unit of S !, 〇1, 04, and 32, and 31 A second scanning unit), 02, 03, and 32), and can meet the short-distance and long-distance requirements, or symmetrical requirements of the patent '972. The actuator element 530 includes a high-resolution linear excitation type stepper motor (model 26000, Haydon Switch and Instrument Inc., Waterbury, CT) and a motor controller (Spectrum PN 42103, Haydon Switch and Instrument Inc.). The exciter element 530 is mounted on the main body 510 and can be engaged with the movable component 520 so that it can be fixedly placed along the linear path 560 and fixedly connected to the main package 505 to linearly transform the movable component 520. A pair of precise guides (model 6725K11, McMaster-Carr Supply, ____ -149-This paper size applies to China National Standard (CNS) A4 (210X297 mm)

Order

588158 A7 B7 V. Description of the invention (147)

Santa Fe Springs, CA) can be used as a rail 560. The image element is provided in the handle 501 and includes a data acquisition card (DAQCARD 1200, National Instruments, Austin, TX). The main package 505 is made of an acrylic appliance and is formed by opening at the front end. Perspex Non-Glare Acrylic Sheet (Liard Plastics, Santa Clara, CA) is a face plate 506 installed on the packaging 505, and can be used as a protective screen to protect the wave source 522 and the ridge detector 5 from mechanical damage. In terms of implementation The movable component 520 is placed at its starting position, that is, the distal end from the left side of the main body 510. An operating unit can activate the main power of the system 500, and activate the wave source 522 and the detector 524 by executing the scanning system software. A human chest can be prepared, and the main body 5 10 of the optical imaging system 500 is placed on the chest, so the sensors 522 and 524 of the movable component 520 are placed on the first target area of the chest and lined up with appropriate light coupling. The first target area is scanned by pressing a control switch 503a on the handle 501. The wave source 522 can irradiate the first target region with a preselected wavelength, and the waveform detector 524 can detect the electromagnetic wave from the first target region and start scanning. The exciter element 530 may linearly and gradually transform the movable assembly 520 along the main body 510-end of the guide rail 560. The wave sources 522 can be synchronized so as to ignite their laser diodes in a continuous selection. For example, the configuration of a first laser diode of the wave source S i can be seen to emit electromagnetic waves with a wavelength of 690 nanometers, and the wave detector 524 can detect the electromagnetic waves and generate a first set of outputs in response to them Signal, during this first irradiation and detection cycle, which typically lasts 1 microsecond (with a duty cycle in the range of 1: 10 to 1: 1, 000), all other laser diodes can be turned off in half Interference-150-This paper size applies to China National Standard (CNS) A4 (210X297 mm)

Order

Line 588158 A7 B7 V. Description of Invention (148) Noise is minimal. After the irradiation and detection are completed, the first laser diode of the wave source core can be turned off, and the first laser diode of the wave source S2 can be turned on to irradiate electromagnetic waves with the same wavelength of 690 nm. The waveform detector 524 can detect electromagnetic waves and generate a second set of output signals. Other laser diodes can remain in the off position during this second cycle of illumination and detection. A similar procedure can be repeated for the second laser diode of the wave source Si, and then for the second laser diode of the wave source & where two second laser diode configurations can continuously illuminate Electromagnetic waves. The image element is also synchronized with the wave source 522 and the detector 524, and can sample the output signals of the previous group at a preselected sampling rate. In particular, the configuration of the image element can process the output signal by defining a first and a second scanning unit, where the first scanning image unit is composed of the wave source core and h, and the waveform detector Di * D4, and the second The scanning unit is composed of the wave source core and S2, and the waveform detectors D2 and D3. The first and second scanning units have a wave source-detector configuration, which can meet the symmetrical requirements of the patent, 972. Therefore, the oxygen and deoxyhemoglobin concentrations can be obtained by the equations (la) to (ld), and the oxygen saturation s02 can be obtained by the equation (le). In addition, the blood volume (that is, a temporary change) can be calculated by evaluating changes in the hematocrit in the target area. The exciter element 530 is also synchronized with the previous irradiation and detection, so before the wave source 522 and the detector 524 move to the next adjacent area of the target area through the exciter element 53, they can scan the entire first of the target area. region. When the exciter element 530 transitions the movable component 52o along a preselected path, the movable component 520 can scan a continuous area of the target area. When the movable assembly 52

588158 A7 B7 V. Description of the invention (149) When the other end of the main body 510 is reached, the exciter element 530 can linearly transform the movable component 520 into that it starts to be placed. The previous irradiation and detection procedures may also be repeated in the same or different areas of the target area during the backward linear movement of the movable component 520. After the linear reciprocating motion of the movable component 520 is completed and the scanning process is completed, the operator can press other control switches 503b to transmit a signal to the image element that starts the image construction process, and provide an oxygen-saturated spatial simulation in the target area Two-dimensional images and temporary changes in blood volume. 47A and 47B are two-dimensional images of normal and abnormal chest blood volume, respectively, both of which can be measured by the optical imaging system of FIG. 46. In addition, FIGS. 48A and 48B are two-dimensional images of oxygen saturation in normal and abnormal chest tissues, respectively, both of which can be measured by the optical imaging system of FIG. 46 according to the present invention. As shown in the figure, the provision of an optical imaging system enables normal tissues to have higher oxygen saturation (for example, more than 70%) in the region of maximum blood volume. However, higher oxygen saturation in the corresponding area of abnormal tissues can be as low as 60%. It can be understood that, although various specific embodiments of the present invention have been described in detail, the foregoing merely illustrates rather than is limited to the scope of the present invention as defined in the subsequent patent applications. Other related specific embodiments, viewpoints, advantages, and / or modifications are within the scope of the following patent applications. -152- This paper size applies to China National Standard (CNS) A4 (210X 297mm)

Order

line

Claims (1)

588158 A8 B8 C8 D8 Patent Application No. 0909119152 Chinese Patent Application Replacement (February 1993) 6. Scope of patent application ---- * ι 1. A system for determining the chromophore concentration of physiological media, including: a wave source module for irradiating at least two sets of two magnetic radiations with different waveform characteristics In the medium; I-radiation; and a detector module for detecting electromagnetic transmission through the medium and a processing module for determining electromagnetic radiation radiated from the wave source module and passing through the detector The absolute value of at least one of the chromophore concentrations detected by the module; wherein the decision is based on the intensity measurement of the continuous wave electromagnetic light emission from the wave source module. 2. The system according to item 1 of the patent application scope, wherein the chromophores are erythrocytes, and the processing module can determine the concentration of at least one of oxyhemoglobin and deoxyhemoglobin. 3. The system according to item 1 of the scope of patent application, wherein the configuration of the wave source and the detector module can be operated on a physiological medium, and the operation on the physiological medium includes at least one of an organ, a tissue, and a body fluid. Cell. 4. The system according to item 3 of the patent application, wherein the processing module is configured to detect abnormal cells. 5. The system according to item 4 of the patent application, wherein the abnormal cells are tumor cells. 6. The system according to item 4 of the patent application, wherein the cells are distributed in at least one of the epidermis and an inner tissue dermis including at least one of a brain, a heart, a lung, a liver, and a kidney. /By. 7. If the system of item 4 of the scope of patent application is applied, where the cells are transplanted on a paper scale suitable for the country ® Family Scale (CNS) A4 specification (21G X 297 mm) 588158 Α Α8 Β8 C8 D8 Range tissue cells. 8. The system of claim 7 in which the transplanted tissue includes at least one of a brain, a heart, a lung, a liver, and a kidney. 9. The system of claim 1 in which the waveform characteristics include at least one of a wavelength, a phase angle, an amplitude, a harmonic, and a combination thereof. 10. The system of claim 9 in which a first group of the electromagnetic radiation has a first wavelength, and a second group of the electromagnetic radiation has a second wavelength ', and the second wavelength is different from the First wavelength. 11. The system of claim 1 in which a first group of the electromagnetic radiation includes a first carrier wave, and a second group of the electromagnetic radiation includes a second carrier wave, and the second carrier wave is different from the first carrier wave. Waveform characteristics of a carrier. 12. The system according to item i of claim 1, wherein the waveform characteristics include at least one of a wavelength, a phase angle, an amplitude, a harmonic, and a combination thereof. 13. The system of claim 1 in which the processing module can determine the absolute value by using one or more parameters that describe the optical interaction properties of the electromagnetic radiation of the medium. 14. If the system of claim 13 is applied, the processing module uses an arithmetic formula including a parameter, which is determined by the following: the optical properties of the medium and the configuration of the wave source module and the detector module . 15. The system of claim 14 wherein the arithmetic formula includes a polynomial of at least one of the concentration and the concentration ratios. 16. If the system of applying for the patent item No. 丨 3, the arithmetic formula essentially includes an item, which is determined by one or more of the following: the light of the media-2-This paper standard applies to the country of China The standard (CNS) A4 specification (210X297 mm) 588158 is replacing the year 9a 12 (F; J, the scope of the patent application, and the configuration of the wave source module and the primary tester module. This item is approximately a constant. 17 The system of patent M, please use the following arithmetic formula for the processing module: 1 = αβ7Ι〇exp {-BL 5 Σ, (8i Cl) + σ}, where I. is transmitted through the wave source module. The intensity of the radiated electromagnetic waves; i is the strength of the electric money detected by the detector module, U is related to at least one of the wave source modules and the media-see m and the detector modules and A parameter related to at least one of the media; 7 is a parameter related to at least one of the wave source module, the detector module, and the media; B is the length of the optical path of the electromagnetic wave passing through the media Is a parameter and is related to the wave source module, the detector module, and the media. ; L is a parameter describing the distance between the wave source module and the detector module; 5 is a proportionality constant, and at least one of the wave source module, the detector module, and the medium Any of the related parameters: Si is a parameter describing an optical interaction between an electromagnetic wave in the medium and a chromophore; Ci is a variable representing the concentration of the chromophore ; And σ is a proportionality constant, and any one of parameters related to at least one of the wave source module, the detector module, and the media. 18. If the system of the 17th scope of the patent application , Where the parameter 6 is a path length factor. 19. For the system in the 17th scope of the patent application, the parameter 1 is at least one of a media extinction coefficient, a media absorption coefficient, and a media scattering coefficient. Paper size applies Chinese National Standard (CNS) Α4 size (210X 297 mm) 588158 f is replacing 8 years 9a service 26 said A8 B8 C8 D8 Patent application scope 20. The system according to item 1 of the scope of patent application, wherein the wave source module includes at least one wave source 'and the detector module includes at least two waveform detectors. ", 21 · If the system of the first scope of the patent application, the wave source module includes at least two wave sources, and the detector module includes at least one waveform detector. 22 · The system of the first scope of patent application Wherein, the wave source module has a first and second wave source, and the detector module has a first and second detector. 23. The system of item 22 in the scope of patent application, wherein the processing module Use the arithmetic formula: Imn = am / SnyI〇m eXp {_Bmn (Si Ci) + σ}, where Ϊ., !!! is the intensity of the electromagnetic wave irradiated through an m-th wave source; Imn is irradiated through the m-th wave source And the intensity of the electromagnetic wave detected by an n-th waveform detector; am is a parameter related to at least one of the m-th source and the medium; / ^ is related to the n-th waveform detector and the medium A parameter related to at least one; 7 is a proportionality constant, and a parameter related to at least one of the m-th wave source, the n-th waveform detector, and the medium; Bmn is a description of the electromagnetic wave optics by the medium Path length, and the m-th wave source, the n-th waveform detector, and the media A parameter related to at least one of them; Lmn is a parameter indicating the distance between the m-th wave source and the n-th waveform detector; 5 is a proportionality constant, and the m-th wave source and the n-th waveform detection Any one of a parameter related to at least one of the measurement medium and the medium; Si is a parameter describing an optical interaction between the electromagnetic wave and an i-th chromophore included in the medium; Q is a parameter The i-th hair color -4- This paper size applies to Chinese National Standard (CNS) A4 specifications (210 X 297 mm) "° £ 1 C8 D8 VI. A variable of the concentration of the patent application range; and σ is a proportional constant And any one of the parameters related to the third wave source, the n-th waveform detector, and at least one of the media, wherein the subscripts m and η are non-zero positive integers. 24_ 如The system of claim 23, wherein the parameter Bmn is a path length factor related to at least one of the m-wave source, the n-th waveform detector, and the media. 25. If the scope of patent application is 23 System, where the parameters r and 5 are approximately 1, so the equation can be simplified to Imn-Q m 石 nI〇, m exp {_Bmn LmnEj (Si Ci) + σ}, 26. For the system of the 22nd scope of the patent application, in which the wave source and the waveform detector can be configured, so the first wave source The distance from the first waveform detector is substantially similar to the distance between the second wave source and the second waveform detector, and the distance between the first wave source and the second waveform detector is substantially similar. The distance is substantially similar to the distance between the second wave source and the first waveform detector. 27. The system according to item 1 of the patent application range, wherein the wave source module has at least M wave sources, and the detector The module has at least ν waveform detectors, where M and N are integers greater than 1, and the configuration of these wave sources and waveform detectors is such that between a Mγ wave source and a Ni-detector The distance is substantially similar to the distance between an M2-wave source and an N2-waveform detector, and the distance between the Mγ-wave source and the N2-waveform detector is substantially similar to the M2-wave detector -The distance between the wave source and the Ni-waveform detector, where the% and 2 are at Integer between 1 and Μ, and where 川 和 仏 is between 1 and N -5- This paper size applies the Chinese National Standard (CNS) A4 specification (210 X 297 mm) 588158 8 8 8 8 A BCD Integer for patent application. 28. The system according to item 1 of the patent application scope, wherein the detector module has two or more waveform detectors arranged along a line, and the wave source module has at least Two wave sources. 29. The system according to item 1 of the patent application scope, wherein the detector module has M22 waveform detectors arranged substantially along a line. 30. The system according to item 1 of the patent application scope, wherein the detector module has at least 3 waveform detectors arranged substantially along a line. 31 · —A system for determining the chromophore concentration of a physiological medium, comprising: one or more wave sources for irradiating the medium with at least two groups of approximately infrared electromagnetic radiation having different waveform characteristics; or Multiple detectors to detect the electromagnetic transmission transmitted through the medium; @ input device to input the input parameter data; and a processing module to determine the concentration of at least one of the concentrations The absolute value, where 泫 is determined not by measuring the phase characteristics of the electromagnetic radiation received from the one or more detectors, or by the media responding to an electromagnetic pulse from the one or more wave sources. 32 · A system for determining the chromophore concentration of a physiological medium, comprising: at least one wave source for irradiating at least two sets of electromagnetic radiation with different waveform characteristics on the medium; -6- this paper Standards are applicable to China National Standard (CNS) A4 specifications (210X297 mm) '' ------- 588158 to '1 '93. Years. Change to A8 B8 C8 D8 At least one detector in the patent application park is used to detect electromagnetic light transmission through the medium; a processor is coupled to the at least one detector to calculate the absolute values of the concentrations and the One of the ratios of equal concentration, where the calculation is based on the intensity measurement of continuous wave electromagnetic light emission from the wave source module. 33. A method for determining the concentration of chromophore in a physiological medium by using a measurement system having at least one wave source and at least one waveform detector, wherein the electromagnetic waves can be irradiated through the at least one wave source, by Transmitted through a physiological medium and detected by the at least one waveform detector, the method includes the following steps: irradiating with at least two sets of electromagnetic radiation having different waveform characteristics to obtain a plurality of measurements; An arithmetic formula for the measurement is provided to the system parameters and the parameters related to the medium; the parameters related to the wave source and the detector are removed from the provided arithmetic formula; and the absolute value of at least one of the concentrations such as children is determined, wherein the decision Is based on continuous wave electromagnetic radiation and predetermined intensity measurements of chromophore-related parameters' and is not based on measuring the electromagnetic light-emitting phase characteristics received from the one or more detectors, or the medium responds to the response from the one or more An electromagnetic pulse from a wave source. 34. If the scope of the application for the patent No. 33 Xi Shi Tu Pu, ... J Bei < Wan Fa, where the arithmetic formula of a child includes a waveform equation, the expression is as follows: 1 = a ^ rI〇exP {. BL ^ i (gi 〇ι) + σ}; I paper size applies Chinese National Standard (CNS) A4 ^^ 1〇X297 公 宝 ^ ----- Where I. Is the intensity of the electromagnetic wave irradiated through at least one wave source module; I is the intensity of the electromagnetic wave detected through at least one detector, α is a parameter related to the at least one wave source and the media; Θ is related to at least one detector A parameter related to the media; T is a proportionality constant, and any one of the parameters related to at least one wave source, detector, and media; B is a parameter indicating the length of the optical path of the electromagnetic wave passing through the media And is related to at least one wave source, detector, and media; L is a parameter of the distance between the wave source and the detector >ruler; 5 is a proportionality constant, and is related to these wave sources, detectors Any one of the parameters related to at least one of the media; Si is a parameter describing a cross-interaction between the electromagnetic wave in the media and an i-th chromophore; q is the i-th A variable of chromophore concentration; and σ is a proportionality constant, and any one of parameters related to at least one of the wave source, the detector, and the medium. A method for determining a chromophore concentration in a physiological medium by using a measurement system having at least one wave source and at least one waveform detector through the application of a wave equation. The wave equation has the following expression: Imn = ^ m / 3nrI. , m exp {-Bmn Lmn δ (8i Ci) + σ} ^ where I0, m is the intensity of the electromagnetic wave irradiated through the m-th wave source; Imn is irradiated through the m-th wave source and through the n-th waveform detector Intensity of the detected electromagnetic wave; am is a parameter related to the m-th wave source and the medium; y3n is a parameter related to reading the n-th wave detector and the medium; r is a proportionality constant, and related to the wave source and the detector Any one of the parameters related to at least one of the media; Bmn is the length of the optical path of the electromagnetic wave passing through the media, and it has -8 with the m-th wave source, the n-th waveform detector, and the media -This paper size applies to China National Standard (CNS) Α4 (210 X 297 mm) C8 D8 " ^ 7 ^-parameters related to the scope of patent application in the sixth year, Lmn is a parameter indicating the distance between the m-th wave source and the n-th wave detector; 5 is a proportionality constant, and at least Any one of a wave source, a waveform detector, and a parameter related to the medium; the heart is a parameter describing an optical interaction between the electromagnetic wave and the chromophore in the medium; Ci is a parameter representing the A variable of the i-th chromophore concentration; and σ is a proportionality constant and any one of a parameter related to at least one of a wave source, a waveform detector, and a medium, the method includes the following steps: Irradiate a first and second set of electromagnetic radiation with different waveform characteristics, and measure signals received from the medium to obtain two sets of equations about the measurement signals with unknown parameters in the waveform equation; by using the first and The second set of equations is obtained by removing at least one of the parameters am, / 3η, 7, 5, and σ from the waveform equations to obtain a third set of equations. Get these after steps Among crossing at least one of an absolute value equation. 36. The method of claim 35, further comprising the steps of: applying the system to the physiological medium, including cells of at least one of organs, tissues, and body fluids; and according to the values Imn, I0, m, and then measure the absolute value of at least one of the concentrations. 37. The method according to item 36 of the scope of patent application, wherein the measuring step includes: monitoring the concentration of oxyhemoglobin, the concentration of deoxyhemoglobin, and a ratio of -9- This paper applies the Chinese National Standard (CNS) A4 specification (210 X 297 mm) A8 B8 C8 D8 '1; .JtL Replacement 93.2.26? The scope of patent application is at least one of ^. 38. If the method of the scope of patent application is applied, it further advances the step of tumor cells appearing in a limited area of the media. 39. If the method of the scope of patent application is applied, it either advances or fails a The step of having a congestive condition on a limited area of the media. 40. The method of claim 35, which further includes at least 2 systems to be applied to the physiological media, including organs and tissues. Transplanted cells; and the absolute values and ratios of these concentrations to 丨, 根据, and 测量, measured according to Imn, 1. ^, and the heart. Soil / ~ 41. If the scope of patent application is No. 4 The method of item, which further, / g ° is used to determine whether a congestive condition has occurred in a limited area of the media. 夂 42. The method according to item 35 of the scope of patent application, wherein the removing step% queuing step : Make the unknown equation parameters approximate constants. I η under 43. The method of item 35 in the scope of patent application, wherein the obtaining step is a sequence of steps: irradiating with different wavelengths, phase angles, amplitudes, and inclusiveness. The first and second sets of electromagnetic radiation of one. Wave 44. The method according to item 43 of the scope of patent application, wherein this step: occupies the following steps to apply the first set of electromagnetic radiation having a first wavelength; And applying the second set of electromagnetic radiation having a second wavelength, ~ the wavelength is different from the first wavelength. Pain Di 45. Such as the method of applying for the scope of the patent lion, wherein the step of removing the column: the spider contains the next -10 -This paper size applies the Chinese National Standard (CNS) A4 specification (21 × 297 mm). 6. The scope of patent application uses the first ratio of one of the two wave equations, and the two wave equations are calculated from the first and The second set of waveform equations is selected. 46. For example, the method of claim 45, wherein the removing step includes the following steps: Solve the waveform equations of the same wave source with different waveform detectors, and from this, The ratios 7, and σ are removed by a ratio. 47. The method of claim 45 in the patent application range, wherein the removing step includes the following steps: solving at least two different wave sources and a waveform detector. Equal waveform equations, thereby removing the parameters, r, and 0 from the first ratio. 48. The method of claim 45, wherein the removing step includes the following steps: Use at least one of the two waveform equations The second ratio of the two, and the two waveform equations are selected from the other of the first and second sets of waveform equations. 49. For the method of claim 48, the removal step includes the following steps : Obtain one less than one of the total and the sound between the first and second ratios, so that at least one of ^ and 可 can be removed. 50. If the method of the 35th scope of the patent application, The removing step includes the following steps: θ represents a polynomial of at least one of the isoconcentrations with a formula of the relevant medium and the relevant geometric parameter. ~ 51. If the method of applying for the 50th item of the patent scope, where the multi-item includes a No. -11-This paper size applies the Chinese National Standard (CNS) A4 specification (210X297 mm) ~ ^ ------- — 52. Zero-order term. 2. The method of item 35 of the patent domain, wherein the providing step includes the following steps: approximating a constant of at least one related medium or related geometric parameter. 53. A method for determining a chromophore / degree in a physiological medium using an arithmetic formula through a system having at least a wave source and at least one waveform detector. The arithmetic formula has the following expression: Imn = am / 3nri〇m eXp {-Bmn LmndZ {(E {Q {) + σ} »where I〇, m is the intensity of the electromagnetic wave irradiated through an m-th wave source; it means that it is irradiated through the m-th wave source and through a first The intensity of the private magnetic wave detected by the n-wave detector; am is a parameter related to at least one of the m-th wave source and the medium; Shi n is at least one of the n-wave detector and the medium A related parameter; 7 is a proportionality constant, and any one of the parameters related to the m-th wave source, the n-th detector, and at least one of the media, Bmn is an explanation of the electromagnetic wave passing through the media Optical path length 'and a parameter related to at least one of the m-th wave source, the n-th waveform detector, and the medium; Lmn is a parameter describing the distance between the n-th source and the n-th waveform detector ; 5 is a proportionality constant, and the m-th wave source, the n-th waveform detector, and the medium Any one of the parameters related to at least one of them; q is a parameter describing an optical interaction between the electromagnetic wave and the i-th chromophore in the medium; q is the i-th chromophore concentration And σ is a proportionality constant, and any one of parameters related to the m-th wave source, the n-th waveform detector, and at least one of the media, the method includes the following steps:- 12- This paper size applies the Chinese National Standard (CNS) A4 specification (210X297). Irradiate the first and second sets of electromagnetic radiation with different waveform characteristics, and measure the signal received from the child media to obtain the waveform equation. At least two sets of equations about the measurement signals with unknown parameters; /. Remove at least one of Um, 0η, and 7 from the waveform equations obtained from these; Define the parameters of the arithmetic formula including Bmn and Lmn & A function of at least one of; and determining a chromophore concentration in a physiological medium. For example, the method of claim 53 in the scope of patent application, the further step includes the following steps: obtaining the value of the degree of the electromagnetic wave and the extinction coefficients of the material concentration. For example, if the method of claim 54 is applied, it further includes the following steps: obtaining an absolute value of at least one of the concentration and the ratio. A system for providing information on the distribution of red blood cells and their properties in a limited area of physiological media, which includes ... called an I moving component / which has at least one wave source ^ at least one waveform detector = to / A configuration of a wave source can irradiate near-infrared electromagnetic radiation to: the nuclear region i or more. At least one configuration of a waveform detector can detect near-infrared wire radiation from the target region and generate an output signal in response thereto; State 'its 疋 is coupled to at least one movable component so as to move it relative to the target area along at least -curve path, and processing state' it may follow the at least -curve path according to the at least -waveform The output signal generated by the detector determines the distribution of erythrocytes. 588158 The scope of the patent application & iL Hershey V. 2. "6 A8 B8 C8 D8 month & 1 or its properties. 57. The system according to item 56 of the patent application, wherein the distribution is at least one of the two-dimensional and three-dimensional distributions of the red blood cells. See, for example, the system of claim 56 in which the distribution is at least one of a spatial and temporal distribution of the red blood cells. 59. The system of claim 56 in which the properties include the absolute values of the erythropoietin concentrations. 60. If the system of claim 56 is applied for, the properties are the relative values of the red blood cells, and the values represent at least one of the spatial and temporary changes in the red blood cells. 61. The system of claim 56, wherein the properties include at least one of the erythropoietin concentrations, a total of at least two concentrations, and a ratio. 62. As claimed, the system of item 56 of the patent, wherein the properties include at least one of volume, mass, weight, volumetric flow rate, and mass flow rate. 63 ·, the system of claim 56 in the scope of patent application, wherein the properties include at least one of oxygen, '' X-hemoglobin; at least one of the degree of concentration, deoxyhemoglobin concentration, and lice saturation is defined as oxyhemoglobin This concentration is a ratio of the total of these concentrations of oxygen and deoxyhemoglobin. 64. The system according to the second item of the patent application, wherein the at least one wave source is configured to emit near-infrared electromagnetic light with different waveform characteristics. 65. The system of item% of the patent application, wherein the configuration of the at least one waveform detection unit can detect near-infrared electromagnetic waves having different waveform characteristics. -14- The paper is of the right size (CNS) A4 Secret (210X297 Public Love) View 158 66 .: The system of claim 56 in the scope of patent application, wherein one of the curvilinear paths includes conversion, conversion, rotation, rotation, and combinations thereof. • A system as claimed in item 56 of the patent, wherein the actuator is configured to produce the operation of the movable assembly at a fixed speed. 8. The system as claimed in item 56 of the patent, wherein the actuator is configured to produce the operation of the movable assembly at a variable speed. 69. If the system is claimed as the first in the scope of the patent, the movable component running through the actuator has a time characteristic, which can be one or more of a pulse, a step, a pulse pulse sequence, a sine curve, and a combination. Each. For example, if the system is called the patent No. 56 system, the movable component running through the actuator is one of periodic, aperiodic, and intermittent. 71. The system of item 56 in the scope of patent application No. 4, wherein the movable component has a vertical axis, and at least one wave source such as M and at least one detector are arranged along the axis of the axis, and the configuration can be formed along the axis. A scan extending along the vertical axis: Early: 'The configuration of the scanning unit can move with the movable component, and a scanning area near it, where the waveform detector can detect /, J from 4 mesh' Zone-transmitted near-infrared electromagnetic radiation. 72. The system according to item 71 of the Zhongli patent, wherein the scanning area is smaller than the target area. 73. The system of claim 71, wherein at least a part of the curve path is substantially orthogonal to the longitudinal axis of the movable component. 74. The system of claim 71, wherein at least 588158 Officials Α8 Β8 C8 D8 6. Scope of patent application The path of the curve is substantially parallel to the longitudinal axis of the movable component. 75. The system of claim 71, wherein the movable component includes at least two waveform detectors arranged substantially along the vertical axis. 76. The system of claim 75, wherein the movable assembly includes at least two wave sources arranged substantially along the longitudinal axis. 77. The system of claim 76, wherein the at least two waveform detection units are inserted between at least two wave sources. 78. The system according to item 77 of the patent application, wherein a first close distance between a first wave source and a first waveform detector is substantially similar to a second wave source and a second waveform detector A second close distance between them, and a first long distance between the first wave source and the second waveform detector is similar in quality between the second wave source and the first waveform detector A second long distance. 79. The system of claim 76, wherein the at least two wave sources are inserted between at least two waveform detectors. 80. The system of claim 75, wherein the movable component includes at least two wave sources, a first wave source arranged on one end of the vertical axis, and a second wave source arranged on the other end of the vertical axis. . 81. If the system is under the scope of patent application No. 80, the configuration of the first and second wave sources is substantially symmetrical to the longitudinal axis. 82. The system of claim 56 wherein the configuration of the exciter can produce at least two movements of the movable component along at least two curved paths. 83. The system of claim 82, wherein the configuration of the actuator can produce continuous movement continuously. This paper size applies to China National Standard (CNS) A4 specification (210 X 297 mm) 588158 A BCD, ¾I Co S2 Wherein the configuration of the exciter can generate at least a portion of the first movement and at least a portion of the second movement simultaneously. 85. The system of claim 82, wherein the first curved path of the at least part is substantially orthogonal to the second curved path of the at least part. 86. The system of claim 85, wherein the at least two curved paths are orthogonal axes of one of Cartesian, cylindrical, and spherical coordinate systems. 87. The system of claim 56, wherein the configuration of the actuator element can continuously generate at least two movements of the movable component, starting from a first part of the target area to a second part of the target area. Move 'and a second move from the second part to the first part of the target area. 88. The system of claim 56 in which the configuration of the actuator element can continuously generate at least three movements of the movable component, starting from a first end of the target area to a second end of the target area. A first movement 'starts from the second end to a second movement of a third end of the target area, and a third movement from the third end to a fourth end of the target area. 89. The system of claim 88, wherein the first and second movements are substantially linear transformations, and the second movement is substantially rotation. 90. The system according to item 88 of the patent application scope, wherein the target area has a rectangle, wherein the first and second ends are a first of the opposite ends of the rectangle -17- _____ This paper size applies to the Chinese National Standard (CNS ) A4 specification (210X 297 mm) 588158 Fanzheng replaced Zhen A8 B8 ______ Yi Nian 93. |. 26 C8 D8 6. Apply for patents, and the third and fourth ends are one of the opposite ends of the rectangle The second pair. 91. If the system of claim 82 is applied for, the configuration of the actuator can generate a first and a second movement of the movable component along a first and a second curved path, respectively, at least a part of the first curved path The configuration is substantially orthogonal to at least a portion of the second curved path. 92. If the system of claim 91 is applied, one of the first and second movements is a substantially linear transformation, and the other of the first and second movements is a substantially reciprocating movement. 93. The system according to claim 56 in which the at least one wave source and the at least one detector are non-invasively configured on the target area of the media. 94. The system according to item 56 of the patent application, wherein the configuration of the at least one wave source and at least one detector can be intrusively configured on the target area configured inside the medium. 95. A system for generating an image representing the distribution of red blood cells and their properties in a target area of a physiological medium, comprising: at least a sensor component having a wave source and a waveform detector, the wave source can be close to Infrared electromagnetic radiation irradiates the medium, and the configuration of the waveform detector can detect near-infrared electromagnetic radiation from a target area of the medium and generate an output signal in response thereto; a supporting portion whose configuration can support the sense Sensor assembly; and an exciter, the configuration of which is coupled to at least one of the sensor assembly and the supporting part, and is generated along a curvilinear path relative to the item -18-This paper size applies to Chinese national standards (CNS) A4 size (21 × 297 mm) 5881 ^ 8 Application for Patent Park At least-movement of at least one of the sensor components and the support portion of the target area; and the processor, which can be determined according to the output signal generated by the waveform detector along the at least-curve path Distribution and Properties of Hemoglobin. 96. As stated in the system and system of page 95J of the patent, wherein the movement includes at least curve transformation, reciprocating motion, rotation, rotation, and combinations thereof. 97. If the system and system of item 95 of the patent application IS S1 are applied, wherein the sensor component is fixedly coupled with the palatine branch and the tooth, the configuration of the actuator can move the sensors related to the target area. Device components and support parts. 98. The system of claim 95, wherein the sensor assembly can be movably coupled to the support portion, and the configuration of the exciter element can move the sensor component related to the support portion and the target area. 99. The system of item 95 in the scope of patent 4 of claim 4, wherein the sensor assembly can be mobilely coupled to the support part, and the configuration of the actuator element can generate the sensing related to the branch points and the target area. A second movement of the device assembly. 100. The system of claim 99, wherein the configuration of the actuator can simultaneously generate the at least a portion of the first movement of the sensor assembly and the at least a portion of the second movement of the support portion. 101. The system according to item 99 of the patent application, wherein the configuration of the actuator element can continuously generate the first and second movements. 102. If the system of item 95 of the scope of patent application, wherein the support part includes a mobile unit, the configuration can be configured from the sensor component and the support part from the item -19-This paper size applies Chinese National Standard (CNS ) A4 specification (210X297 male ~ --- 588158 A8 B8 C8 D8 patent application target area moved to another target area of the media. 103.-a kind of used to produce a distribution of red blood cells in a target area of physiological media Or its nature imaging system; the system has one or more wave sources' configured to irradiate near-infrared electromagnetic radiation on the medium; and one or more waveform detectors configured to detect near-infrared electromagnetic radiation, And generating an output signal in response to the system, the system includes: at least one portable probe having a movable component and an excitation component, the movable component including at least one of the wave sources, and the waveform detector At least one of them, and the configuration of the actuator element is coupled to the movable component and moved along at least one curved path; and a monitoring station including a processing unit The configuration of the processor can receive output signals from one or more detectors to determine the distribution or properties of erythroglobin, and generate an image of the distribution. 104. If the system of the scope of patent application No. 103, It further includes: a connector section configured to provide at least one of electrical communication, optical communication, power transmission, mechanical power transmission, and data transmission between the portable probe and the monitoring center. 105 · For example, the system for applying scope of patent 104, wherein the connector part includes at least one fiber optic object. 106. For the system for applying scope of patent 103, wherein the portable probe includes a rechargeable power source And form an object separated from the monitoring station. 107. For example, the system of the scope of patent application No. 106, wherein the configuration of the portable probe can communicate with the monitoring station. 108. For the scope of patent application The system of item 106, wherein the portable probe bag -20- This paper size applies Chinese national standard ⑴! ^^ A4 specification (21〇297mm) The device can store at least one of the S output signals, a signal 2 indicates the distribution, and a signal represents the images. A system for providing information about red blood cells' and distribution properties in a target area of physiological media, including a soil source, configured to irradiate near-infrared electromagnetic radiation to the media; detecting at least one waveform The detector is configured to generate an output signal in response to the near-infrared electromagnetic light emitted by the detection; and a soil optical probe, which includes a movable component and an exciter element. The movable component includes the wave source and detection At least one of the actuators; and an actuator element configured to be coupled to the movable component for operation and generating at least one movement of the movable component along at least one curved path. 110. The system according to item 109 of the patent application scope, further comprising: a monitoring station which can be coupled to operate with the optical probe, and includes a processor that can receive the output signal, and can be used from the wave source and the A set of waveform equations of the input and output parameters of the waveform detector are solved to determine these properties of red blood cells. 111 · An optical image system, a dwelling, etc. that can produce an image of a target area of a physiological media # The image represents the distribution of red blood cell properties in the target area. The optical image system includes: at least two wave sources configured to illuminate near infrared electromagnetic radiation To the medium; and at least two waveform detectors configured to generate an output signal in response to the near-infrared pen magnetic library detected by the detection; 21-588158 Ei A8 B8 C8 D8 At least two of them and at least two of the waveform detectors are substantially arranged along a line; and an exciter element configured to generate movement of at least one of the wave sources and the detectors. 112. The system of claim 111, wherein the configuration of the exciter element can move substantially all such wave sources and detectors arranged along the line. 113. The system of claim 1 丨 丨, wherein the movement includes at least one of curve conversion, reciprocating motion, rotation, rotation, and combinations thereof. 114. A method for providing second- or three-dimensional distribution information on the properties of red blood cells through a measurement system in a target area of physiological media, wherein the measurement system includes at least one wave source, at least one waveform detector, a movable component, And an exciter element, the configuration of the wave source can illuminate near-infrared electromagnetic light to the target area of the medium, and the configuration of the waveform detector can generate an output signal in response to the near-infrared electromagnetic radiation detected by The movable component has a vertical axis, and its configuration includes at least one of the wave source and the detector, and the exciter element coupled with the movable component, wherein the configuration of the wave source and the detector can be along the movable component. The longitudinal axis is extended to form a scanning unit, and a scanning area is defined in the vicinity thereof, wherein the exciter element is coupled with the movable component, and its configuration can generate at least one movement of the movable component along at least one curved path The method contains: -22- A8 B8 C8 D8 588158 VI. Patent application scope Place the movable component in a first area of the target area of the media, irradiate the near-infrared electromagnetic radiation through the wave source, and obtain an output signal violation through the waveform detector Scanning the first area; and processing the exciter element to generate the movement of the movable component from the first area of the target area to a second area along at least one curved path. 115. The method of claim 114, further comprising: continuously placing the movable component in a plurality of target areas of the media; and repeating the scanning and processing steps 116 in each of the target areas The method of claim 114, further comprising: determining the distribution of the properties of the erythropoietin in the target area of the child; and obtaining the images that represent the distribution in the target area. 117. The method of claim 114, wherein the positioning includes at least one of the following: forming an optical coupling between the medium and the wave source and between the medium and the waveform detector; and At least a portion of the optical coupling is maintained during the movement. 118. The method according to item 114 of the patent application scope, wherein the process includes one of the following: moving the movable component at a fixed speed; and this paper size applies the Chinese National Standard (CNS) A4 specification (210 X 297 mm) (Centi) 588158 repair. S 'is replacing Ziqq Π), year ^ ^ Η Α8 Β8 C8 D8 6. The scope of the patent application will move the mobile at a speed that changes with at least one of the time and position of the target area Component moves. 119. The method according to item 114 of the patent application scope, wherein the process includes only one of the following ... moving the movable component along a curved path that is at least substantially orthogonal to the longitudinal axis of the movable component; Moving the movable component along the curved path that is at least substantially parallel to the longitudinal axis; and moving the movable component along the curved path arranged at a preselected angle related to the longitudinal axis. 120. The method of claim 114, wherein the processing includes one of the following: linearly transforming the movable component along at least one linear path; transforming the movable component along at least one curved chain path; along At least one curved path rotates the movable component near the at least one rotation center by a predetermined angle; along the at least one curved path, rotates the movable component near the at least one rotation center by a predetermined rotation amount; and along the at least one curved path, The movable assembly reciprocates. 121 · If the scope of patent application is the first! The method of item 14, wherein the processing comprises: generating at least two movements of the movable component along at least two curved paths. 122. The method according to item 121 of the patent application scope, wherein the generation includes: along at least two of at least one of simultaneous, continuous, and intermittent • 24- This paper size applies the Chinese National Standard (CNS) a4 specification (2i0x297 mm) 123 to move the movable component. A method for extracting physiology through image J to generate a two-dimensional or three-dimensional distribution image in a target area of a physiological media. 4 The optical imaging system includes a sensor component, a main body, and ::: The detector assembly has at least a wave source, and its configuration can be light and magnetic! Irradiated to the medium; and at least-waveform detection ", a signal that can generate ΓΓ in response to near-infrared electromagnetic radiation detected thereby, the configuration of the main body can support at least-part of the sensor, and Moreover, the child exciter element is lightly coupled to the sensor component and the main body, and its configuration can generate at least one movement of the sensor component and at least one of the royal body. The method includes: The sensor component is placed in a first area of the target area of the media; 'using the sensor component through the near-infrared electromagnetic radiation to the first area of the media, and generating the output therefrom Signal to scan the first area; and cause the exciter element to generate at least one of the sensor component and the main body along at least one curved path from the first area of the target area of the media to A second area. 124. The method of claiming scope 123, further comprising: fixedly coupling the sensor assembly to the main body; and moving the main body during the moving. 125. The method of applying for item # 1 of the patent scope, further comprising: coupling and moving the sensor assembly with the main body; and -25- this paper size is applicable to China National Standard (CNS) A4 specification (210 X 297) (Centimeter) During the movement, the sensor may move with at least one of the subject and the target area <. 126. The method of claim 125, further comprising: generating another moving port of the subject through the exciter element; and the subject may move with the target area during the movement of the child. 7. The method of claim 126, wherein the generation includes one of: continuously moving the sensor components and the main body; and simultaneously moving the sensor components and the main body. . A method of generating an image of a target area of physiological media through a #image system, the image represents a two- or three-dimensional distribution of physiological properties in the target area. The method includes the following steps: Place at least two wave sources and at least two wave detectors substantially along a line in the area; sufficient for a scanning unit near the source and detector of the unequal wave, the unit having a scanning area smaller than the target area; and At least one of the wave source and the detector is generated to move one of the wave source and the detector to another area of the target area. 129. The method of claim 128, further comprising: scanning the target of the medium by irradiating the near-infrared electromagnetic radiation and generating an output signal in response to the near-infrared electromagnetic radiation detected by the waveform detector. Of these areas. 130 • The method of applying for item i29 of the patent scope, further comprising: repeating the scanning step in a plurality of these target areas, thereby establishing the -26- This paper size applies the Chinese National Standard (CNS) A4 specification (210 X 297 mm) The areas of the entire area are equal to the target area. … The scan area of Tian Zao 70, and it is true. 131. If the method of applying for the scope of the patent No. 130, it further advances the package. End the repeating step after repeating a predetermined amount. … 132. For the method of applying for the scope of patent No. 13, the further steps include: When the total area of the areas reaches a predetermined portion of the target area, the repeating step is ended. 133 · An optical probe capable of generating an optical imaging system representing a physiology or one of nature distribution images in a target area of a physiological medium, the optical probe having a plurality of wave sources and a waveform detector Near-infrared electromagnetic radiation can be irradiated to the media, and the configuration of the waveform detector is customized It can detect infrared electromagnetic radiation and generate an output signal in response to it. The optical probe includes: a plurality of symmetrically arranged scanning units, each of which has a first wave source, a first wave source, and a first waveform detection And a second waveform detector, the configuration of the first wave source is closer to the first waveform detector than the second waveform detector, and the configuration of the second wave source is The detector is closer to the second waveform detector, wherein a first close distance between the first wave source and the first waveform detector is substantially similar to that between the second wave source and the second waveform detector A second short distance between them, wherein a first long distance between the first wave source and the second waveform detector is substantially similar to that between the second wave source and the first waveform detector A second long distance, and among them the first and second waveform detection-27- This paper size is applicable to China National Standard (CNS) A4 specifications (210X 297 mm) C8 D8 The first and second wave sources detected by this The output signal produced by the near-infrared electromagnetic correction irradiated by at least one of the children is an optical interaction between the near-infrared electromagnetic radiation and erythropoietin in the target areas of the medium. 134. The optical probe of the scope of application for item 133, wherein the first and second close distances are substantially similar. Among them, the first and the second long distances of the optical probe such as item us in the scope of patent application are substantially similar. Among them, the symmetric sweep 136. If at least one of the optical probe tracing units of the scope of application for patent 133 includes a symmetry axis, the symmetry axis is related to the symmetrical configuration of the first and second wave sources, and It is related to the symmetrical configuration of the first and second waveform detectors. 137. For example, the optical probe according to item 36 of the application, wherein at least two of the symmetrical scanning units include at least one of a common wave source and a common waveform detector. 138. If the optical probe of the scope of patent application No. 136 is applied, the first and second wave sources and the first and second waveform detectors are substantially linearly configured. 139. The optical probe of claim 138, wherein the first and second wave sources are inserted between the first and second waveform detectors. 140. The optical probe of claim 138, wherein the first and second waveform detectors are inserted between the first and second wave sources. 141. The optical probe of item 138 in the scope of patent application, wherein the close distance is half of the long distance. -28- This paper size applies to China National Standard (CNS) A4 (210X297 mm) 588158 Positive replacement 6. Patent application Fanyuan U2. For example, the optical probe of item 138 of the patent application scope, wherein the optical probe includes at least a first symmetrical scanning unit and at least a second scanning plug The first and second scanning units share a symmetry axis, and the second and fourth scanning units have the first source f of the wave source and the waveform detector, wherein the second scanning unit has the wave source and the waveform detection unit. Time-saving-configuration, and is an optical probe arranged below the first scanning unit 143 · = the 142th application range, wherein the second scanning unit is directly arranged below the first scanning unit. Tian 144 · If the optical probe of the scope of application for the patent No. 138, it has at least ^ two symmetry, tracing unit and at least-second symmetric scanning unit, wherein the two scan units and the second scanning unit share a symmetry axis, where The first scan unit: there is a first configuration of the wave source and the waveform detector, and the second scan unit is directly below the first scan unit and has a wave source such as M and A second configuration of the waveform detector, the _ a_ setting is substantially opposite to the first configuration. 145. The optical probe according to item 144 of the patent application scope, wherein the second unit is directly disposed below the first scanning unit. 146. The optical probe according to item 138 of the patent application, wherein the light beam includes at least one first, second, third, and fourth symmetrical scans, each of which shares a symmetry axis with the other, wherein The first scanning unit has a first configuration of the wave source and the waveform detector, wherein the second scanning unit is directly disposed below the first scanning unit, and The second configuration, the second configuration is the opposite of the first configuration, where the third scanning unit is directly configured = -29 This paper size applies the Chinese National Standard (CNS) Α4 specification (210X297 mm) = the second scan Below the unit, and has a four-scan unit for the county ’s Gulanaisi configuration, and among which there is the first-configuration 4-connected configuration below the third scanning-insertion unit, and the optics with 147 · such as the scope of patent application No. 146 It is said that the scanning and inserting unit has the same shape and size of all such pairs of source-valence detector configurations in Feng 1, where the pairs are synonymous—the 4X4 wave detector is separated by a fixed distance. The wave source and detection of “Early”, the detection device configuration of the 47th patent scope of Rushen ’s patent has right-h rod, where the 4X4 wave source_ and detection • configuration has a quadrilateral, the quadrilateral can be, two the 4 ... Among the various shapes, -parallelograms, and-rhombuses: rectangle 49 · ^ optics of patent application No. 136 ^ a :: equal to the first and second waveform detectors 2 = detection; ^: polygonal Two upper vertices, and the first and second waveforms 1% are placed at the two lower vertices of the quadrangle. Yes .: The optical probe with the scope of patent application No. 149, where the quadrilateral is opposite to one of the rectangular, rectangular, and square, and the trapezoid has an equal length of 151. The optical probe with scope of patent application No. 149 , Where the optical probe. The first and second scanning units including at least one first symmetric scanning unit and at least one second symmetric scanning unit have different scanning axes, and the first t-scanning unit has a first of the wave source and the detector. Configuration, and the second scanning unit is laterally disposed on the first scanning unit and has the first configuration. Z -30- This paper size is applicable to China National Standard (CNS) A4 specifications (21G> < 297 public love) • The wind of item i49 of the patent scope includes at least one first symmetrical scanning unit rod, where the Optical probe unit, the first and second scanning and inserting unit = less-the second symmetrical scanning single scanning unit has the wave source and the detector = the same scanning axis, the first and second scanning units are configured sideways In the second, second, and first configuration, and the wave source and the detector are in a second configuration, the plug-in unit has the opposite configuration. The second side configuration is at least one first, second, second :, and 々 / rod 'of the first 153. If the light of the scope of patent application No. 149, the probe includes 哕 first connection and 罘 four symmetrical scanning Unit, of which ::, :: -th-configuration with the source and detector of the wave, 2right: early 70 is arranged on the side of the -scanning unit, and Second configuration, the second configuration is the opposite of the first configuration, where: r broadcast protection _ ^ /, T is a miscellaneous early configuration is directly below the first mobile element, and has the first And the fourth field is configured directly below the second scanning unit, and has the first configuration. 154. If the optical probe of the scope of patent application No. 136 is applied, wherein a first group of the wave source detectors is a substantially linear configuration, and wherein a configuration of the second wave and the second group of the detectors is feasible as a quadrangle : 4 points. 155. The optical probe of claim 154, wherein the first and second groups include at least one of a common wave source and a common waveform detector. 156 · If the optical probe of item 13 of the scope of the application for patent, among which the symmetrical scanning -31-This paper size applies the Chinese National Standard (CNS) A4 specification (210 X 297 mm) 588158 X. 4f · \ ir ' R] History 93.2 2 change. A8 B8 C8 D8 Patent application scope At least one of the trace elements includes a symmetry point, which is related to the symmetrical configuration of the first and second wave sources, and to the symmetrical configuration of the first and second wave detectors. / 157. If the optical probe with the scope of patent application No. 156 is applied, at least two of the symmetrical scanning units include at least one of a common wave source and a common waveform detector. 158. The optical probe of claim 156, wherein the first and second wave sources and the first and second waveform detectors are in a substantially linear configuration. 159. If the optical probe of the scope of application for patent No. 156, wherein the configuration of the first and second wave sources and the first and second waveform detectors can form four vertices of a quadrilateral, wherein The first and second wave sources and detectors are arranged on the top two vertices of the quadrangle, and the second wave detectors and the wave sources are arranged on the bottom two vertices of the quadrangle. 160. The optical probe of claim 59, wherein the quadrilateral is one of a rectangle and a parallelogram, and the parallelogram has two sides of different lengths. 161. For example, the optical probe of the scope of application 133, wherein at least one of the symmetrical scanning units includes at least one of a third wave source and a third waveform detector. 162. For example, the optical probe with the scope of patent application No. 61, wherein at least one of the third wave source and the detector is disposed in a substantially middle portion of the symmetrical scanning unit. 163. If you apply for an optical probe of item 13 in the scope of patent application, the symmetrical scanning -32- This paper size is applicable to China National Standard (CNS) A4 (210X 297 mm) 588158 The symmetrical configuration of at least two of the tracing units of the symmetry axis of the Wang domain is related to the Φ s, 丨, soil 3 Y, and temple pairs of the optical probe to the tracing unit of the optical probe of item 163 of the patent application. % # The other one is directly below the symmetric scanning unit. Please refer to the optical probe of range 163, where at least two of the symmetric scanning early 7C < are substantially side configuration. 166. ^ Please refer to the optical probe of item 133, in which the symmetrical configuration of at least two of the symmetrical sweeps is related to the global symmetry 0 167. If = please request the optical probe of item 166 of the patent scope, where At least two of the symmetrical scan sheets 7L are substantially arranged in a chess shape near the symmetrical point. 168. For example, please apply the optical probe of item 166 of the patent, in which at least two of the symmetrical scanning units are arranged substantially concentrically near the point of symmetry. 169. The optical probe of the scope of application for item 133, in which at least one of the wave sources is configured to irradiate multiple recombined electromagnetic radiation with different waveform characteristics. 170. The optical probe of item in the scope of application for patent, wherein the configuration of at least one of the waveform detectors may have a plurality of groups of electromagnetic waves with different waveform characteristics. 171. In the case of an optical probe according to item in the scope of patent application, the configuration of one of the wave sources can radiate electromagnetic waves, and at least one of the wave sources does not radiate electromagnetic waves. -33- This paper size applies to China National Standard (CNS) Α4 size (210 X 297 mm) '" 一一 " 58815 ° 6. Scope of patent application ′ Among which, the electromagnetic radiation is ultraviolet, laser, and sound wave, 172. The optical probe of item 133 of the scope of patent application is at least one of sound wave, near infrared, infrared, visible light, and photon. 173. If the optical probe of the scope of application for item 133 is applied, the images are expressed in at least one of the erythroglobin and the properties: dimension = at least one of the three-dimensional distribution. 174. If the optical probe of the scope of patent application No. 133 is applied, the properties are at least one of a spatial distribution and a time distribution of at least one of the red blood cells and the properties. 175. The optical probe of claim 133, wherein the properties are at least one of an absolute value and a relative value of at least one of the erythrocytes and the properties. 176. The optical probe of claim 133, wherein the properties include at least one of deoxyhemoglobin concentration, oxygen hemoglobin concentration, and monooxygen saturation, which is the concentration of the oxygen hemoglobin and A ratio of the concentration of the oxyhemoglobin to the concentration of the oxyhemoglobin. 177. The optical probe of item i 33 in the scope of patent application, wherein the properties include extended properties including at least one of volume, mass, weight, volume flow rate, and mass flow rate of the erythropoietin. 178_ —An optical probe for an optical imaging system capable of producing an image of red blood cells or a property distribution in a target area of a physiological medium, the optical probe includes a plurality of wave sources and a plurality of waveform detectors, and the configuration of the wave sources The medium can be irradiated with near-infrared electromagnetic radiation, and the configuration of the waveform detector can detect the near-infrared electromagnetic radiation and generate an output signal in response thereto. ~ 'The optical probe contains: tracing: element, where: the first scanning unit is associated with a fourth ^ 〇 β " and one of the second scanning unit is associated with a third scanning c, each scanning unit has a first A wave source, a second wave 1—a first wave detector, and a second wave detector, wherein the configuration of the wave source is closer to the first wave detector than the second wave detector. And the configuration of the second wave source is closer to the second waveform detector than the first waveform ij 詻, and a first close-range configuration between the first wave source and the waveform detector is substantially similar 4 A second short-distance soil between the first wave source and the second waveform detector, wherein a first, = distance configuration between the first wave source and the second waveform detector is substantially similar to the first A second close distance between the two wave source and the first waveform detector, and the configuration of the first and second wave sources is synchronized with the first and second waveform detectors of the child to generate an absent The near-infrared radiation interacts with the erythropoietin electromagnetically in the target areas of the child media The output signals. Π9. Please refer to the optical probe of range 178, in which all the wave sources and all the wave detectors of the scan sheet 7C and the mother are in a substantially linear configuration.胤 If the optical probe of the scope of patent application No. 179 is applied, wherein the first and second wave sources are inserted between the first and second waveform detectors in the first and fourth scanning units, Moreover, the first and second waveform detectors are inserted between the first and second wave sources in the second and third scanning units. -35- This paper size is in accordance with Chinese National Standard (CNS) A4 (210 X 297 mm) 588158 f is replacing IVaf2% A8 B8 C8 D8 Patent application scope 181 · —An optical probe for generating an optical imaging system representing erythroglobin or its properties in a target area of a physiological medium, the optical probe includes: a plurality of wave sources and a plurality of waveform detectors, the The configuration of the iso-wave source can irradiate the near-infrared electromagnetic radiation to the media, and the configuration of the waveform detector can detect the near-infrared electromagnetic radiation and generate an output signal in response to the at least one first wave source and at least one first waveform. The detector is defined as a first scanning element, wherein the first wave source can illuminate the near-infrared electromagnetic wheel, and the waveform detector can detect the waveforms irradiated by the first waveform detector. And generating a first output signal, wherein at least one second wave source and at least one second waveform detector are defined as a second scanning element, wherein the first wave source can illuminate the near-infrared electromagnetic light emission, and the second The waveform detector can detect the waveforms irradiated by the second waveform detector and generate a second output signal, wherein the first and second scans A component is a scanning unit, in which # 等 一一 and 一一 波源 疋 are symmetrically arranged with a symmetrical line and a symmetrical point, and in each of them, the first and second waveform detectors are also It is a symmetrical arrangement related to the symmetry line and the symmetry point. 182. The optical probe of item 1 § 1 in the scope of patent application, wherein the configurations of the first and second scanning units are intersected with each other. 183. The optical probe of item 81 of the patent application scope, further comprising: a processor configured to receive the first and second output signals generated by the first and second waveform detectors, In order to obtain the input used in the first and second wave sources and the first and second waveform detectors -36- 588158 f Positive replacement page A8 1 year 93.1 26 E] B8 C8 D8, patent application scope and output A set of waveform equations for the parameters is solved to determine the distribution of at least one of the heme and its properties, and the images that produce the distribution. 184. If the optical probe of the scope of patent application No. 183 is applied, the images are corresponding to a plurality of voxels, and each of the first and second scanning units can respectively generate a plurality of first voxels and a plurality of voxels. A second voxel, and wherein the configuration of the processor may calculate at least a first voxel value for each of the first voxels from the solutions of the group, and from the At least one second voxel value for each of the second voxels calculated and solved. 185. For example, the optical probe of the scope of application for patent 184, wherein the configuration of the processor is to define a plurality of intersected voxels, and each of the intersected voxels is defined as one of the first and second voxels crossing each other. Overlapping parts. 186. If the optical probe of the scope of claim 185 is applied, the configuration of the processor may directly calculate the intersections from the first and second voxel values of the intersecting first and second voxels, respectively. At least one intersected voxel value for each of the voxels. 187. If the optical probe of the scope of patent application 186 is applied, wherein each of the intersected voxel values is the first and second voxel values of the first and second voxels crossing each other At least one of an arithmetic sum and an arithmetic average. 188. If the optical probe of the scope of patent application 186 is applied, wherein each of the intersecting voxel values is the first and second voxel values of the first and second voxels crossing each other At least one of a weighted sum and a weighted average 0 -37- This paper size applies to the Chinese National Standard (CNS) A4 specification (210 X 297 mm) D8 VI. Patent application Fan Yuan Generated by the optical imaging system of the probe — a method of studying two-dimensional or three-dimensional images of the domain, these images express the > image of the spatial or temporal distribution of hematoglobin or its properties, in which the optical probe includes a plurality of wave sources And multiple detectors' the configuration of these wave sources can project near-infrared electromagnetic light to the media, and the configuration of the waveform detector can generate output signals in response to the near-infrared and electromagnetic light emitted by the detection, the method The method includes the following steps: ^ $ for a plurality of scanning elements, each of which includes at least one of the waveform detectors and at least one of the waveform detectors; Scanning unit At least two of the components < The field uses one or more scanning units to scan the target area; The output signals generated by each of the scanning units are grouped; and the input and shape equations obtained by these scanning units are used to solve ; Let ㈣ ,, ′, and WDM be resolved to determine at least one of erythropoietin and properties that provide one or more images of the distribution. 190. If the method of the scope of application for patent No. 189, the method further includes scanning the target area over the entire time; determining at least one of the red blood cells and properties in the target area of the media over the entire time Providing the distribution; providing the images of the distribution over time; and providing the images of changes in the distribution over time. -38- This paper size is suitable for Towels® National Scales (CNs) M Specifications (Sin> < Norwegian Public Manager) 588158 191. The method according to claim 189, further comprising: a plurality of first voxels in at least one of the scanning units;-determining at least one of each of the first voxels of the child; A first voxel value, each of the first voxel values representing an average of at least one of the red blood cells and the properties; and directly generating the Distribution of these images. 192. The method according to item 191 of the patent application range, wherein the definition includes: ... controlling the resolution of the images by adjusting at least one characteristic range of each of the first voxel values. 193 · The method of item 92 in the scope of patent application No.4, wherein the control includes at least one of the following: · Trimming at least one of the wave sources in at least one of the same scanning element and the same scanning unit And the geometric configuration between at least one of the waveform detectors; trimming the geometric configuration between at least two scanning elements of the same scanning unit; adjusting the geometric configuration between at least two scanning orders; adjusting the Data sampling rate of the output signal. 194. The method of claiming scope 191, further comprising: a plurality of second voxels defined in at least one of the scanning units; determining at least one of each of the second voxels The second voxel value, the parental unity value indicates that at least -39 of these red blood cells and these properties. This paper size applies Chinese National Standard (CNS) A4 specifications (210X297 public love) 588158 Α8 Β8 C8 D8 f The positive replacement page is 009 years ο 6 years, an average of one of the scope of patent application; and the images of the distribution are directly generated from the first and second voxel values. 195. The method of claiming scope 194, further comprising: defining a plurality of intersecting voxels in at least one of the scanning units, each of the intersecting voxels being defined as two intersecting firsts And an overlapping portion of the second voxel; determining at least one intersected voxel value of each of the intersected voxels, each interstitial voxel value representing the value of the red blood cells and at least one of the properties An average value; and the images of the distribution are generated directly from one of the intersected voxel values and the first and second voxel values. 196. If the method of applying for item 195 of the patent scope, wherein the intersected voxel value is determined by at least one of the following: plus the first and second voxels that intersect the first and second voxel values Prime values; arithmetically average the first and second voxel values of the intersecting first and second voxel values; add the weighted first and second of the intersecting first and second voxel values Voxel values; and a weighted average of the first and second voxel values that intersect the first and second voxel values. 197. If the method of applying for the item 194 of the patent scope, further includes: a plurality of third bodies defined in at least one of the scanning units -40-This paper size applies the Chinese National Standard (CNS) Α4 specification (210X 297 mm) 588158 A8 B8 C8 D8 f is replacing page 2, 26, dated 26, patent application range; determining at least one third voxel value for each of these third voxels, each third The voxel value represents an average of the red blood cells and at least one of the properties; and the images of the distribution are directly generated from the first, second, and third voxel values. 198. If the method of claiming scope 197 of the patent application, further comprising: a plurality of intersecting voxels defined in at least one of the scanning units, each of the second intersecting voxels being defined as two Intersect an overlapping portion of the first and third voxels; determine at least one second intersected voxel value of each of the second intersected voxels, and each second intersected voxel value indicates that the red blood cells and An average of at least one of the properties; and based on at least one of the intersected voxel values, the second intersected voxel value, the first voxel value, the second voxel value, and the third voxel value One produces the images of the distribution. 199. A system for generating an image representing one or more chromophore properties in a target area of a physiological medium, comprising: at least one movable support; an exciter coupled to the at least one movable support, and The configuration can move the support with the target area along at least one curved path; one or more wave sources and one or more waveform detectors installed on the support ix to form a vertical axis, a scanning area, and Scanning of one scan volume-41-This paper size is applicable to China National Standard (CNS) A4 specifications (210X 297 mm) The configuration of the wave source such as Unit 4 can irradiate the near-infrared electromagnetic radiation to the target area of the medium, and the configuration of the waveform detectors can detect the near-infrared electromagnetic light from the target area and generate an output in response to it. A signal; and a processor that can receive the output signal and a plurality of voxels defined in the target area, wherein each of the plurality of voxels has a characteristic range and a -voxel axis', and the processor can The output signal in the voxels determines the nature of the chromophore and produces these images. 200. The system of claim 199, in which the characteristic range of a plurality of individual voxels is one of height, length, and width, and the formation of a pre-footing angle is related to the movement of the movable support. At least one curved path is related. 201. The system of claim 199, wherein the voxel axis of each of the plurality of voxels is substantially parallel to the longitudinal axis of the scanning unit. 202. The system of claim 199, wherein the plurality of voxels have a degree characteristic, which is substantially similar to a high characteristic of the scanning unit. 203. The system of claim 199, wherein the characteristic range of the plurality of voxels is substantially parallel to the path of the at least one curve moved by the movable support. 204. The system according to item 199 of the patent application, wherein the processor is configured to sample the output signal at a preselected time interval. 205. The system of claim 204, wherein the characteristic range of the plurality of individual voxels is proportional to the moving speed of the movable support. 206. If the system of the scope of patent application is No. 204, the characteristics of plural individual voxels are -42- This paper size is applicable to China National Standard (CNS) A4 specification (210 X 297 mm) 588158 ^, page 9a 2.26 The range of patent application for the EJf year is proportional to the time interval between successive samples. 4Declares the system of item i99 of the patent scope, wherein the configuration of the processor: determines the voxel value of each of the plurality of voxels, and generates a -sequential sequence of the determined voxel values, each voxel value representing the body The properties of erythropoietin are average. 208. The system of claim 207 of the patent scope, wherein the voxel values represent the properties of erythrocytes averaged over at least one of the scanning area and the scanning volume. 209. For a system with the scope of patent application No. 207, wherein the configuration of the actuator can move the support along at least two curved paths, and wherein the configuration of the processor defines a Individual groups of voxels' and determine a series of voxel values corresponding to individual groups of voxels. 210. The system of claim 209, wherein the processor is further configured to define a plurality of intersecting voxels to define intersecting voxels belonging to individual groups of voxels. 211. If the system of the scope of patent application No. 21 is applied, the configuration of the processor may determine the intersected voxel value of each of the intersected voxels, and generate a continuous_intersect from the voxel values of the intersected voxels Voxel value. 212. If the system of the scope of patent application No. 211, wherein each of the intersected voxel values is an arithmetic sum, arithmetic mean, geometric sum, geometric mean, weighted sum of voxels of intersected voxels At least one of the total and weighted averages. 213. If the system of the scope of application for patent No. 211 is applied, wherein each of the intersected voxel values is the entire sum of the intersected voxel voxel values and the entire flat -43- This paper size applies Chinese national standards (CNS) A4 size (210X297 mm) 588158 At least one of them. 214 · ^ The system for applying scope of patent No. 199, wherein the generated images 疋 correspond to one of a two-dimensional distribution and a three-dimensional distribution of the properties of the chromophores. 215 · ^ The system for applying scope of patent No. 199, wherein the generated images are at least one of a spatial distribution and a temporal distribution representing the properties of the chromophores. 216. The system according to item 199 of the patent application scope, wherein these properties are at least one of the spatial and temporal distribution of chromophores in the target area. 217. If the system of item I of the scope of patent application, the properties include at least one of the chromophore concentration properties, the concentration sum, the concentration difference, the concentration ratio, and combinations thereof 218. If the system of the scope of application for patent No. 199, wherein one or more chromophores contain erythropoietin, and these properties include at least one of the erythropoietin expansion values, including volume, mass, volume flow 219. The system according to item 21 of the patent application scope, wherein the one or more chromophores contain erythropoietin, and these properties include the concentration of oxyhemoglobin and the concentration of deoxyhemoglobin At least one of them, and the oxygen saturation is a ratio of these concentrations of oxyhemoglobin and the concentrations of deoxyhemoglobin and oxyhemoglobin combined. 220. A system such as the 199th in the scope of patent application , Where the electromagnetic radiation is at least one of sound waves, near-infrared rays, infrared rays, visible light, external lines, lasers, and photons. -44- ^ The paper size applies the Chinese National Standard (CNS) A4 specification (210 X 297 mm) 588158 φ is positively replaced ^ 丨 AS __ Lannian 9afj26uii Patent scope ^ & 221. If the system of the patent application scope item 199, wherein the vertical axis of the scanning unit is passed through one or more of the scanning unit Wave sources, and one or more waveform detectors. 222. The system of item “I” of the patent application scope, wherein the one or more chromophores include at least one solvent of the medium, one of the solvents dissolved in the medium, The solute, and an object included in the medium, each of which is configured to interact with an electromagnetic wave irradiated through the wave source and transmitted through the medium. 223. The system of claim 199, wherein the chromophore or chromophores include a cytochrome, cytosome, Cytosol, enzyme, hormone, neurotransmitter, chemical or chemotransmitter, protein, cholesterol, at least one of apoprotein, fat, sugar, blood cells, water, and oxyhemoglobin including oxyhemoglobin and deoxyhemoglobin. 224 · A system for generating an image representing the distribution of at least one erythropoietin property in a target area of a physiological medium, comprising: a sensor component including at least one wave source and at least one waveform detector 'the at least one The configuration of the wave source can irradiate near-infrared electromagnetic radiation to the medium, and the configuration of the at least one waveform detector can detect the near-infrared electromagnetic radiation in the target area and generate an output signal in response thereto; The sensor component is lightly closed, and its configuration can move the sensor component with the target area of the media along at least one curved path; and a processor for receiving the sensor component from the sensor component. The output signal is in violation of the configuration of the processor. It is defined as a plurality of individual voxels in the target area, in order to determine the properties of the red blood cell by solving a plurality of waveform equations. -45- — This paper size applies the Chinese National Standard (CNS) A4 specification 210 X 297 mm) A8 B8 C8 D8 588158 VI. Patent application and these waveform equations are applied to the input radiation from the at least one wave source and the radiation detected through the at least one detector; and generating the target area in the target area An image of the distribution of red blood cells. 225. According to the system of claim 224 in the scope of patent application, in which one of the plurality of individual voxels has a characteristic range and an integral prime axis, and wherein the plurality of months of soya glutamate are along at least one of the corresponding sensor components The curved movement path is continuously arranged in one or more directions. 226. If the system of the scope of application for patent No. 224, the configuration of the processor can determine the voxel value of a plurality of voxels, and generate a series of voxel values, each voxel value is the At least one hemoglobin has an average property. 227. The system according to item 224 of the patent application, wherein the configuration of the processor can be at least one of the parent voxels, and an intersecting voxel is defined as belonging to a voxel arranged in two or more directions. At least the voxels in the group are crossed. 228. A system for generating at least a property distribution image representing at least one erythroglobin in a target area of physiological media, the system includes: to = a wave source, which can be configured for near-infrared electrophysiology media; at least one The waveform detector is configured to detect the private magnetic field in the target area and generate an output signal in response thereto; a portable probe having at least _ ^ & waibei ,, ,, and movable components And at least one excitation port, in which at least one movable component of A f ^ is provided, the women's clothing has at least one wave source and the first waveform detector, and the configuration of the at least one / inspirant is the same as the to -46- 588158, D8 VI. Patent application: One movable component is coupled and coupled to move it along one or more curved paths; and a processing state for receiving an output signal from the at least one detector, And providing a plurality of individual voxels in the target area, the processor can determine the at least one property of the at least one chromophore by solving a plurality of wave equations, and the wave equations are applied to radiation from the at least one wave source, And radiation detected by the at least one detector; and the distribution image in the nature of the chromophore. 229 · A system for generating at least one property distribution information about at least one chromophore in a target area of a physiological medium, comprising: at least one wave source 'configured to irradiate near-infrared electromagnetic radiation to the physiological medium; At least one wave on > Detector's configuration can detect electromagnetic in the target area and generate an output signal in response to it; an optical probe, which includes at least one movable component, in which the wave source and detection are configured At least one of the sensors; a monitoring station 'which is coupled to the optical probe, and includes a processor configured to receive the output signal, the processor may provide a plurality of voxels in a portion of these target areas, And determining the chromophore properties by solving a plurality of waveform equations that are applied to radiation from the at least one wave source and radiation detected through the at least one detector; and related to the target region Information about the nature distribution of the chromophore, an exciter whose configuration can be coupled to the at least one movable component, so that Chinese National Standard (CNS) A4 specification (210X297 mm) 588158 2 〇ΗΓ4 Α8 Β8 C8 D8 Patent application scope _____ Move it along at least one curved path; and a connector for providing electrical communication, optical communication, At least one of electric power transmission and mechanical force transmission, and data transmission between at least two of the optical probe, the monitoring station, and the exciter element. 230. A system for generating at least one property distribution information about at least one chromophore in a target area of a physiological media, comprising: at least two wave sources configured to irradiate near-infrared electromagnetic radiation to the media Target area; at least two waveform detectors configured to generate output signals in response to electromagnetic radiation detected from the target areas; wherein at least two of the wave sources and at least two of the waveform detectors Is essentially configured along a line; and the processor's configuration can receive and output signals to provide a plurality of individual voxels in a portion of these target regions in order to determine the properties of the at least one chromophore by solving a set of waveform equations, The waveform equations are applied to radiation from the at least two wave sources and radiation detected through the at least two detectors; and generating a distribution of properties of the at least one chromophore in the target area of the physiological media. The information. 231. A method for generating an image representing the distribution of red blood cells in a target area of a physiological medium through a portable measurement system, the system has a movable component, and at least one wave source and at least one waveform detector are installed to define a device having a The scanning unit of the vertical axis has a scanning area smaller than the target area and a nearby scanning volume. The at least one wave source can irradiate near-infrared electromagnetic radiation to the target area. The configuration of the at least one waveform detector can detect -48- 588158 The scope of the patent application is: gVa 126¾ A8 B8 C8 D8 f, infrared electromagnetic radiation in the target area, and the output generated in response to it. The system further includes an exciter element, which is related to the movable, a in order to scan the target area by moving it along at least one curved path, the method includes the following steps: placing the movable component on the target area for the media; and placing the first element in a first area of the target area. Area · Scanning the first area of the target area by radiating near-infrared electromagnetic radiation, and obtaining the output signal from the waveform detector;-inverting the exciter element in order to connect the movable component and the scanning unit Move from the first region to the other two regions of the target region along a first curved path; define at least one of the regions of the target region a first set of voxels from the output k number; decide Corresponding to the voxel value of the first group of voxels, each voxel value is an average of the properties on the one-one voxel; and generating a value representing the voxel value from the first group The erythropoietin distribution shadow 232 · As in the method of patent application No. 231, it further includes the following steps: ° Forming an optical coupling between the medium and the wave source and detector; and the movable component and scanning The optical coupling is maintained during the movement & of at least one of the A's. 233. If the method for applying for item 231 of the patent scope, further comprising the following steps: ’# 588158 f is replacing 9a | 2 (A8 B8 C8 D8 in the year of application. 6. The scope of patent application is substantially along the line to configure the at least -wave source and at least -waveform detector. 234 · If the method of applying for the scope of patent No. 231, The generating step includes the following steps: Controlling the resolution of the images by changing the first group of voxels. 235. For example, the method of patent item IS 234 is used, wherein the changing step includes at least one of the following steps. By: " adjusting a distance between the wave source and the detector; adjusting the geometric configuration between the wave source and the detector; adjusting the movement of at least one of the movable component and the scanning unit; Adjust at least one of the contour, length, and distortion of the curved path; adjust many such movements of at least one of the movable component and the scanning unit on the target area; and adjust a sample of the output signal 236. The method of claim 231, further comprising the following steps: a second set of voxel values in at least one different region of the target region; 'Decide on the one-valued voxels related to the second set of voxel values; define a plurality of intersecting voxels, which are defined as the intersection of at least two voxels each belonging to a different set of voxels; from these intersections The voxel values of the voxels are obtained from the intersected voxels of the intersected voxels; and & The red blood cell distribution shadows are generated based on the obtained intersected voxels. -50- This paper applies the Chinese National Standard (CNS) A4 Specifications (210X297 public love) 588158 奂 2 Replaced al for 9 years | 8 A BCD VI. Apply for a patent fan garden image. 237. For the method of applying for the scope of patent No. 236, in which the first sequence of the first This step of intersecting voxel values includes at least one of the following steps: arithmetically averaging the voxel values of the intersecting voxel values; making the geometry of the voxels of the intersecting voxel values geometric Average; the weighted average of the voxel values of the intersecting voxel values; and the total average of the voxel values of the intersecting voxel values. The following steps are further included: A third group of voxels is defined in another region of the domain; a voxel value of the third group of voxels is determined; a second plurality of intersected voxels are defined, and the intersected voxels are defined as belonging to different groups of voxels At least two voxels intersect; obtain the interdigitated voxel values of the second group of intersecting voxels from the voxel values of the intersecting voxels; and generate the distribution image of red blood cells according to the second intersecting voxel values. 239. If the method according to item 238 of the patent application scope, it further comprises the following steps: by disposing the intersecting voxel values of a plurality of the sequences, generating the images of the distribution of the red blood cells, thereby improving the And other image resolutions. 240. A method for generating at least one property distribution image representing at least one chromophore in a target area of physiological media through a portable system, wherein the -51-this paper size is applicable to China National Standard (CNS) A4 specifications (210X297 mm) Α8 Β8 C8 D8 Patent scope system includes at least one wave source 'configured to irradiate near-infrared electromagnetic radiation to the medium; and at least one waveform detector configured to detect infrared electromagnetic radiation and generate an output signal in response thereto, The method includes the following steps: placing the wave source and detector in the target area; defining a first set of voxels from the output signals; determining a series of voxel values for the first set of voxels, and the integral voxel value is The property average on the one-body voxel is defined; a second group of voxels from the output signals are defined; a series of voxel values of the second voxels are determined; a first group of intersected voxels is allocated, the group of intersected bodies A voxel is defined as the intersection of at least two intersecting voxels belonging to one of the first and second groups of voxels, respectively; the intersect of the first group of intersecting voxels is calculated from the voxel values of the intersecting voxels. Voxel values; and generating the images of the distribution of the chromophore properties from the first intersected voxels of the first sequence. 241. The method of claiming scope of claim 24, wherein at least one of the defining steps includes the step of defining the voxels of the group in at least one of the following: each along the target area Pre-selected distance; each pre-selected sampling interval of the output signal; one of the source and one of the waveform detectors of each pair; and -52- this paper size applies to Chinese national standards (CNS) Α4 specification (210X297 mm) 588158 f Positive replacement page more 9a 2 ^ 26 years patent application scope Each scan unit contains at least two of the iso-sources and at least two of the waveform detectors. 242. If the method for applying scope 240 of the patent is applied, at least one of the defining steps includes at least one of the following steps: By changing at least one range of at least one of the voxels and the intersecting voxels And the image resolution of the distribution of this property is adjusted. 243. If the method of applying for the scope of patent application No. 240, wherein at least one of the predetermined steps includes at least one of the following steps ... average the property over a region of the voxel; and This property is averaged over the volume of the voxel. 244. For the method of applying for the scope of patent application No. 240, wherein the calculating step includes at least one of the following steps: arithmetically averaging the voxel values of the cross voxels; The voxel values are geometrically averaged; the voxel values of the intersected voxels are weighted average; and the voxel values of the intersected voxels are total averaged. 245 · —A method for generating a distribution image representing at least one property of at least one chromophore in a physiological media target region through a measurement system: wherein the system includes at least one wave source, at least one waveform detector, and a movable Component, and an exciter element, the configuration of the wave source can irradiate near-infrared electromagnetic radiation to the medium, the configuration of the waveform detector can generate an output signal in response to the near-infrared electromagnetic radiation detected thereby, the configuration of the movable component Including at least one of the wave source and the detector, and the exciter element is coupled with the movable component for operation, wherein the wave source -53- 588158 A8 B8 C8 D8 专利, patent application scope and detector configuration A movable scanning unit may be formed, which includes a vertical axis connecting the wave source and the detector, and defines at least one of a scanning area and a scanning volume in the vicinity thereof, and the configuration of the exciter element may be along at least A curved path causes at least one movement of at least one of the movable component and the scanning unit. The method includes the following steps: Placing the movable component on the target area of the media; placing the scanning unit on a first area of the target area; manipulating the exciter element so as to follow a first curved path from the first area of the target area A region to a second region generates a first movement of at least one of the movable component and the scanning unit; a first group defining a first voxel from the output signals in at least a portion of the target region ; Determining a first voxel value of a first sequence of the first voxels, each first voxel value representing a first average value of the average property on the first voxel; in at least a part of A second group of second voxels from the output signals is defined in the target region; a second voxel value of a second sequence of the second voxels is determined, and each second voxel is represented in the first voxel. A second average of this average property on two voxels; a set of intersecting voxels, each of which is a cross section defined as at least two intersecting voxels, each of which belongs to the first And the second voxel Wait one of the first and second groups; directly calculate a continuous_intersecting voxel value of the intersecting voxels from the voxel values of the intersecting voxels; and from the intersecting voxels of the sequence The value directly produces the images of the distribution of that property. -54- This paper size applies to China National Standard (CNS) A4 (210X297 mm) 24 \ systems for in-physical media object and property distribution information system, including: M for an optical probe of hemoglobin, and one: the configuration of the wave source can be close to ΓΪ— / waveform detector, Wherein, the W — m — e ¥,, and Gong line electromagnetic radiation is irradiated to the self-contained area of the physiological media, and the configuration of the waveform detector can detect the near-infrared electromagnetic radiation from the media group, and respond to it. A first output signal is generated. A 7-blade analyzer can receive and sample the first output signal to obtain a plurality of amplitude values. These amplitude values can be analyzed to determine and have substantially similar amplitudes. At least one set of samples of the first output signal; and, two signal processors configured to calculate: a: baseline from the first output signal, where the first baseline represents a child determined by the analyzer; It is substantially similar in amplitude and provides a self-calibrating first output signal by processing the first output signal and its first baseline. 247. The system according to item 2 (1) of the patent application scope, wherein the optical probe has a scanning unit including two or more waveforms and two or more waveform detectors, and the scanning unit is defined near it A scanning area, which is a substantial part of the first target area. 248. If the system of the scope of application for patent No. 246, wherein the optical probe has a scanning unit 'which contains two or more waveforms, and two or more waveform detectors, the scanning unit is defined in the vicinity of a A scanning area, which is a part of the first target area. 249. If the system of the scope of application for patent No. 248, wherein the optical probe has an exciter and a package, the configuration of the exciter can move the scanning unit on a plurality of areas of the first target area, and the optical The package of the probe is placed in the first target area. -55- This paper size applies to China National Standard (CNS) A4 (210X297mm) 250. As claimed, the system and system of item 249 of the patent norm, wherein the configuration of at least one of the waveform detectors < can generate a plurality of the first in the areas of the first target area. output signal. 251. The system of claim 246, wherein the signal processor is configured to provide the self-calibrating first output signal on a substantially instant basis. 252. If the system of the scope of application for patent No. 246, further includes: An image processor configured to configure the first output signal from the self-calibration first output signal to form the distribution image of erythropoietin in the first target area. 253. If the system of claim 252 is declared, the configuration of the image processor can constitute the images on a substantially real-time basis. 254. The system of claim 252, wherein the erythropoietin in the first target area is at least one of oxyhemoglobin and deoxyhemoglobin. 255. The system of item 252 in the scope of the patent of Rushengu, wherein the images are related to at least one of oxygen saturation, oxyhemoglobin concentration, oxyhemoglobin concentration, blood volume, and blood volume change in the first target area The distribution of one, where the oxygen saturation is defined as the concentration of oxyhemoglobin and a ratio of the sum of the concentrations of oxygen and deoxyhemoglobin. 256. The system according to claim 246, wherein the distribution includes at least one of a spatial distribution of red blood cells in the first target region and a temporal distribution of red blood cells in the first target region in time. . 257. The system for applying scope of claim 246, further comprising: a memory unit configured to store the first output signal, the first -56- 588158 One of the baseline and the self-calibrated first output signal. 258. The system of claim 246, wherein the signal analyzer includes: a critical unit for providing a critical amplitude; a comparison unit for comparing the first output signal with a critical amplitude; and A selection unit is used to identify the plurality of samples of the first output signal having substantially similar amplitudes. 259. The system of claim 258, wherein the configuration of the critical unit can receive input from an operator. 260. The system of claim 258, wherein the configuration of the critical unit can calculate a reference amplitude from the first output signal, and calculate the amplitude based on the reference amplitude. 261. The system of claim 260, wherein the reference amplitude is calculated from at least one of the following: a region maximum value of the first output signal from the first target region of the child; from the first target region A region minimum of the first output signal; an average of the first output signal of at least one fraction; a global maximum of the plurality of output signals from the plurality of the target regions of the media; and A combination of the above. 262 · If the system of the scope of patent application is No. 260, where the critical amplitude is the -57- This paper size is applicable to China National Standard (CNS) A4 specifications (210X 297 public love) 588158 A8 B8 C8 D8 A product of amplitude and a predetermined factor. 263. The system of claim 258, wherein the similar amplitude of the plurality of points is one of a point larger than the critical amplitude and a point smaller than the critical amplitude. 264. The system of claim 246, wherein the signal analyzer includes: a critical unit for providing a critical range of the amplitude; a comparison unit for the amplitudes of the first output signal Compared with the threshold value range; and a selection unit for identifying the plurality of points of the first output signal. 265. If the system of the scope of patent application No. 246 is applied, the similar amplitude of the plurality of points is one of the threshold value range and outside the threshold value range. 266. The system of claim 246, wherein the signal processor includes an averaging unit for calculating the first baseline, which is an average of the similar amplitudes, wherein the average is one of the following : An arithmetic average of the similar amplitudes; a geometric mean of the similar amplitudes; a weighted average of the similar amplitudes; and an overall average of the similar amplitudes. 267. For example, please refer to the system of the scope of patent No. 246, wherein the signal includes a calibration unit, which can provide the first output signal of the self-calibration through the first base green and the first round out = normalization . -58- 588158 The system of item 267 is applied silently, wherein the self-calibrated first output # or one of the following: a ratio of the first output signal to its first baseline; and at the first output signal The difference from its first baseline to the first baseline. The system of item 2 in the patent scope No. 246, where the signal analysis test includes at least m units, the configuration of which can improve the No.-signal-noise ratio. This captures the system of the patent scope item, wherein the filter unit includes at least one of the following: a flat Φ unit configured to provide & one of the second output signals from the first target area At least one of an arithmetic average, a geometric average, an overall average, and a weighted average; and a low-pass filter configured to remove high-frequency noise from the first output signal.如 If the system of the scope of patent application No. 246, wherein the signal analyzer advancement includes a control unit, the configuration of which can store a plurality of the baselines measured in a plurality of target areas of the media, and the baselines At least one of them is compared with the other. 272. The system of claim 271, wherein the control unit is configured to provide an average of the plurality of baselines. 273. If the system of the scope of patent application No. 271 is applied, when at least one of the baselines is at least substantially different from at least one of the others, the configuration of the control unit can generate a signal. -59- This paper size is in accordance with Chinese National Standard (CNS) A4 (210X297 mm) 274. 274. Irradiate electromagnetic radiation to the medium; and at least one waveform detector, which is configured to detect electricity from μ media. The system then emits and generates an output k5 tiger in response to the system. The system includes:-a type for generating a hair color or a sexual sword in a target region of a physiological medium; Analytical state can be received and sampled from the at least one waveform detector-the output-number "and its configuration can analyze the amplitude of the first output signal 'and select the first output signal having a substantially similar amplitude A plurality of sampling points of 'where the _th output signal represents the distribution of chromophores or properties in the first target region of the media; a bluff processor whose configuration can calculate a first number based on the first output signal A baseline, and provided by processing the output signal and its first baseline: a self-calibrated first output signal, where the first baseline is a representative amplitude corresponding to the similar amplitudes; and an image processing location A processor configured to form the distributed image of at least one of the chromophores or properties from the self-calibrated first output signal. 275. An optical image system capable of generating an image of a target area of physiological media The images represent the chromophore or property distribution in the target areas. The system includes at least one wave source configured to radiate electromagnetic radiation to the medium; and at least one waveform detector configured to detect The system measures electromagnetic radiation from the medium and generates an output signal in response to the medium. The system includes:, a movable component including at least one of the wave source and the detector, -60- 588158 iii The scope of the patent application is that the configuration of the waveform detector can generate a first output signal from a first area of the media, wherein the first output signal is representative of the distribution in a first target area of the media; an exciter A component configured to generate at least one movement of the movable component; a signal analyzer configured to receive the first output signal to analyze the amplitude of the first output signal, and select a violation of the first output having a substantially similar amplitude A plurality of points of the signal; a processor configured to calculate a first baseline from the first output signal, and provide a self-calibrated first output signal by processing the first output signal and its first baseline Wherein the first baseline is a representative amplitude corresponding to the similar amplitudes; and an image processor configured to form at least one of the chromophores and the properties from the self-calibrated first output signal Image of this distribution. μ 276 · —A system for generating an image representing one or more chromophores and their property distribution in a target area of physiological media, including: an optical probe having at least one wave source and at least one waveform detection The configuration of the wave source can irradiate electromagnetic radiation to a first target area of the physiological medium, and the configuration of the waveform detector can detect the electromagnetic radiation from the first target area of the media, And a first output signal is generated in response to it; a signal analyzer configured to receive and sample the first-round output signal, analyze the amplitude of the output signal of the offender, and select a paper with a substantial mouth -61- The scale applies to the Chinese National Standard (CNS) A4 specification (210X297). 6. The patent application scope is similar to the plurality of sampling points of the output signal; and-: the number can be calculated from the output signal. -The first provides a self-explanation processing output signal and its first baseline and is the first output signal for self-leveling, where 哕 first dragon beginning σ and other similar amplitude-represents the amplitude"I, Quan 疋 277 .: a method of obtaining a calibrated light transmission from an optical imaging system = with an optical probe; and at least-a wave source with a matching = photographing the magnetic material-the target area of the physiological media; and At least one waveform detector 'is capable of generating an output signal in response to the near-infrared electromagnetic radiation thus detected, the method comprising: placing the optical probe on a -th-target area of the medium; and generating light Output signal 'without identifying at least a first portion of the first output signal from the first target region, wherein the signal at the first sub-point has a substantially similar first amplitude; and obtaining a first output signal of the first output signal A baseline is regarded as a representative value equivalent to the actual first amplitude. 278. The method according to item 277 of the patent application, further comprising: normalizing the first output signal through 4 first baselines to provide a Self-calibrating first output signal. 279. The method of claim 278, wherein the normalizing step includes: providing a ratio signal representing a ratio of the first output signal to a first baseline thereof. 588158 Positive year 93. VI. Application scope of patent 280 · For the method of applying scope of patent No. 278, the normalization step includes: 疋 疋 for reference ^, which represents the first output signal and the first baseline And a ratio signal is provided, which is the ratio of the difference signal to the first baseline representing the first round-out signal. 281. ^ A method for applying for a scope of patent No. 277, wherein the generating step package Providing movement of at least one of the wave source and the detector on the first target area; and generating the first output signal during the movement. 282. If the method of claim 277 applies, the steps further include ·· At least one of the identification and obtaining steps is performed ^ Noise from the first output signal. The method "..." please apply for the method of patent scope 282, in which at least one of the following is used : The y step includes arithmetic average of a plurality of the first output signals; geometric average of the plurality of the first output signals; weighted average of the plurality of the first output signals; The output signal is averaged as a whole; and the first part is processed by a low-pass filter. ^ As for at least ~ 284 · If the method of the scope of patent application No. 277, one of the following ...硪 Other steps include: This paper size applies to China National Standard (CNS) A4 specifications -63-588158 I: 2,26 years are being replaced. Η Α8 Β8 C8 D8 6. The patent application park selects a critical amplitude and identifies the first part having the amplitudes greater than the critical amplitude; selects a critical amplitude, and identifies the amplitude having the amplitudes smaller than the critical amplitude. The first part; selecting at least a threshold value range, and identifying the first part having the amplitudes within the threshold value range; and selecting at least a threshold value range, and identifying the amplitudes having the amplitudes outside the threshold value range The first part. 285. According to the method of claiming range 284 of the patent application, wherein the selection step includes one of the following: manually selecting at least one of the critical amplitude and range; and providing a reference amplitude, and according to the reference amplitude At least one of the critical amplitude and range is provided. 286. The method of claim 285, wherein the reference amplitude is one of the following: a region maximum value of the first output signal from the first target area of the child; A region minimum of the first output signal; at least a portion of the average of the first output signal; a global maximum of the plurality of the output signals from the plurality of the target regions of the media; and a combination of the foregoing . 287. The method of applying for the scope of patent No. 285, wherein the providing step package 64 588158 VI. The scope of applying for patent 1J A8 B8 C8 D8 Including: multiplying the reference amplitude by a preselected factor to provide at least one of the critical amplitude and range. 288. If the method according to item 277 of the patent application scope, wherein the obtaining step is one of the following: arithmetically average the similar amplitudes; geometrically average the similar amplitudes; and weighting 4 similar amplitudes average. 289. The method of claim 277, further comprising: placing the optical probe in a second target area of the media; generating a second output signal from the second target area; 5, passing through the first The first baseline of the target area normalizes the first baseline to provide a self-calibrated second output signal. Then "bluff 290. If the method of applying for the scope of patent No. 289, it further includes people in the media in the plurality of these target areas. · The steps of placing and generating around No. 43. Repetition" 291 · As the method of applying for the scope of patent No. 277, it further advances, "^ one step package 4 · Place the photon probe into the _ 第 _ ^ of the media Two output numbers are used to identify that at least one first-stander portion of the second output signal has a substantially similar second amplitude; and, the second obtains a second baseline of the second output signal, which is similar to the second A representative value of the amplitude. Zha et al. 292. If the method of applying for the scope of the patent No. 291, only one step includes: -65- This paper size applies the Chinese National Standard (CNS) A4 specification (210X297 mm) ~ ---- 588158 Patent application scope A8 B8 C8 D8 Calculating a mixed baseline by comparing the first baseline from the first target area and the second baseline from the first mesh area; and normalizing the first and second output signal mounds through the mixed baseline ° 293. The method in item 292 of the 4th patent scope, wherein the calculation step includes one of the following: · average the baselines; average the baselines; and select the baselines One is taken as the mixed baseline. 294 .: A method for obtaining a calibration output signal from an optical imaging system including an optical probe, the optical probe having at least one wave source and at least a / waveform detector, the configuration of the wave source can be near-infrared electromagnetic radiation Target areas irradiated with physiological media. The target areas include a normal area and an abnormal area. The configuration of the waveform detector can generate an output signal in response to the near-infrared electromagnetic radiation detected by the waveform detector. The method includes: Placing the optical probe on a first target area of the media; generating a first output signal without moving the optical probe from the first target area; identifying the normal area belonging to the normal area of the child target area At least a first portion of a first output signal; and obtaining a first baseline of the first output signal from a representative value of the first region of the first output signal, where the first portion belonging to the normal region is characterized by The substantially flat contour is substantially similar to the first amplitude. -66- 588158 1¾¾¾, patent application park 295 ·-A method for calibrating an optical imaging system with an optical probe having at least one wave source for irradiating near-infrared electromagnetic radiation to a target area of a physiological medium; And at least one waveform detector, which can generate an output signal in response to the near-infrared electromagnetic light emission detected by the method, the method includes: placing the optical probe on a first target area of the medium; generating a first An output signal without moving the optical probe from the first target area; before moving the optical probe from the first target area, identifying at least a first portion of the first output signal, the at least one first A part and substantially similar to the first amplitude; and before moving the optical probe from the first target area, obtain a first / first basis of the first output signal from the representative value of the real similar amplitude. If the method of applying for patent scope item 295 further includes: normalizing the first output signal through the first baseline-provided on a substantially instant basis The first self-calibration will be in the application 297. Method 296 patentable scope of the further packets Si. The image of the first output signal, the image of the self-calibration # 1, and the image of the first output signal calibrated based on the first output signal of the first output signal are at least applicable to the reading self-67-this paper scale Towel SS Home Standard (CNS) A4 Specification (21GX 297 Public Love)