JP2574347B2 - Biosensor - Google Patents
BiosensorInfo
- Publication number
- JP2574347B2 JP2574347B2 JP62316610A JP31661087A JP2574347B2 JP 2574347 B2 JP2574347 B2 JP 2574347B2 JP 62316610 A JP62316610 A JP 62316610A JP 31661087 A JP31661087 A JP 31661087A JP 2574347 B2 JP2574347 B2 JP 2574347B2
- Authority
- JP
- Japan
- Prior art keywords
- mediator
- layer
- electrode
- glucose
- oxidase
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Landscapes
- Measuring Or Testing Involving Enzymes Or Micro-Organisms (AREA)
Description
【発明の詳細な説明】 産業上の利用分野 本発明は、種々の試料中の特性成分を迅速かつ容易に
定量することのできるバイオセンサに関するものであ
る。Description: TECHNICAL FIELD The present invention relates to a biosensor capable of quickly and easily quantifying a characteristic component in various samples.
従来の技術 近年、酵素反応と電極反応を結びつけて、試料中の特
定成分を測定するバイオセンサが利用されるようになっ
てきた。2. Description of the Related Art In recent years, biosensors that measure a specific component in a sample by linking an enzyme reaction and an electrode reaction have come to be used.
以下に従来のバイオセンサについて説明する。第４図
は従来のバイオセンサの断面図であり、８は絶縁性基
板、９と10は絶縁性基板８上に導電性カーボンペースト
をスクリーン印刷して形成した測定板と対極である。11
は絶縁層で、絶縁性樹脂ペーストを絶縁性基板8,測定極
9,対極10上に前記同様印刷し、電極部とした。12はメデ
ィエーターを前記電極部表面に塗布して製作したメディ
エーター担持層で、13はメディエーター担持層12上に設
置された酵素固定化層である。Hereinafter, a conventional biosensor will be described. FIG. 4 is a cross-sectional view of a conventional biosensor. Reference numeral 8 denotes an insulating substrate, and reference numerals 9 and 10 denote a measuring plate formed by screen printing a conductive carbon paste on the insulating substrate 8 and a counter electrode. 11
Is an insulating layer, the insulating resin paste is applied to the insulating substrate 8,
9, printing was performed on the counter electrode 10 in the same manner as described above to form an electrode portion. Reference numeral 12 denotes a mediator supporting layer produced by applying a mediator to the surface of the electrode portion, and reference numeral 13 denotes an enzyme immobilization layer provided on the mediator supporting layer 12.
以上のように構成されたバイオセンサについて以下、
その動作を説明する。試料液を上部から滴下すると、ま
ず酵素固定化層13において（１）式に示すように試料液
中の特定成分と酸化酵素が特異的に反応する。The biosensor configured as above is described below.
The operation will be described. When the sample solution is dropped from above, first, a specific component in the sample solution and the oxidase specifically react with each other in the enzyme immobilization layer 13 as shown in equation (1).
Ｓ＋Ｅ（ox）→Ｐ＋Ｅ（red） ……（１） S:特定成分、Ｅ（ox）：酸化型酵素 P:生成分、Ｅ（red）：還元型酵素 さらにメディエーター担持層12において（２）式に示
すようにメディエーターが還元される。S + E (ox) → P + E (red) (1) S: specific component, E (ox): oxidized enzyme P: product, E (red): reduced enzyme Further, in the mediator supporting layer 12, the formula (2) The mediator is reduced as shown in FIG.
Ｅ（red）＋Ｍ（ox）→Ｅ（ox）＋Ｍ（red）……（２） Ｍ（ox）：酸化型メディエーター Ｍ（red）：還元型メディエーター ここで生成した還元型メディエーターを電極系9,10上
で（３）式に示すように酸化し、 Ｍ（red）→Ｍ（ox）＋ｅ ……（３） e:電子 この酸化電流値を測定することにより試料液中の特定
成分濃度を検知する。E (red) + M (ox) → E (ox) + M (red) (2) M (ox): oxidized mediator M (red): reduced mediator The reduced mediator generated here is used as an electrode system 9, 10. Oxidize as shown in equation (3) above, M (red) → M (ox) + e (3) e: Electron The concentration of a specific component in the sample liquid is detected by measuring the oxidation current value. I do.
発明が解決しようとする問題点 しかしながら前記従来の構成では、酸化酵素を使用す
る場合、メディエーター担持層において前記（２）式に
示す反応と、（４）式に示すように試料液中の溶存酸素
との競争反応が起こるため、還元型メディエーターの生
成が阻害される。Problems to be Solved by the Invention However, in the conventional configuration, when an oxidase is used, the reaction represented by the above formula (2) and the dissolved oxygen A competitive reaction occurs with, which inhibits the production of reduced mediators.
Ｅ（red）＋O2→Ｅ（ox）＋H2O2 ……（４） O2:酸素、H2O2:過酸化水素 特にフェロセン，ベンゾキノンなどの難水溶性のメデ
ィエーターを使用する場合、前記（４）式の反応の影響
は大きく、高濃度の特定成分に十分対応できない。ま
た、メディエーター担持層12上に酵素固定化層13を形成
する際、酵素を湿式で固定化する間に、酵素とメディエ
ーターの湿潤状態での共存による相互の酸化還元反応が
進行し、メディエーターの酸化還元状態が不安定で、精
度良い測定ができないという問題点を有していた。E (red) + O 2 → E (ox) + H 2 O 2 ... (4) O 2 : oxygen, H 2 O 2 : hydrogen peroxide Particularly when a poorly water-soluble mediator such as ferrocene or benzoquinone is used. The effect of the reaction of the formula (4) is so large that it cannot sufficiently cope with a high concentration of a specific component. Further, when forming the enzyme immobilization layer 13 on the mediator supporting layer 12, while the enzyme is immobilized in a wet state, a mutual oxidation-reduction reaction due to the coexistence of the enzyme and the mediator in a wet state progresses, and the oxidation of the mediator is performed. There was a problem that the reduction state was unstable and accurate measurement was not possible.
本発明は前記従来の問題点を解決するもので、酸化型
メディエーターを多量に供給し、各層間を密着させるこ
とにより、特定成分を高濃度域まで精度良く測定できる
バイオセンサを提供することを目的とする。An object of the present invention is to solve the above-mentioned conventional problems, and an object of the present invention is to provide a biosensor capable of measuring a specific component with high accuracy up to a high concentration range by supplying a large amount of an oxidized mediator and bringing the layers into close contact. And
問題点を解決するための手段 この目的を達成するために本発明のバイオセンサは、
測定極と対極から成る電極系の表面上にカルボキシメチ
ルセルロースと酸化酵素からなる酸化酵素の固定化層を
直接設置し、さらにその上部に水溶性メディエーターが
不溶性多孔体膜に乾燥状態で担持された層を密着させた
構成とし、酸化酵素の固定化層は試料液に溶解しうる状
態としたものである。Means for Solving the Problems To achieve this object, the biosensor of the present invention comprises:
A layer in which an immobilized layer of oxidase consisting of carboxymethylcellulose and oxidase is directly installed on the surface of an electrode system consisting of the measurement electrode and the counter electrode, and a water-soluble mediator is carried on the insoluble porous membrane in a dry state on top of it. Are adhered to each other, and the immobilized layer of the oxidase is in a state that can be dissolved in the sample solution.
作用 この構成によって、バイオセンサ形成過程において酸
素とメディエーターが湿潤状態で共存することがなく、
酸化型メディエーターが安定に保持され精度良く測定で
きる。また、測定の際、上部から試料液を滴下すると、
まず水溶性メディエーター担持層を通過し、試料液中に
多量のメディエーターが溶解した後、酵素反応が起こる
ため試料液中の溶存酸素の競争反応の影響が減少し、特
定成分が高濃度まで測定可能となり、さらに、各層間の
密着性が高い構造であることから、反応液の移動が円滑
に起こり、精度良い測定が可能である。Action With this configuration, oxygen and the mediator do not coexist in a wet state during the biosensor formation process,
The oxidized mediator is stably retained and can be measured accurately. In addition, at the time of measurement, if a sample liquid is dropped from the top,
First, a large amount of mediator is dissolved in the sample solution after passing through the water-soluble mediator support layer, and then an enzymatic reaction occurs, so the effect of the competitive reaction of dissolved oxygen in the sample solution is reduced, and specific components can be measured at high concentrations. Further, since the structure has a high adhesion between the respective layers, the movement of the reaction solution occurs smoothly, and accurate measurement is possible.
実 施 例 以下本発明の一実施例としてのグルコースセンサにつ
いて、図面を参照しながら説明する。Embodiment Hereinafter, a glucose sensor as one embodiment of the present invention will be described with reference to the drawings.
第１図は本発明の一実施例におけるグルコースセンサ
の断面図を模式的に示すものである。第１図において、
１は絶縁性基板、２は測定極、３は対極、４は絶縁層で
これらは従来例の構造と同じものである。５は酵素固定
化層で、電極部2,3,4上に0.5％カルボキシメチルセルロ
ース水溶液を塗布し45℃30分で恒温乾燥を行い、電極部
と密着性の良い膜厚１μのカルボキシメチルセルロース
膜を得、これを担体として、酵素溶液であるグルコース
オキシダーゼ溶液を塗布，乾燥しグルコースオキシダー
ゼを固定化して作製した。この場合、グコースオキシダ
ーゼはカルボキシメチルセルロースとともに電極上に密
着して乾燥担持されており、試料液に溶解しうる状態で
ある。６はメディエーター担持層で、セルロース多孔体
膜を担体として、メディエーターであるフェリシアン化
カリウムのリン酸塩緩衝液（pH5.6）中に含浸後乾燥し
て作製したものである。７は保持枠で酵素固定化層５の
上に前記の様にして作製したメディエーター担持層６を
密着性良く圧着し保持するためのものである。FIG. 1 schematically shows a sectional view of a glucose sensor according to one embodiment of the present invention. In FIG.
1 is an insulating substrate, 2 is a measuring electrode, 3 is a counter electrode, and 4 is an insulating layer, which is the same as the structure of the conventional example. Reference numeral 5 denotes an enzyme-immobilized layer. A 0.5% carboxymethylcellulose aqueous solution is applied onto the electrodes 2, 3, and 4 and dried at 45 ° C. for 30 minutes. Using this as a carrier, a glucose oxidase solution as an enzyme solution was applied and dried to immobilize glucose oxidase. In this case, the glucose oxidase and the carboxymethylcellulose are tightly dried and supported on the electrode, and can be dissolved in the sample solution. Reference numeral 6 denotes a mediator-supporting layer, which is prepared by impregnating a porous cellulose membrane as a carrier in a phosphate buffer (pH 5.6) of potassium ferricyanide as a mediator and then drying. Reference numeral 7 denotes a holding frame for pressing and holding the mediator supporting layer 6 prepared as described above on the enzyme-immobilized layer 5 with good adhesion.
以上のように構成された本実施例のグルコースセンサ
について、以下その動作を説明する。まず試料液を第１
図の上部に滴下すると、まずメディエーター担持層６に
おいて水溶性のフェリシアン化カリウムが試料液中に溶
解し、高濃度のフェリシアン化カリウム溶液が生成され
る。次に、メディエーター担持層６と密着している酵素
固定化層５に速やかに溶液が移動し、酵素固定化層５に
おいてはグルコースオキシダーゼが試料液に溶解し、グ
ルコースオキシダーゼとフェリシアン化カリウムの反応
が前記の（１）式，（２）式のように起こり、フェロシ
アン化カリウムが生成する。そして、酵素固定化層５と
密着している電極上でフェロシアン化カリウムの酸化電
流値を測定することにより試料中のグルコース濃度を検
知する。The operation of the glucose sensor of the present embodiment configured as described above will be described below. First, the sample liquid is
When dropped on the upper part of the figure, first, water-soluble potassium ferricyanide dissolves in the sample solution in the mediator supporting layer 6, and a high-concentration potassium ferricyanide solution is generated. Next, the solution quickly moves to the enzyme immobilization layer 5 which is in close contact with the mediator support layer 6, and in the enzyme immobilization layer 5, glucose oxidase is dissolved in the sample solution, and the reaction between glucose oxidase and potassium ferricyanide is performed as described above. (1) and (2), and potassium ferrocyanide is produced. Then, the glucose concentration in the sample is detected by measuring the oxidation current value of potassium ferrocyanide on the electrode which is in close contact with the enzyme immobilization layer 5.
第２図は前記のグルコースセンサで測定した酸化電流
値とグルコース水溶液のグルコース濃度との関係を示す
ものである。Ａは本発明の電極系上に酵素固定化層を設
置した上にメディエーター担持層を密着させて形成した
もので、Ｂは従来例の電極上にメディエーター担持層を
設置した上に酵素定化層を形成したものである。この図
より、Ａでは電流値とグルコース濃度は500mg/dlまで非
常に良い直線性を示しているが、これに対し従来例のＢ
では、グルコース濃度が200mg/dl以上の応答に直線性が
見られないことがわかる。これはＢの構成では、メディ
エーターが試料液中に十分存在しないために、メディエ
ーターの還元反応（前記（２）式）の競争反応である溶
存酵素の反応（前記（４）式）が優性となり、メディエ
ーターの還元量がグルコース濃度に反応しないためと考
えられる。FIG. 2 shows the relationship between the oxidation current value measured by the glucose sensor and the glucose concentration of the aqueous glucose solution. A shows an electrode system of the present invention in which an enzyme-immobilized layer was provided and a mediator-supporting layer was adhered to the electrode system, and B was a conventional electrode provided with a mediator-supporting layer and an enzyme-immobilized layer. Is formed. From this figure, in A, the current value and glucose concentration show very good linearity up to 500 mg / dl, whereas in contrast,
Shows that there is no linearity in the response at glucose concentrations of 200 mg / dl or more. This is because, in the configuration B, since the mediator is not sufficiently present in the sample solution, the reaction of the dissolved enzyme (formula (4)), which is a competitive reaction of the mediator reduction reaction (formula (2)), becomes dominant, This is probably because the reduced amount of the mediator does not respond to the glucose concentration.
第３図は前記のグルコースセンサで測定した同一のグ
ルコース水溶液の各グルコースセンサにおける酸化電流
値を示すものである。図中Ａは前記本発明のグルコース
センサ、Ｂは前記従来のグルコースセンサである。この
図より、Ａは各グルコースセンサ間での電流値のばらつ
きが小さく安定した測定値を示している。しかし、Ｂは
応答値の平均が高く、各グルコースセンサ間の電流値の
ばらつきが大きく安定に測定されていないことがわか
る。これは、酵素固定化層作製の際の湿潤状態におい
て、メディエーターの還元が起こり、試料液中のグルコ
ース量に依存しない還元メディエーターが生成し、メデ
ィエーター担持層内に酸化型と還元型メディエーターが
混在するため測定値の平均が大きくなり、ばらつきも増
加すると考えられる。さらに、本願発明のバイオセンサ
は実施例に示した通り、電極系の表面にカルボキシメチ
ルセルロースなどを用いて直接密着した状態で酵素固定
化層を設けているため、気泡が電極表面に直接接触する
状態で発生することはない。従って、本願バイオセンサ
は極めて安定した、信頼性の高い応答が得られ、実用面
から非常に価値の高いものである。FIG. 3 shows oxidation current values of the same glucose aqueous solution measured by the glucose sensor in each glucose sensor. In the figure, A is the glucose sensor of the present invention, and B is the conventional glucose sensor. From this figure, A indicates a stable measured value with small variation in the current value between the glucose sensors. However, it can be seen that B has a high average response value, and the current values among the glucose sensors have large variations, and are not measured stably. This is because the mediator is reduced in the wet state during the preparation of the enzyme-immobilized layer, a reduced mediator independent of the amount of glucose in the sample solution is generated, and the oxidized and reduced mediators are mixed in the mediator-supporting layer. Therefore, it is considered that the average of the measured values increases and the variation also increases. Further, as shown in Examples, the biosensor of the present invention is provided with an enzyme immobilization layer in a state of being directly adhered to the surface of the electrode system using carboxymethylcellulose or the like, so that air bubbles directly contact the electrode surface. It does not occur in. Therefore, the biosensor of the present application can obtain a very stable and highly reliable response, and is very valuable in practical use.
以上のように、本実施例によれば電極系上にグルコー
スオキシダーゼのような酸化酵素の固定化層を設置し、
さらにその上部に水溶性メディエーターであるフェリシ
アン化カリウムが不溶性多孔体膜であるセルロース膜に
乾燥担持された層を密着させた構成を設けたことによ
り、試料液中のグルコース量を高濃度まで精度良く測定
することができる。これは、測定の際、試料液中にフェ
リシアン化カリウムが多量に供給され、かつ各層間の試
料反応液の移動が円滑に行われているためと考えられ
る。As described above, according to this embodiment, an immobilized layer of an oxidase such as glucose oxidase is provided on the electrode system,
In addition, a structure in which a layer in which potassium ferricyanide, which is a water-soluble mediator, is soluble and insoluble on a cellulose membrane, which is an insoluble porous membrane, is adhered to the top of the membrane to accurately measure the amount of glucose in a sample solution to a high concentration. can do. This is probably because a large amount of potassium ferricyanide was supplied to the sample solution during the measurement, and the sample reaction solution was smoothly moved between the layers.
なお本実施例では水溶性メディエーターとしてフェリ
シアン化カリウムを用いたが、他に、プルシアンブルー
ルテニウムレッド，メチレンブルーなどの色素でも良
い。In this embodiment, potassium ferricyanide is used as the water-soluble mediator, but other dyes such as Prussian blue ruthenium red and methylene blue may be used.
発明の効果 以上のように本発明によれば、測定極と対極からなる
電極系の表面上に酸化酵素の固定化層を直接設置し、さ
らにその上部に水溶性メディエーターが不溶性多孔体膜
に乾燥状態で担持された層を密着させた構成とすること
により、特定成分を高濃度域まで精度良く測定できると
いう効果が得られる。Effects of the Invention As described above, according to the present invention, an immobilized layer of an oxidase is directly provided on the surface of an electrode system consisting of a measurement electrode and a counter electrode, and a water-soluble mediator is further dried on the insoluble porous membrane. By adopting a structure in which the layers supported in a state are adhered to each other, an effect that a specific component can be accurately measured up to a high concentration range can be obtained.
第１図は本発明の一実施例におけるグルコースセンサの
断面図、第２図はグルコースセンサのグルコース濃度と
応答電流の相関特性図、第３図は各グルコースセンサと
応答電流の関係図、第４図は従来例におけるバイオセン
サの断面図である。 １……絶縁性基板、２……測定極、３……対極、４……
絶縁層、５……酵素固定化層、６……メディエーター担
持層、７……保持枠。FIG. 1 is a cross-sectional view of a glucose sensor according to an embodiment of the present invention, FIG. 2 is a correlation characteristic diagram of a glucose concentration and a response current of the glucose sensor, FIG. The figure is a cross-sectional view of a conventional biosensor. 1 ... insulating substrate, 2 ... measuring electrode, 3 ... counter electrode, 4 ...
Insulating layer, 5: Enzyme-immobilized layer, 6: Mediator carrying layer, 7: Holding frame.
───────────────────────────────────────────────────── フロントページの続き (72)発明者 小松 きよみ 大阪府門真市大字門真1006番地 松下電 器産業株式会社内 (72)発明者 南海 史朗 大阪府門真市大字門真1006番地 松下電 器産業株式会社内 (72)発明者 河栗 真理子 大阪府門真市大字門真1006番地 松下電 器産業株式会社内 (56)参考文献 特開 昭60−173459（ＪＰ，Ａ) ──────────────────────────────────────────────────の Continued on the front page (72) Inventor Kiyomi Komatsu 1006 Kadoma Kadoma, Osaka Prefecture Inside Matsushita Electric Industrial Co., Ltd. (72) Inventor Mariko Kawaguri 1006 Kazuma, Kadoma, Osaka Pref. Matsushita Electric Industrial Co., Ltd. (56) References JP-A-60-173459 (JP, A)
Claims (1)
電極系の表面上にカルボキシメチルセルロースと酸化酵
素からなる酸化酵素の固定化層を直接設置し、さらにそ
の上部に水溶性メディエーターが不溶性多孔体膜に乾燥
状態で担持された層を密着させた構成であり、前記酸化
酵素の固定化層は試料液に溶解しうることを特徴とする
バイオセンサ。An electrode system comprising a measuring electrode and a counter electrode is provided, and an immobilized layer of oxidase comprising carboxymethylcellulose and oxidase is directly provided on the surface of the electrode system, and a water-soluble mediator is insoluble thereon. A biosensor having a configuration in which a layer supported in a dry state is adhered to a porous membrane, and the immobilized layer of the oxidase can be dissolved in a sample solution.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP62316610A JP2574347B2 (en) | 1987-12-15 | 1987-12-15 | Biosensor |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP62316610A JP2574347B2 (en) | 1987-12-15 | 1987-12-15 | Biosensor |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH01156658A JPH01156658A (en) | 1989-06-20 |
| JP2574347B2 true JP2574347B2 (en) | 1997-01-22 |
Family
ID=18078985
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP62316610A Expired - Lifetime JP2574347B2 (en) | 1987-12-15 | 1987-12-15 | Biosensor |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP2574347B2 (en) |
Families Citing this family (25)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| AU634863B2 (en) * | 1989-12-15 | 1993-03-04 | Roche Diagnostics Operations Inc. | Redox mediator reagent and biosensor |
| US5508171A (en) * | 1989-12-15 | 1996-04-16 | Boehringer Mannheim Corporation | Assay method with enzyme electrode system |
| AU6157898A (en) | 1997-02-06 | 1998-08-26 | E. Heller & Company | Small volume (in vitro) analyte sensor |
| US5997817A (en) | 1997-12-05 | 1999-12-07 | Roche Diagnostics Corporation | Electrochemical biosensor test strip |
| US8480580B2 (en) | 1998-04-30 | 2013-07-09 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
| US8974386B2 (en) | 1998-04-30 | 2015-03-10 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
| US8688188B2 (en) | 1998-04-30 | 2014-04-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
| US8465425B2 (en) | 1998-04-30 | 2013-06-18 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
| US6175752B1 (en) | 1998-04-30 | 2001-01-16 | Therasense, Inc. | Analyte monitoring device and methods of use |
| US9066695B2 (en) | 1998-04-30 | 2015-06-30 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
| US6591125B1 (en) | 2000-06-27 | 2003-07-08 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
| US6338790B1 (en) | 1998-10-08 | 2002-01-15 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
| US6560471B1 (en) | 2001-01-02 | 2003-05-06 | Therasense, Inc. | Analyte monitoring device and methods of use |
| USRE45764E1 (en) | 2001-09-14 | 2015-10-20 | Arkray, Inc. | Concentration measuring method, concentration test instrument, and concentration measuring apparatus |
| US7381184B2 (en) | 2002-11-05 | 2008-06-03 | Abbott Diabetes Care Inc. | Sensor inserter assembly |
| WO2004061420A2 (en) | 2002-12-31 | 2004-07-22 | Therasense, Inc. | Continuous glucose monitoring system and methods of use |
| USD902408S1 (en) | 2003-11-05 | 2020-11-17 | Abbott Diabetes Care Inc. | Analyte sensor control unit |
| CA2556331A1 (en) | 2004-02-17 | 2005-09-29 | Therasense, Inc. | Method and system for providing data communication in continuous glucose monitoring and management system |
| US7766829B2 (en) | 2005-11-04 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and system for providing basal profile modification in analyte monitoring and management systems |
| JP4839451B2 (en) * | 2006-02-02 | 2011-12-21 | 国立大学法人東京海洋大学 | Biosensor and manufacturing method thereof |
| US7620438B2 (en) | 2006-03-31 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and system for powering an electronic device |
| US8226891B2 (en) | 2006-03-31 | 2012-07-24 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods therefor |
| US8123686B2 (en) | 2007-03-01 | 2012-02-28 | Abbott Diabetes Care Inc. | Method and apparatus for providing rolling data in communication systems |
| US20100213057A1 (en) | 2009-02-26 | 2010-08-26 | Benjamin Feldman | Self-Powered Analyte Sensor |
| EP2827140A1 (en) * | 2012-03-15 | 2015-01-21 | Murata Manufacturing Co., Ltd. | Method for manufacturing biosensor |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH0640086B2 (en) * | 1984-02-20 | 1994-05-25 | 松下電器産業株式会社 | Biosensor |
-
1987
- 1987-12-15 JP JP62316610A patent/JP2574347B2/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| JPH01156658A (en) | 1989-06-20 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| JP2574347B2 (en) | Biosensor | |
| EP1308720B1 (en) | Biosensor | |
| JP3267936B2 (en) | Biosensor | |
| US6340428B1 (en) | Device and method for determining the concentration of a substrate | |
| JP3874321B2 (en) | Biosensor | |
| US6740215B1 (en) | Biosensor | |
| JP3297630B2 (en) | Biosensor | |
| JPH0795056B2 (en) | Biosensor | |
| JP2502635B2 (en) | Biosensor | |
| KR100490762B1 (en) | Method of determining substrate, and biosensor | |
| JPH04340453A (en) | Biosensor and separation and quantification method using the same | |
| JP2001330581A (en) | Substrate concentration determination method | |
| JP3267933B2 (en) | Substrate quantification method | |
| JP3024394B2 (en) | Biosensor and measurement method using the same | |
| JP2009244013A (en) | Biosensor for measuring neutral fat | |
| JP3437016B2 (en) | Biosensor and method of quantifying substrate using the same | |
| JPH09274010A (en) | Determination method for substrate | |
| JPH02245650A (en) | Biosensor | |
| JP2001249103A (en) | Biosensor | |
| JP3611268B2 (en) | Biosensor and manufacturing method thereof | |
| JP3070818B2 (en) | Biosensor and manufacturing method thereof | |
| JP2002340838A (en) | Alcohol measuring method, reagent system kit for use in it and biosensor | |
| JP4036883B2 (en) | Biosensor | |
| JPH0758272B2 (en) | Glucose sensor | |
| JPH0792138A (en) | Lactic acid sensor |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| FPAY | Renewal fee payment (event date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20081024 Year of fee payment: 12 |
|
| EXPY | Cancellation because of completion of term | ||
| FPAY | Renewal fee payment (event date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20081024 Year of fee payment: 12 |
