JPS62232554A - Biosensor - Google Patents
BiosensorInfo
- Publication number
- JPS62232554A JPS62232554A JP61075728A JP7572886A JPS62232554A JP S62232554 A JPS62232554 A JP S62232554A JP 61075728 A JP61075728 A JP 61075728A JP 7572886 A JP7572886 A JP 7572886A JP S62232554 A JPS62232554 A JP S62232554A
- Authority
- JP
- Japan
- Prior art keywords
- electrode
- porous body
- biosensor
- electrode system
- substrate
- 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.)
- Granted
Links
- 239000000758 substrate Substances 0.000 claims abstract description 16
- 102000004169 proteins and genes Human genes 0.000 claims abstract description 13
- 108090000623 proteins and genes Proteins 0.000 claims abstract description 13
- 102000009027 Albumins Human genes 0.000 claims abstract description 9
- 108010088751 Albumins Proteins 0.000 claims abstract description 9
- 108090000854 Oxidoreductases Proteins 0.000 claims abstract description 8
- 102000004316 Oxidoreductases Human genes 0.000 claims abstract description 8
- 238000005259 measurement Methods 0.000 claims description 17
- 102000004190 Enzymes Human genes 0.000 claims description 5
- 108090000790 Enzymes Proteins 0.000 claims description 5
- 239000007788 liquid Substances 0.000 claims description 5
- 238000006911 enzymatic reaction Methods 0.000 claims description 4
- 238000007650 screen-printing Methods 0.000 claims description 3
- 238000006243 chemical reaction Methods 0.000 claims description 2
- 239000000126 substance Substances 0.000 claims description 2
- 239000003575 carbonaceous material Substances 0.000 claims 1
- WQZGKKKJIJFFOK-GASJEMHNSA-N Glucose Natural products OC[C@H]1OC(O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-GASJEMHNSA-N 0.000 abstract description 9
- 108010015776 Glucose oxidase Proteins 0.000 abstract description 9
- 239000004366 Glucose oxidase Substances 0.000 abstract description 9
- 239000008103 glucose Substances 0.000 abstract description 9
- 229940116332 glucose oxidase Drugs 0.000 abstract description 9
- 235000019420 glucose oxidase Nutrition 0.000 abstract description 9
- -1 polyethylene terephthalate Polymers 0.000 abstract description 7
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 abstract description 6
- 229910052799 carbon Inorganic materials 0.000 abstract description 6
- 238000001035 drying Methods 0.000 abstract description 5
- 239000011347 resin Substances 0.000 abstract description 5
- 229920005989 resin Polymers 0.000 abstract description 5
- 239000004677 Nylon Substances 0.000 abstract description 3
- 239000004745 nonwoven fabric Substances 0.000 abstract description 3
- 229920001778 nylon Polymers 0.000 abstract description 3
- 239000000243 solution Substances 0.000 abstract description 3
- 229920000139 polyethylene terephthalate Polymers 0.000 abstract description 2
- 239000005020 polyethylene terephthalate Substances 0.000 abstract description 2
- 239000012086 standard solution Substances 0.000 abstract description 2
- 230000001590 oxidative effect Effects 0.000 abstract 1
- 239000008055 phosphate buffer solution Substances 0.000 abstract 1
- BYGOPQKDHGXNCD-UHFFFAOYSA-N tripotassium;iron(3+);hexacyanide Chemical compound [K+].[K+].[K+].[Fe+3].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-] BYGOPQKDHGXNCD-UHFFFAOYSA-N 0.000 abstract 1
- 239000012488 sample solution Substances 0.000 description 11
- 239000000370 acceptor Substances 0.000 description 10
- 239000011148 porous material Substances 0.000 description 5
- 239000000523 sample Substances 0.000 description 5
- 238000001179 sorption measurement Methods 0.000 description 5
- 239000012472 biological sample Substances 0.000 description 4
- 238000000576 coating method Methods 0.000 description 4
- 229940088598 enzyme Drugs 0.000 description 4
- 238000000034 method Methods 0.000 description 4
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 4
- 239000011248 coating agent Substances 0.000 description 3
- 239000007772 electrode material Substances 0.000 description 3
- 238000010586 diagram Methods 0.000 description 2
- 238000007865 diluting Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 230000003647 oxidation Effects 0.000 description 2
- 238000007254 oxidation reaction Methods 0.000 description 2
- 229910052697 platinum Inorganic materials 0.000 description 2
- 239000000276 potassium ferrocyanide Substances 0.000 description 2
- 239000012460 protein solution Substances 0.000 description 2
- 210000002966 serum Anatomy 0.000 description 2
- XOGGUFAVLNCTRS-UHFFFAOYSA-N tetrapotassium;iron(2+);hexacyanide Chemical compound [K+].[K+].[K+].[K+].[Fe+2].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-].N#[C-] XOGGUFAVLNCTRS-UHFFFAOYSA-N 0.000 description 2
- 229920000297 Rayon Polymers 0.000 description 1
- 239000007864 aqueous solution Substances 0.000 description 1
- 210000004369 blood Anatomy 0.000 description 1
- 239000008280 blood Substances 0.000 description 1
- 229920002678 cellulose Polymers 0.000 description 1
- 239000001913 cellulose Substances 0.000 description 1
- 239000000919 ceramic Substances 0.000 description 1
- 239000003795 chemical substances by application Substances 0.000 description 1
- 238000004140 cleaning Methods 0.000 description 1
- 239000000470 constituent Substances 0.000 description 1
- 239000003431 cross linking reagent Substances 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 238000010438 heat treatment Methods 0.000 description 1
- 238000007654 immersion Methods 0.000 description 1
- 230000010354 integration Effects 0.000 description 1
- 239000006193 liquid solution Substances 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 239000012528 membrane Substances 0.000 description 1
- 239000008363 phosphate buffer Substances 0.000 description 1
- 239000004417 polycarbonate Substances 0.000 description 1
- 229920000515 polycarbonate Polymers 0.000 description 1
- 238000007639 printing Methods 0.000 description 1
- 239000002964 rayon Substances 0.000 description 1
- 238000003756 stirring Methods 0.000 description 1
- 238000005406 washing Methods 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
- 238000009736 wetting Methods 0.000 description 1
- 230000037303 wrinkles Effects 0.000 description 1
Landscapes
- Investigating Or Analysing Biological Materials (AREA)
- Measuring Or Testing Involving Enzymes Or Micro-Organisms (AREA)
- Apparatus Associated With Microorganisms And Enzymes (AREA)
Abstract
Description
【発明の詳細な説明】
産業上の利用分野
本発明は、種々の微量の生体試料中の特定成分について
、試料液を希釈することなく迅速かつ簡易に定量するこ
とのできるバイオセンサに関する。DETAILED DESCRIPTION OF THE INVENTION Field of Industrial Application The present invention relates to a biosensor that can quickly and easily quantify specific components in various minute amounts of biological samples without diluting the sample liquid.
従来の技術
従来、血液などの生体試料中の特定成分について、試、
料液の希釈や撹拌などの操作を行うことなく高精度に定
量する方式としては、第4図に示す様なバイオセンサが
提案されている(例えば、特開昭59−166852号
公報)。このバイオセンサは、絶縁性基板9にリード1
2.13をそれぞれ有する白金などからなる測定極10
および対極11を埋設し、これらの電極系の露出部分を
酸化還元酵素および電子受容体を担持した多孔体で覆っ
たものである。試料液を多孔体上へ滴下すると、試料液
に多孔体中の酸化還元酵素と電子受容体が溶解し、試料
液中の基質との間で酵素反応が進行し、電子受容体が還
元される。酵素反応終了後、この還元された電子受容体
を電気化学的に酸化し、このとき得られる酸化電流値か
ら試料液中の基質濃度を求めることがなされていた。Conventional technology Traditionally, specific components in biological samples such as blood have been tested,
A biosensor as shown in FIG. 4 has been proposed as a method for highly accurate quantitative determination without operations such as diluting or stirring the liquid solution (for example, Japanese Patent Application Laid-Open No. 166852/1982). This biosensor has a lead 1 on an insulating substrate 9.
Measuring electrodes 10 made of platinum or the like, each having 2.13
and a counter electrode 11 are buried, and the exposed portions of these electrode systems are covered with a porous material carrying an oxidoreductase and an electron acceptor. When a sample solution is dropped onto a porous material, the oxidoreductase and electron acceptor in the porous material are dissolved in the sample solution, an enzymatic reaction proceeds with the substrate in the sample solution, and the electron acceptor is reduced. . After the enzymatic reaction is completed, the reduced electron acceptor is electrochemically oxidized, and the substrate concentration in the sample solution is determined from the oxidation current value obtained at this time.
発明が解決しようとする問題点
この様な従来の構成では、多孔体については、測定毎に
取り替えることにより簡易に測定に供することができる
が、電極系については洗浄等の操作が必要である。一方
電極系をも含めて測定毎の使い棄てが可能となれば、測
定操作上、極めて簡易になるものの、白金等の電極材料
や構成等の面から、非常に高価なものにならざるを得な
い。Problems to be Solved by the Invention In such a conventional configuration, the porous body can be easily used for measurement by replacing it for each measurement, but the electrode system requires operations such as cleaning. On the other hand, if the electrode system, including the electrode system, could be disposed of after each measurement, the measurement operation would be extremely simple, but it would be extremely expensive due to the electrode materials such as platinum and the structure. do not have.
本発明はこれらの点について種々検討の結果、電極系と
多孔体を一体化することにより、生体試料中の特定成分
を極めて容易に迅速かつ高精度に定量することのできる
安価なディスポーザブルタイプのバイオセンサを提供す
るものである。As a result of various studies on these points, the present invention has developed an inexpensive disposable type biotechnology that can extremely easily quantify specific components in biological samples quickly and with high precision by integrating an electrode system and a porous body. It provides a sensor.
問題点を解決するだめの手段
本発明は上記問題点を解決するため、絶縁性基板に少な
くとも測定極と対極からなる電極系を設け、酵素と電子
受容体と試料液の反応に際しての物質濃度変化を電気化
学的に前記電極系で検知し、試料液中の基質濃度を測定
するバイオセンサにおいて、前記電極系の少なくとも測
定極の表面をあらかじめ蛋白質で被覆し、さらに酸化還
元酵素および電子受容体を担持した多孔体とともに一体
化したものである。これ、によりあらかじめ予想される
試料液中の蛋白質等の吸着による測定のばらつきを防ぐ
ことができる。Means to Solve the Problems In order to solve the above-mentioned problems, the present invention provides an electrode system consisting of at least a measurement electrode and a counter electrode on an insulating substrate, and detects changes in substance concentration during reactions between enzymes, electron acceptors, and sample liquids. In a biosensor that electrochemically detects substrate concentration in a sample solution by electrochemically detecting it with the electrode system, the surface of at least the measurement electrode of the electrode system is coated with protein in advance, and further coated with a redox enzyme and an electron acceptor. It is integrated with the supported porous body. This can prevent measurement variations due to adsorption of proteins, etc. in the sample solution, which may be expected in advance.
作用
本発明によれば、電極系をも含めたディスポーザブルタ
イプのバイオセンサを構成することができ、試料液を多
孔体に添加することにより、極めて容易に基質濃度を測
定することができる。Effects According to the present invention, a disposable type biosensor including an electrode system can be constructed, and the substrate concentration can be extremely easily measured by adding a sample liquid to a porous body.
しかも、電極系の表面をあらかじめ蛋白質で被膜するこ
とにより、試料液中の蛋白質等の吸着による測定のばら
つきがなくなり、精度のよい測定が可能となった。Moreover, by coating the surface of the electrode system with protein in advance, measurement variations due to adsorption of proteins in the sample solution are eliminated, making it possible to perform highly accurate measurements.
実施例 以下、本発明の一実施例について説明する。Example An embodiment of the present invention will be described below.
バイオセンサの一例として、グルコースセンサについて
説明する。第1図は、グルコースセンサの一実施例につ
いて示したもので、構成部分の分解図である。ポリエチ
レンテレフタレートからなる絶縁性基板1に、スクリー
ン印刷により導電性カーボンペーストを印刷し、加熱乾
燥することによシ、対極2.測定極3.参照極4からな
る電極系を形成する。次に、電極系を部分的に覆い、各
々の電極の電気化学的に作用する部分となる2′。A glucose sensor will be described as an example of a biosensor. FIG. 1 shows an embodiment of a glucose sensor, and is an exploded view of the constituent parts. A counter electrode 2. is formed by printing a conductive carbon paste on an insulating substrate 1 made of polyethylene terephthalate by screen printing and drying it by heating. Measuring pole 3. An electrode system consisting of a reference electrode 4 is formed. 2' then partially covers the electrode system and becomes the electrochemically active part of each electrode.
s/ 、 4/ (各1ffiIIP)を残す様に、絶
縁性ペーストを前記同様印刷し、加熱処理して絶縁層5
を形成する0
この電極系(2/ 、 3/ 、 4/ )の露出表面
を被覆するように、アルブミン(rs o mg/cc
)の水溶液を滴下し、乾燥する。An insulating paste is printed in the same manner as above so as to leave s/, 4/ (1 ffiIIP each), and heat treated to form an insulating layer 5.
Albumin (rs o mg/cc) was added to coat the exposed surfaces of this electrode system (2/, 3/, 4/) to form a
) was added dropwise and dried.
次に穴を開けた樹脂製の保持枠6を絶縁層6に接着し、
前記電極系2’、 3’、 4’を覆う様に多孔体7を
穴の中に保持する。さらに多孔体より小さい径の開孔部
を有する樹脂製カバー8を接着し、全体を一体化する。Next, a resin holding frame 6 with holes is glued to the insulating layer 6,
The porous body 7 is held in the hole so as to cover the electrode systems 2', 3', and 4'. Furthermore, a resin cover 8 having an opening having a diameter smaller than that of the porous body is adhered to integrate the entire body.
この一体化されたバイオセンサについて、測定極3に沿
った断面図を第2図に示す。上記に用いた多孔体は、酸
化還元酵素としてグルコースオキシダーゼ100 mf
と電子受容体としてフェリシアン化カリウム150mf
ftPH6,6のリン酸緩衝液1 ml に溶解した液
をナイロン不織布に含浸後、減圧乾燥して作製したもの
であ為。A cross-sectional view along the measurement electrode 3 of this integrated biosensor is shown in FIG. The porous body used above contained 100 mf of glucose oxidase as an oxidoreductase.
and potassium ferricyanide 150 mf as an electron acceptor.
This material was prepared by impregnating a nylon nonwoven fabric with a solution dissolved in 1 ml of phosphate buffer with a pH of 6.6 and drying it under reduced pressure.
上記の様に構成したグルコースセンサの多孔体へ試料液
としてグルコース標準液を滴下し、滴下2分後k、参照
極を基準にして測定極の電位をアノード方向へo、1v
/秒の速度で掃引した。この場合、添加されたグルコー
スは多孔体に担持されたグルコースオキシダーゼの作用
でフェリシアン化カリウムと反応してフェロシアン化カ
リウムを生成する。そこで、上記のアノード方向への掃
引により、生成したフェロシアン化カリウム濃度に基づ
く酸化電流が得られ、この電流値は基質であるグルコー
ス濃度に対応する。Glucose standard solution is dropped as a sample solution into the porous body of the glucose sensor configured as above, and 2 minutes after dropping, the potential of the measurement electrode is changed to o, 1v toward the anode with reference to the reference electrode.
/second. In this case, the added glucose reacts with potassium ferricyanide by the action of glucose oxidase supported on the porous material to produce potassium ferrocyanide. Therefore, by the above-mentioned sweep toward the anode, an oxidation current based on the concentration of potassium ferrocyanide produced is obtained, and this current value corresponds to the concentration of glucose, which is the substrate.
上記ノグルコースセンサに血清サンプルを滴下し、2分
後に得られたピーク電流値は第3図の人に示すように非
常に再現性のよいものであった。A serum sample was dropped onto the noglucose sensor, and the peak current value obtained 2 minutes later had very good reproducibility as shown in Figure 3.
第3図のBは電極系の表面に蛋白質を被覆していない時
、人と同様に測定したものでピーク電流値のばらつきが
大きい。これは、電極材料のカーボンペーストの表面に
血清中の蛋白質等が吸着され、その吸着の度合が測定毎
に変化し、ピーク電流がばらついたものと考えられる。B in FIG. 3 was measured in the same manner as humans when no protein was coated on the surface of the electrode system, and the peak current value varied widely. This is thought to be because proteins in serum were adsorbed on the surface of the carbon paste of the electrode material, and the degree of adsorption varied with each measurement, causing the peak current to vary.
しかし、あらかじめアルブミンで処理しておくと、カー
ボンペースト表面の吸着部位はすべてアルブミンが吸着
されているため、試料液中の蛋白質などによる吸着によ
って測定値がばらつくことが防げ、再現性の良い応答が
得られる。However, if the carbon paste is treated with albumin in advance, all of the adsorption sites on the surface of the carbon paste will have albumin adsorbed, which will prevent the measured values from varying due to adsorption by proteins in the sample solution, resulting in a response with good reproducibility. can get.
アルブミンのかわりに、グルコースオキシダーゼの水溶
液100mg/cc を用いて、電極系の表面を被覆し
た。この場合も、アルブミンと同様に再現性の良い応答
が得られた。しかも、アルブミンと同様にグルコースオ
キシダーゼの被膜により電極表面が親水性となりぬれが
良くなり、少量のサンプル液でもすみやかに電極表面に
広がり応答が得られた。又、非常にぬれやすいため、電
極表面にアワが形成されることもなくなった。さらに、
グルコースオキシダーゼで電極系を被覆することにより
、酵素反応に関与する酸化還元酵素の量が増加し、充分
量の電子受容体(フェリシアン化カリウム)を多孔体7
に担持しておけば、アルブばンで被覆した時よりも高濃
度のグルコース濃度の測定が可能となった。グルコース
オキシダーゼを高密度に電極表面に担持すれば、多孔体
7にフェリシアン化カリウムのみを担持しておき試料液
を滴下するとフェリシアン化カリウムを溶かした試料液
が電極表面上でグルコースオキシダーゼと反応させるこ
ともできる。Instead of albumin, an aqueous solution of glucose oxidase (100 mg/cc) was used to coat the surface of the electrode system. In this case as well, a response with good reproducibility was obtained as with albumin. Furthermore, like albumin, the glucose oxidase coating made the electrode surface hydrophilic and improved wetting, so that even a small amount of sample liquid quickly spread over the electrode surface and a response was obtained. In addition, since it is very easy to wet, no wrinkles are formed on the electrode surface. moreover,
By coating the electrode system with glucose oxidase, the amount of redox enzyme involved in the enzymatic reaction increases, and a sufficient amount of electron acceptor (potassium ferricyanide) is transferred to the porous material 7.
If it was supported on the membrane, it became possible to measure a higher glucose concentration than when coated with albuman. If glucose oxidase is supported at a high density on the electrode surface, if only potassium ferricyanide is supported on the porous body 7 and a sample solution is dropped, the sample solution in which potassium ferricyanide is dissolved can react with glucose oxidase on the electrode surface. .
被覆する蛋白質は、アルブミンやグルコースオキシダー
ゼに限定されない。又、被覆の方法は、蛋白質の水溶液
を滴下し乾燥する方法に限らず、蛋白質の水溶液に浸漬
後水洗して乾燥したり、酵素などは架橋剤により固定化
してもよい。The protein to be coated is not limited to albumin or glucose oxidase. Further, the coating method is not limited to the method of dropping an aqueous protein solution and drying, but may also be immersion in an aqueous protein solution followed by washing with water and drying, or immobilization of enzymes and the like with a crosslinking agent.
電極系を形成する方法としてのスクリーン印刷は、均一
な特性を有するディスポーザブルタイプのバイオセンサ
を安価に製造することができ、特に、価格が安く、しか
も安定した電極材料であるカーボンを用いて電極を形成
するのに好都合な方法である。Screen printing as a method for forming electrode systems can produce disposable biosensors with uniform characteristics at low cost, and in particular, it is possible to fabricate electrodes using carbon, which is an inexpensive and stable electrode material. This is a convenient way to form.
本発明のバイオセンサにおける一体化の方法としては、
実施例に示した枠体、カバーなどの形や組み合わせに限
定されるものではない。また、用いる多孔体としては、
ナイロン不織以外に、セルロース、レーヨン、セラミッ
ク、ポリカーボネート等からなる多孔体を単独、あるい
は組み合わせて用いることができる。さらに酸化還元酵
素と電子受容体の組み合わせも前記実施例に限定される
ことはなく、本発明の主旨に合致するものであれば用い
ることができる。一方、上記実施例においては、電極系
として3電極力式の場合について述べだが、対極と測定
極からなる2電極力式でも測定は可能である。The method of integration in the biosensor of the present invention is as follows:
The present invention is not limited to the shapes and combinations of frames, covers, etc. shown in the examples. In addition, the porous body used is
In addition to nylon nonwovens, porous bodies made of cellulose, rayon, ceramic, polycarbonate, etc. can be used alone or in combination. Further, the combination of oxidoreductase and electron acceptor is not limited to the above examples, and any combination can be used as long as it meets the gist of the present invention. On the other hand, in the above embodiment, a three-electrode force type electrode system is described, but measurement can also be performed using a two-electrode force type consisting of a counter electrode and a measurement electrode.
発明の効果
このように本発明のバイオセンサは、絶縁性基板、電極
系および酸化還元酵素と電子受容体を担持した多孔体を
一体化することによシ、極めて容易に生体試料中の基質
濃度を測定することができ、さらに電極表面を蛋白質で
被覆して再現性を向上させたものである。Effects of the Invention As described above, the biosensor of the present invention extremely easily adjusts the substrate concentration in a biological sample by integrating an insulating substrate, an electrode system, and a porous body carrying an oxidoreductase and an electron acceptor. can be measured, and the electrode surface is coated with protein to improve reproducibility.
第1図は本発明の一実施例であるバイオセンサの分解斜
視図、第2図はその縦断面図、第3図はバイオセンサの
応答特性図、第4図は従来のバイオセンサの縦断面図で
ある。
1・・・・・・基板、2・・・・・・対極、3・・・・
・・測定極、4・・・・・・参照、極、6・・・・・・
絶縁層、6・・・・・・保持枠、7・・・・・・多孔体
、8・・・・・・カバー。
代理人の氏名 弁理士 中 尾 敏 男 ほか1名第2
図
第3図
嘉4図Fig. 1 is an exploded perspective view of a biosensor that is an embodiment of the present invention, Fig. 2 is a longitudinal cross-sectional view thereof, Fig. 3 is a response characteristic diagram of the biosensor, and Fig. 4 is a longitudinal cross-section of a conventional biosensor. It is a diagram. 1...Substrate, 2...Counter electrode, 3...
...Measurement pole, 4...Reference, pole, 6...
Insulating layer, 6... Holding frame, 7... Porous body, 8... Cover. Name of agent: Patent attorney Toshio Nakao and 1 other person 2nd
Figure 3 Figure 4
Claims (5)
絶縁性基板を備え、酵素と電子受容体と試料液の反応に
際しての物質濃度変化を電気化学的に前記電極系で検知
し前記試料液の基質濃度を測定するバイオセンサであっ
て、前記電極系の少くとも測定極の表面をあらかじめ蛋
白質で被覆しさらに酸化還元酵素および電子受容体を担
持した多孔体とともに一体化したことを特徴とするバイ
オセンサ。(1) An insulating substrate is provided with an electrode system consisting of at least a measurement electrode and a counter electrode, and the electrode system electrochemically detects a change in substance concentration during the reaction between an enzyme, an electron acceptor, and a sample liquid. A biosensor for measuring the substrate concentration of a biosensor, characterized in that the surface of at least the measuring electrode of the electrode system is coated with a protein in advance and is further integrated with a porous body carrying an oxidoreductase and an electron acceptor. biosensor.
ている特許請求の範囲第1項記載のバイオセンサ。(2) The biosensor according to claim 1, wherein the electrode system includes a measurement electrode, a counter electrode, and a reference electrode.
されたカーボンを主体とする材料からなる特許請求の範
囲第1項又は第2項記載のバイオセンサ。(3) The biosensor according to claim 1 or 2, wherein the electrode system is made of a carbon-based material formed by screen printing on an insulating substrate.
られる酸化還元酵素である特許請求の範囲第1項記載の
バイオセンサ。(4) The biosensor according to claim 1, wherein the protein covering the surface of the electrode system is an oxidoreductase used in an enzyme reaction.
る特許請求の範囲第1項記載のバイオセンサ。(5) The biosensor according to claim 1, wherein the protein covering the surface of the electrode system is albumin.
Priority Applications (6)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP61075728A JP2624236B2 (en) | 1986-04-02 | 1986-04-02 | Biosensor |
PCT/JP1986/000311 WO1986007632A1 (en) | 1985-06-21 | 1986-06-19 | Biosensor and method of manufacturing same |
EP86903608A EP0230472B2 (en) | 1985-06-21 | 1986-06-19 | Biosensor and method of manufacturing same |
US07/027,204 US4897173A (en) | 1985-06-21 | 1986-06-19 | Biosensor and method for making the same |
DE3687646T DE3687646T3 (en) | 1985-06-21 | 1986-06-19 | BIOSENSOR AND THEIR PRODUCTION. |
US07/774,129 US5185256A (en) | 1985-06-21 | 1991-10-15 | Method for making a biosensor |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP61075728A JP2624236B2 (en) | 1986-04-02 | 1986-04-02 | Biosensor |
Publications (2)
Publication Number | Publication Date |
---|---|
JPS62232554A true JPS62232554A (en) | 1987-10-13 |
JP2624236B2 JP2624236B2 (en) | 1997-06-25 |
Family
ID=13584620
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP61075728A Expired - Lifetime JP2624236B2 (en) | 1985-06-21 | 1986-04-02 | Biosensor |
Country Status (1)
Country | Link |
---|---|
JP (1) | JP2624236B2 (en) |
Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH02157645A (en) * | 1988-12-09 | 1990-06-18 | Matsushita Electric Ind Co Ltd | Biosensor |
JPH03239958A (en) * | 1990-02-17 | 1991-10-25 | Omron Corp | Biochemical measuring instrument |
JPH05281181A (en) * | 1992-03-30 | 1993-10-29 | Nippon Telegr & Teleph Corp <Ntt> | Enzyme modified electrochemical detector and its manufacture |
JPH05340915A (en) * | 1991-10-18 | 1993-12-24 | Matsushita Electric Ind Co Ltd | Biosensor and measuring method using the same |
EP0691539A2 (en) * | 1994-06-27 | 1996-01-10 | Bayer Corporation | Method of making and amperometric electrodes |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS59166852A (en) * | 1983-03-11 | 1984-09-20 | Matsushita Electric Ind Co Ltd | Biosensor |
JPS60173452A (en) * | 1984-02-20 | 1985-09-06 | Fuji Electric Corp Res & Dev Ltd | Formation of immobilized enzyme film for enzyme electrode |
-
1986
- 1986-04-02 JP JP61075728A patent/JP2624236B2/en not_active Expired - Lifetime
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPS59166852A (en) * | 1983-03-11 | 1984-09-20 | Matsushita Electric Ind Co Ltd | Biosensor |
JPS60173452A (en) * | 1984-02-20 | 1985-09-06 | Fuji Electric Corp Res & Dev Ltd | Formation of immobilized enzyme film for enzyme electrode |
Cited By (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH02157645A (en) * | 1988-12-09 | 1990-06-18 | Matsushita Electric Ind Co Ltd | Biosensor |
JPH03239958A (en) * | 1990-02-17 | 1991-10-25 | Omron Corp | Biochemical measuring instrument |
JPH05340915A (en) * | 1991-10-18 | 1993-12-24 | Matsushita Electric Ind Co Ltd | Biosensor and measuring method using the same |
JPH05281181A (en) * | 1992-03-30 | 1993-10-29 | Nippon Telegr & Teleph Corp <Ntt> | Enzyme modified electrochemical detector and its manufacture |
EP0691539A2 (en) * | 1994-06-27 | 1996-01-10 | Bayer Corporation | Method of making and amperometric electrodes |
EP0691539A3 (en) * | 1994-06-27 | 1996-07-24 | Bayer Ag | Method of making and amperometric electrodes |
Also Published As
Publication number | Publication date |
---|---|
JP2624236B2 (en) | 1997-06-25 |
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