JPH04121652A - Biosensor - Google Patents
BiosensorInfo
- Publication number
- JPH04121652A JPH04121652A JP2241311A JP24131190A JPH04121652A JP H04121652 A JPH04121652 A JP H04121652A JP 2241311 A JP2241311 A JP 2241311A JP 24131190 A JP24131190 A JP 24131190A JP H04121652 A JPH04121652 A JP H04121652A
- Authority
- JP
- Japan
- Prior art keywords
- electrode
- glucose
- electrode system
- biosensor
- pyruvic acid
- 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
- 239000000126 substance Substances 0.000 claims abstract description 26
- 239000000758 substrate Substances 0.000 claims abstract description 17
- 238000006243 chemical reaction Methods 0.000 claims abstract description 13
- 238000005259 measurement Methods 0.000 claims description 10
- 239000007788 liquid Substances 0.000 claims description 9
- 239000011148 porous material Substances 0.000 claims description 8
- 108090000790 Enzymes Proteins 0.000 claims description 6
- 102000004190 Enzymes Human genes 0.000 claims description 6
- 239000007795 chemical reaction product Substances 0.000 claims description 4
- 244000005700 microbiome Species 0.000 claims description 4
- MHAJPDPJQMAIIY-UHFFFAOYSA-N Hydrogen peroxide Chemical compound OO MHAJPDPJQMAIIY-UHFFFAOYSA-N 0.000 abstract description 22
- LCTONWCANYUPML-UHFFFAOYSA-N Pyruvic acid Chemical compound CC(=O)C(O)=O LCTONWCANYUPML-UHFFFAOYSA-N 0.000 abstract description 17
- 229940107700 pyruvic acid Drugs 0.000 abstract description 9
- 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 8
- 239000008103 glucose Substances 0.000 abstract description 8
- 239000012488 sample solution Substances 0.000 abstract description 8
- 229920002284 Cellulose triacetate Polymers 0.000 abstract description 6
- NNLVGZFZQQXQNW-ADJNRHBOSA-N [(2r,3r,4s,5r,6s)-4,5-diacetyloxy-3-[(2s,3r,4s,5r,6r)-3,4,5-triacetyloxy-6-(acetyloxymethyl)oxan-2-yl]oxy-6-[(2r,3r,4s,5r,6s)-4,5,6-triacetyloxy-2-(acetyloxymethyl)oxan-3-yl]oxyoxan-2-yl]methyl acetate Chemical compound O([C@@H]1O[C@@H]([C@H]([C@H](OC(C)=O)[C@H]1OC(C)=O)O[C@H]1[C@@H]([C@@H](OC(C)=O)[C@H](OC(C)=O)[C@@H](COC(C)=O)O1)OC(C)=O)COC(=O)C)[C@@H]1[C@@H](COC(C)=O)O[C@@H](OC(C)=O)[C@H](OC(C)=O)[C@H]1OC(C)=O NNLVGZFZQQXQNW-ADJNRHBOSA-N 0.000 abstract description 6
- 239000012528 membrane Substances 0.000 abstract description 6
- 108010015776 Glucose oxidase Proteins 0.000 abstract description 5
- 239000004366 Glucose oxidase Substances 0.000 abstract description 5
- 108090000854 Oxidoreductases Proteins 0.000 abstract description 5
- 102000004316 Oxidoreductases Human genes 0.000 abstract description 5
- 229940116332 glucose oxidase Drugs 0.000 abstract description 5
- 235000019420 glucose oxidase Nutrition 0.000 abstract description 5
- 239000004744 fabric Substances 0.000 abstract description 4
- WQZGKKKJIJFFOK-VFUOTHLCSA-N beta-D-glucose Chemical compound OC[C@H]1O[C@@H](O)[C@H](O)[C@@H](O)[C@@H]1O WQZGKKKJIJFFOK-VFUOTHLCSA-N 0.000 abstract description 3
- 229920000642 polymer Polymers 0.000 abstract description 3
- UFHFLCQGNIYNRP-UHFFFAOYSA-N Hydrogen Chemical compound [H][H] UFHFLCQGNIYNRP-UHFFFAOYSA-N 0.000 abstract 1
- 229910052739 hydrogen Inorganic materials 0.000 abstract 1
- 239000001257 hydrogen Substances 0.000 abstract 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 abstract 1
- 239000010410 layer Substances 0.000 description 11
- 239000000523 sample Substances 0.000 description 8
- 239000013076 target substance Substances 0.000 description 7
- 238000007254 oxidation reaction Methods 0.000 description 6
- 229940088598 enzyme Drugs 0.000 description 4
- 230000003647 oxidation Effects 0.000 description 4
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 4
- 239000000276 potassium ferrocyanide Substances 0.000 description 3
- 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 3
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 2
- 238000000354 decomposition reaction Methods 0.000 description 2
- 239000001301 oxygen Substances 0.000 description 2
- 229910052760 oxygen Inorganic materials 0.000 description 2
- 229910052697 platinum Inorganic materials 0.000 description 2
- LCTONWCANYUPML-UHFFFAOYSA-M Pyruvate Chemical compound CC(=O)C([O-])=O LCTONWCANYUPML-UHFFFAOYSA-M 0.000 description 1
- 108010042687 Pyruvate Oxidase Proteins 0.000 description 1
- 238000004458 analytical method Methods 0.000 description 1
- 239000012472 biological sample Substances 0.000 description 1
- 239000004020 conductor Substances 0.000 description 1
- 239000012792 core layer Substances 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000003487 electrochemical reaction Methods 0.000 description 1
- 238000003891 environmental analysis Methods 0.000 description 1
- 238000006911 enzymatic reaction Methods 0.000 description 1
- 238000004186 food analysis Methods 0.000 description 1
- 125000002791 glucosyl group Chemical group C1([C@H](O)[C@@H](O)[C@H](O)[C@H](O1)CO)* 0.000 description 1
- 150000004680 hydrogen peroxides Chemical class 0.000 description 1
- WABPQHHGFIMREM-UHFFFAOYSA-N lead(0) Chemical compound [Pb] WABPQHHGFIMREM-UHFFFAOYSA-N 0.000 description 1
- 229920000728 polyester Polymers 0.000 description 1
- -1 potassium ferricyanide Chemical compound 0.000 description 1
- 239000000047 product Substances 0.000 description 1
- 229940076788 pyruvate Drugs 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 238000000926 separation method Methods 0.000 description 1
- 238000004544 sputter deposition Methods 0.000 description 1
Landscapes
- Measuring Or Testing Involving Enzymes Or Micro-Organisms (AREA)
Abstract
Description
【発明の詳細な説明】
（産業上の利用分野）
本発明は食品分析、医療分析、環境分析等の分野におい
て、液体状の試料をセンサ部に滴下するだけで微量の、
しかも複数の特定成分を定量することができるバイオセ
ンサに関する。Detailed Description of the Invention (Industrial Field of Application) The present invention is useful in the fields of food analysis, medical analysis, environmental analysis, etc., by simply dropping a liquid sample onto the sensor unit.
Moreover, the present invention relates to a biosensor that can quantify a plurality of specific components.
（従来の技術）
従来、環境中や生体試料中の特定成分を複雑な前処理を
行なうことなく高精度に測定する手段として、第２図に
示すようなバイオセンサが特開昭５９−１６６８５２号
において提案されている。(Prior Art) Conventionally, a biosensor as shown in Fig. 2 was disclosed in Japanese Patent Application Laid-Open No. 59-166852 as a means of measuring specific components in the environment or biological samples with high precision without complex pretreatment. It has been proposed in
絶縁性基板８にリード線１１．１２をそれぞれ有する白
金などからなる測定極９および対極１０を埋設し、それ
らの電極系の上部を酸化還元酵素を担持させた多孔体１
３で覆ったものである。試料液を多孔体１３に滴下する
と、試料液中に酸化還元酵素が溶解し、試料液中の基質
との間で酵素反応が進行し過酸化水素が発生する。この
過酸化水素を電気化学的に酸化し、この特待られる酸化
電流値から試料液中の基質濃度を求めるものである。A porous body 1 in which a measurement electrode 9 and a counter electrode 10 made of platinum or the like, each having lead wires 11 and 12, are embedded in an insulating substrate 8, and an oxidoreductase is supported on the upper part of the electrode system.
It is covered by 3. When the sample liquid is dropped onto the porous body 13, the oxidoreductase is dissolved in the sample liquid, an enzymatic reaction proceeds with the substrate in the sample liquid, and hydrogen peroxide is generated. This hydrogen peroxide is electrochemically oxidized, and the substrate concentration in the sample solution is determined from the oxidation current value.
（発明が解決しようとする課Ｂ）
このような従来の構成のバイオセンサでは、本質的には
一種類の目的物質の定量しか行なえず、複数種類の酵素
を用いたとしても、これらの酵素系から誘導された一種
類の目的物質の定量か、あるいは多種類の目的物質の総
量でしか定量することができなかった。従って複数種類
の目的物質を分離して検出するには目的物質の種類の数
に応じたセンサを用意しなければならなかった。また、
大きな電極出力を得るためには、電極表面積を大きくす
る必要から形状を大きくセざるを得なかった。(Problem B to be solved by the invention) In a biosensor with such a conventional configuration, essentially only one type of target substance can be quantified, and even if multiple types of enzymes are used, these enzyme systems It has been possible to quantify only one type of target substance derived from the target substance, or the total amount of multiple types of target substances. Therefore, in order to separate and detect multiple types of target substances, it is necessary to prepare sensors corresponding to the number of types of target substances. Also,
In order to obtain a large electrode output, it was necessary to increase the electrode surface area, so the shape had to be made larger.
本発明は上記問題点を解消し、−組の電極系で複数種類
の目的物質の濃度を高感度に検出できるバイオセンサを
提供しようとするものである。The present invention aims to solve the above problems and provide a biosensor that can detect the concentrations of multiple types of target substances with high sensitivity using a pair of electrode systems.
（課題を解決するための手段）
上記目的を達成するため本発明は、少くとも測定極と対
極とを有する電極系、および酵素、微生物等の生体関連
物質を備え、試料液中の基質と前記生体関連物質との反
応により生じる反応生成物の濃度変化を電気化学的に検
出するバイオセンサにおいて、前記測定極および対極の
中、少な（とも一方は導電性もしくは導電処理した基質
透過性の多孔体で構成すると共に、はぼ同一平面上に配
置し、該測定極および対極を挟んで両側に互いに種類の
異なる酵素、微生物等の生体関連物質を担持させた多孔
体よりなる層を設けた構成としたものである。(Means for Solving the Problems) In order to achieve the above object, the present invention comprises an electrode system having at least a measurement electrode and a counter electrode, and biologically related substances such as enzymes and microorganisms, In a biosensor that electrochemically detects a change in the concentration of a reaction product caused by a reaction with a biologically related substance, one of the measuring electrodes and the counter electrode is a porous material that is conductive or permeable to a substrate that has been treated to be conductive. and a layer made of a porous material supporting different types of enzymes, microorganisms, etc. on both sides of the measuring electrode and the counter electrode. This is what I did.
また上記構成のバイオセンサにおいて、前記生体関連物
質を担持させた多孔体よりなる層に、生体関連物質に加
えて酸化型電子受容体をも担持させた構成にしたもので
ある。Furthermore, in the biosensor having the above configuration, the layer made of the porous body supporting the biologically related substance also supports an oxidized electron acceptor in addition to the biologically related substance.
（作 用）
上記のような構成にすることにより、担持させた生体関
連物質に対応する複数の基質を含む試料液を電極系の上
側に配置した多孔体の層に滴下すると、核層の生体関連
物質とこれに対応する基質との反応は速やかに開始し、
一方試料液が基質透過性の電極部を通過して電極系の下
側に配置した多孔体の層に達するとこの層の生体関連物
質とそれに対応する試料液中の基質との反応が、上記上
側の層における反応より遅れて開始する。(Function) With the above configuration, when a sample solution containing a plurality of substrates corresponding to the supported biological substances is dropped onto the layer of the porous body placed above the electrode system, the biological substances in the core layer are dropped. Reactions between related substances and their corresponding substrates begin quickly;
On the other hand, when the sample solution passes through the substrate-permeable electrode section and reaches the porous layer placed below the electrode system, the reaction between the biologically relevant substances in this layer and the corresponding substrate in the sample solution occurs as described above. It starts later than the reaction in the upper layer.
このように反応開始時刻に時間差を住じるので、それぞ
れの反応開始時刻に対応して電極系に逐次パルス電圧を
印加すると、まず第１のパルス電圧により上側の多孔体
に担持させた生体関連物質に対応する基質の濃度に比例
する応答電流が、次に第２のパルス電圧により、上記応
答電流と、下側の多孔体に担持させた生体関連物質に対
応する基質の濃度に比例する電流との和に相当する応答
電流が得られる。従って後者の基質の濃度は再応答゛電
流の差として検出することが可能となる。In this way, since there is a time difference in the reaction start time, when pulse voltages are sequentially applied to the electrode system corresponding to each reaction start time, the first pulse voltage first removes the biological substances supported on the upper porous body. A response current proportional to the concentration of the substrate corresponding to the substance is then generated by the second pulse voltage, which is equal to the response current and a current proportional to the concentration of the substrate corresponding to the biologically relevant substance supported on the lower porous body. A response current corresponding to the sum of Therefore, the concentration of the latter substrate can be detected as a difference in re-response current.
（実施例）
第１図に本発明の一実施例、グルコース、ピルビン酸セ
ンサを示す。同図（ａ）はその断面図、同図（ロ）はそ
の主要部の分解図である。１は測定極でありポリエステ
ルの基布に白金をスパッタリング（膜厚０．２μｓ）し
た導電処理クロスに吸水性高分子を含浸させたもの、２
は対極でリボン状カーボン、３はグルコースオキシダー
ゼを固定化したトリアセチルセルロース膜、４はピルビ
ル酸オキシダーゼを固定化したトリアセチルセルロース
膜、５は絶縁性支持体、６および７はそれぞれ測定極１
および対極２のリード線である。(Example) FIG. 1 shows an example of the present invention, a glucose and pyruvic acid sensor. Figure (a) is a sectional view of the same, and figure (b) is an exploded view of its main parts. 1 is the measurement electrode, which is a conductive cloth made by sputtering platinum (film thickness 0.2 μs) on a polyester base cloth and impregnated with water-absorbing polymer; 2
3 is a triacetylcellulose membrane on which glucose oxidase is immobilized, 4 is a triacetylcellulose membrane on which pyruvate oxidase is immobilized, 5 is an insulating support, and 6 and 7 are each the measurement electrode 1.
and a lead wire for the counter electrode 2.
上記のように構成したセンサにグルコースとピルビン酸
を含む試料液を滴下すると、トリアセチルセルロース膜
３において、まず、試料液中のグルコースがグルコース
オキシダーゼによって分解され過酸化水素を発生する。When a sample liquid containing glucose and pyruvic acid is dropped onto the sensor configured as described above, the glucose in the sample liquid is first decomposed by glucose oxidase in the triacetyl cellulose membrane 3 to generate hydrogen peroxide.
一方試料液中のピルビン酸はグルコースオキシダーゼと
は反応せず、吸水性高分子を含んだ導電処理クロスより
なる測定極ｌを通過し、その下側のトリアセチルセルロ
ース膜４に達しここでピルビン酸オキシダーゼによって
分解され、過酸化水素を発生する。それぞれの過酸水素
の発生には、時間的遅れが存在するが、試料液滴下直後
測定極に対極に対し７００＋Ｖ、パルス幅２００ｍ５の
パルス電圧を印加するとグルコースの分解により最初に
発生した過酸化水素が電気化学的に酸化され、酸化に伴
う応答電流を生じるのでまずこれを測定する。次にたと
えば２秒後に再び上記と同様なパルス電圧を印加すると
、この時点ではピルビン酸の分解による過酸化水素も発
生しており、両過酸化水素の濃度の和に対応する応答電
流を生じる。この結果箱１のパルス電圧による応答電流
はグルコースの濃度に、第２のパルス電圧による応答電
流はグルコースの濃度とピルビン酸の濃度の和に対応し
たものとなる。従って両応答電流の差がピルビン酸の濃
度に対応したものとしてとらえられる。On the other hand, the pyruvic acid in the sample solution does not react with glucose oxidase, passes through the measurement electrode 1 made of a conductive cloth containing a water-absorbing polymer, reaches the triacetylcellulose membrane 4 below, and the pyruvic acid Decomposed by oxidase to generate hydrogen peroxide. There is a time delay in the generation of each hydrogen peroxide, but when a pulse voltage of 700+V and a pulse width of 200 m5 is applied to the measurement electrode immediately after dropping the sample liquid, the hydrogen peroxide that is first generated due to the decomposition of glucose. is electrochemically oxidized and a response current is generated due to oxidation, so this is first measured. Next, for example, when the same pulse voltage as above is applied again after 2 seconds, hydrogen peroxide has also been generated due to the decomposition of pyruvic acid at this point, and a response current corresponding to the sum of the concentrations of both hydrogen peroxides is generated. As a result, the response current due to the pulse voltage in box 1 corresponds to the concentration of glucose, and the response current due to the second pulse voltage corresponds to the sum of the concentration of glucose and the concentration of pyruvic acid. Therefore, the difference between both response currents can be interpreted as corresponding to the concentration of pyruvate.
（発明の効果）
以上説明したように本発明の構成によるバイオセンサは
測定極および対極の中、少なくとも一方は基質透過性の
多孔体で構成し、電極系を挾んで両側に互いに異なる種
類の生体関連物質を担持させた多孔体の層を設けている
ので、試料液中の基質が電極系を通過する際の時間遅れ
を利用した検出が可能となり、−組の電極系でありなが
ら、複数種類の基質の濃度を分離測定を行なわせること
ができる。なお、生体関連物質の種類により反応速度に
遅速がある場合は、反応速度の速い生体関連物質を電極
系の前面の多孔体の層に、反応速度の遅い生体関連物質
を電極系の背面の多孔体の層に担持させることが分離測
定上望ましい。(Effects of the Invention) As explained above, in the biosensor according to the present invention, at least one of the measurement electrode and the counter electrode is made of a substrate-permeable porous material, and different types of living organisms are placed on both sides of the electrode system. Since it is equipped with a layer of porous material that supports related substances, it is possible to perform detection using the time delay when the substrate in the sample liquid passes through the electrode system. The concentration of the substrate can be measured separately. If the reaction rate is slow depending on the type of biological substance, the biological substance with a fast reaction rate is placed in the porous layer on the front side of the electrode system, and the biological substance with a slow reaction rate is placed in the porous layer on the back side of the electrode system. It is desirable for separation and measurement to have it supported on body layers.
本発明の電極系の少なくとも一方の電極は、基質透過性
の導電性または導電処理した多孔体で構成されることか
ら生体関連物質と基質との反応による反応生成物との接
触面積は一般の導体を用いた電極系の場合に較べ著しく
大きくなり、形状を大きくすることなく高感度なセンサ
を作ることができる。At least one electrode of the electrode system of the present invention is composed of a substrate-permeable conductive or conductive-treated porous material, so that the contact area with the reaction product of the reaction between the biologically related substance and the substrate is smaller than that of a general conductor. The size of the sensor is significantly larger than that of an electrode system using a 300°C, and a highly sensitive sensor can be created without increasing the size.
なお上記の実施例では、電気化学的に検出される反応生
成物が過酸化水素の場合について説明したが、生体関連
物質による酸化反応において溶存酸素が少なく充分な酸
化が得られないような場合、また電極電圧の印加により
目的外の電気化学的反応による生成物を生じないよう極
力印加電圧値を低（したい場合など、生体関連物質を担
持させた多孔体の層に酸化型電子受容体をも担持させる
構成が有効である。In the above example, the case where the electrochemically detected reaction product was hydrogen peroxide was explained, but in the case where there is insufficient dissolved oxygen in the oxidation reaction with biologically related substances and sufficient oxidation cannot be obtained, In addition, in order to avoid producing products due to unintended electrochemical reactions due to the application of electrode voltage, the applied voltage value should be kept as low as possible. A configuration in which it is supported is effective.
例えば生体関連物質として酸化還元酸素を用いる場合、
酸化型電子受容体、フェリシアン化カリウムを共存させ
ると、この電子受容体は、基質との酸化反応に伴って還
元型電子受容体、フェロシアン化カリウムに変じ、この
フェロシアン化カリウムが前述の過酸化水素と同等な電
気化学的役目を果たし、電極系への電圧印加により同様
な応答電流を得ることができる。この還元型電子受容体
、フェロシアン化カリウムの場合、必要な電圧（酸化電
位）は３００ｍＶであり、過酸化水素の場合の７００ｍ
Ｖの半分以下に抑制することができる。For example, when using redox oxygen as a biologically related substance,
When an oxidized electron acceptor, potassium ferricyanide, coexists, this electron acceptor changes into a reduced electron acceptor, potassium ferrocyanide, through an oxidation reaction with the substrate, and this potassium ferrocyanide becomes a substance equivalent to the aforementioned hydrogen peroxide. It plays an electrochemical role, and a similar response current can be obtained by applying a voltage to the electrode system. In the case of this reduced electron acceptor, potassium ferrocyanide, the required voltage (oxidation potential) is 300 mV, and in the case of hydrogen peroxide, it is 700 mV.
It can be suppressed to less than half of V.
上記説明中、電極系としては測定極および対極のみに言
及したが特に精度を必要とする場合は、よく知られてい
るように参考極を併設した構造が有効である。In the above description, only the measurement electrode and the counter electrode were mentioned as the electrode system, but when particularly high precision is required, a structure that includes a reference electrode is effective, as is well known.
第１図は本発明の一実施例のバイオセンサを示す。同図
（帽よその縦断面図、同図（ｂ）はその主要部の分解図
である。第２図は従来のバイオセンサの縦断面図である
。
１．９・・・測定極、２，１ｏ・・・対極、３．４・・
・互いに異なる種類の生体関連物質を担持させた多孔体
よりなる層、
３・・・酸化還元酵素を担持させた
多孔体。FIG. 1 shows a biosensor according to an embodiment of the present invention. The same figure (longitudinal cross-sectional view of the cap, the same figure (b) is an exploded view of its main parts. Figure 2 is a vertical cross-sectional view of a conventional biosensor. 1.9... Measuring electrode, 2 , 1o... Opposite pole, 3.4...
- A layer made of a porous material supporting different types of biologically related substances, 3... A porous material supporting an oxidoreductase.
Claims (2)
び酵素、微生物等の生体関連物質を備え、試料液中の基
質と前記生体関連物質との反応により生じる反応生成物
の濃度変化を電気化学的に検出するバイオセンサにおい
て、 前記測定極および対極の中、少なくとも一方は、導電性
もしくは導電処理した基質透過性の多孔体で構成すると
共に、該測定極および対極をほぼ同一平面上に配置し、
これら両極を挟んで両側に互いに異なる種類の酵素、微
生物等の生体関連物質を担持させた多孔体よりなる層を
設けたことを特徴とするバイオセンサ。(1) Equipped with an electrode system having at least a measurement electrode and a counter electrode, and a biologically related substance such as an enzyme or a microorganism, and electrochemically detects a change in the concentration of a reaction product caused by a reaction between a substrate in a sample liquid and the biologically related substance. In the biosensor for detecting the ,
A biosensor characterized in that a layer made of a porous body carrying different types of enzymes, microorganisms, and other biologically related substances is provided on both sides of these two poles.
生体関連物質を担持させた多孔体よりなる層に、生体関
連物質に加えて酸化型電子受容体をも担持させたことを
特徴とするバイオセンサ。(2) The biosensor according to claim 1, characterized in that the layer made of the porous material supporting the biologically relevant substance also supports an oxidized electron acceptor in addition to the biologically relevant substance. biosensor.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2241311A JP2977258B2 (en) | 1990-09-13 | 1990-09-13 | Biosensor |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2241311A JP2977258B2 (en) | 1990-09-13 | 1990-09-13 | Biosensor |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH04121652A true JPH04121652A (en) | 1992-04-22 |
| JP2977258B2 JP2977258B2 (en) | 1999-11-15 |
Family
ID=17072405
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP2241311A Expired - Fee Related JP2977258B2 (en) | 1990-09-13 | 1990-09-13 | Biosensor |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP2977258B2 (en) |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5532634A (en) * | 1993-11-10 | 1996-07-02 | Kabushiki Kaisha Toshiba | High-integration J-K flip-flop circuit |
| US8083993B2 (en) | 2003-06-20 | 2011-12-27 | Riche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
| US8092668B2 (en) | 2004-06-18 | 2012-01-10 | Roche Diagnostics Operations, Inc. | System and method for quality assurance of a biosensor test strip |
| US8293538B2 (en) | 2003-06-20 | 2012-10-23 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
| US8507289B1 (en) | 2003-06-20 | 2013-08-13 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
-
1990
- 1990-09-13 JP JP2241311A patent/JP2977258B2/en not_active Expired - Fee Related
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5532634A (en) * | 1993-11-10 | 1996-07-02 | Kabushiki Kaisha Toshiba | High-integration J-K flip-flop circuit |
| US8083993B2 (en) | 2003-06-20 | 2011-12-27 | Riche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
| US8293538B2 (en) | 2003-06-20 | 2012-10-23 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
| US8507289B1 (en) | 2003-06-20 | 2013-08-13 | Roche Diagnostics Operations, Inc. | System and method for coding information on a biosensor test strip |
| US8092668B2 (en) | 2004-06-18 | 2012-01-10 | Roche Diagnostics Operations, Inc. | System and method for quality assurance of a biosensor test strip |
Also Published As
| Publication number | Publication date |
|---|---|
| JP2977258B2 (en) | 1999-11-15 |
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