JPH04160354A - Biosensor - Google Patents
BiosensorInfo
- Publication number
- JPH04160354A JPH04160354A JP2284173A JP28417390A JPH04160354A JP H04160354 A JPH04160354 A JP H04160354A JP 2284173 A JP2284173 A JP 2284173A JP 28417390 A JP28417390 A JP 28417390A JP H04160354 A JPH04160354 A JP H04160354A
- Authority
- JP
- Japan
- Prior art keywords
- oxidation
- electrode
- potential
- reduction
- biosensor
- 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.)
- Pending
Links
- 239000000126 substance Substances 0.000 claims abstract description 13
- 239000000758 substrate Substances 0.000 claims abstract description 13
- 238000006479 redox reaction Methods 0.000 claims abstract description 9
- 108090000854 Oxidoreductases Proteins 0.000 claims abstract description 7
- 102000004316 Oxidoreductases Human genes 0.000 claims abstract description 7
- 239000012488 sample solution Substances 0.000 claims abstract description 6
- 238000006243 chemical reaction Methods 0.000 claims abstract description 4
- 238000005259 measurement Methods 0.000 claims description 7
- 239000000523 sample Substances 0.000 claims description 7
- 230000033116 oxidation-reduction process Effects 0.000 abstract 5
- 238000010276 construction Methods 0.000 abstract 1
- 238000012883 sequential measurement Methods 0.000 abstract 1
- JVTAAEKCZFNVCJ-UHFFFAOYSA-N lactic acid Chemical compound CC(O)C(O)=O JVTAAEKCZFNVCJ-UHFFFAOYSA-N 0.000 description 16
- AZQWKYJCGOJGHM-UHFFFAOYSA-N 1,4-benzoquinone Chemical compound O=C1C=CC(=O)C=C1 AZQWKYJCGOJGHM-UHFFFAOYSA-N 0.000 description 13
- 102000004190 Enzymes Human genes 0.000 description 12
- 108090000790 Enzymes Proteins 0.000 description 12
- 229940088598 enzyme Drugs 0.000 description 12
- RXGJTUSBYWCRBK-UHFFFAOYSA-M 5-methylphenazinium methyl sulfate Chemical compound COS([O-])(=O)=O.C1=CC=C2[N+](C)=C(C=CC=C3)C3=NC2=C1 RXGJTUSBYWCRBK-UHFFFAOYSA-M 0.000 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 description 9
- 239000008103 glucose Substances 0.000 description 9
- 108010015776 Glucose oxidase Proteins 0.000 description 8
- 239000004366 Glucose oxidase Substances 0.000 description 8
- 229940116332 glucose oxidase Drugs 0.000 description 8
- 235000019420 glucose oxidase Nutrition 0.000 description 8
- 235000014655 lactic acid Nutrition 0.000 description 8
- 239000004310 lactic acid Substances 0.000 description 8
- 230000003647 oxidation Effects 0.000 description 8
- 238000007254 oxidation reaction Methods 0.000 description 8
- 108010073450 Lactate 2-monooxygenase Proteins 0.000 description 6
- LCTONWCANYUPML-UHFFFAOYSA-N Pyruvic acid Chemical compound CC(=O)C(O)=O LCTONWCANYUPML-UHFFFAOYSA-N 0.000 description 6
- 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 description 5
- WABPQHHGFIMREM-UHFFFAOYSA-N lead(0) Chemical compound [Pb] WABPQHHGFIMREM-UHFFFAOYSA-N 0.000 description 5
- -1 potassium ferricyanide Chemical group 0.000 description 4
- 239000013076 target substance Substances 0.000 description 4
- 238000010586 diagram Methods 0.000 description 3
- 229920000642 polymer Polymers 0.000 description 3
- 229940107700 pyruvic acid Drugs 0.000 description 3
- 108010042687 Pyruvate Oxidase Proteins 0.000 description 2
- 239000004809 Teflon Substances 0.000 description 2
- 229920006362 Teflon® Polymers 0.000 description 2
- XSQUKJJJFZCRTK-UHFFFAOYSA-N Urea Chemical compound NC(N)=O XSQUKJJJFZCRTK-UHFFFAOYSA-N 0.000 description 2
- 239000004202 carbamide Substances 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 239000007788 liquid Substances 0.000 description 2
- 230000001590 oxidative effect Effects 0.000 description 2
- 239000008363 phosphate buffer Substances 0.000 description 2
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 2
- 239000002861 polymer material Substances 0.000 description 2
- LCTONWCANYUPML-UHFFFAOYSA-M Pyruvate Chemical compound CC(=O)C([O-])=O LCTONWCANYUPML-UHFFFAOYSA-M 0.000 description 1
- 238000004458 analytical method Methods 0.000 description 1
- 239000012472 biological sample Substances 0.000 description 1
- 238000000502 dialysis 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
- ZIPLUEXSCPLCEI-UHFFFAOYSA-N iminomethylideneazanide Chemical compound [NH-]C#N ZIPLUEXSCPLCEI-UHFFFAOYSA-N 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 239000012528 membrane Substances 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 229910052697 platinum Inorganic materials 0.000 description 1
- 239000011148 porous material Substances 0.000 description 1
- 229940076788 pyruvate Drugs 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
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、環境分析等の分野で、
液体試料をセンサ部に滴下するだけで微量かつ複数の成
分を、迅速、簡便に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 Application Field] The present invention is applicable to the fields of food analysis, medical analysis, environmental analysis, etc.
The present invention relates to a biosensor that can quickly and easily quantify trace amounts of a plurality of components simply by dropping a liquid sample onto a sensor section.
従来、環境中や生体試料中の目的成分を、複雑な前処理
を行なうことなく、高精度に測定するバイオセンサとし
て、第３図に示すような構造のものが提案されている。BACKGROUND ART Conventionally, a biosensor having a structure as shown in FIG. 3 has been proposed as a biosensor that can measure target components in the environment or biological samples with high precision without performing complicated pretreatment.
（特開昭５９−１６６８５２．）図において２１は測定
極、２２は対極、２３はリード線、２４は酵素固定化多
孔体である。(JP-A-59-166852.) In the figure, 21 is a measurement electrode, 22 is a counter electrode, 23 is a lead wire, and 24 is an enzyme-immobilized porous body.
このバイオセンサは、絶縁基板にそれぞれリード線２３
を有する白金などからなる測定極２１と対極２２が埋設
され、これらの電極系の上部を覆うように酸化還元酵素
及び電子受容体を担持した多孔体２４が取付けられたも
のである。This biosensor has lead wires 23 on each insulating substrate.
A measuring electrode 21 and a counter electrode 22 made of platinum or the like are buried, and a porous body 24 carrying an oxidoreductase and an electron acceptor is attached to cover the upper part of these electrode systems.
試料液を多孔体２４上に滴下すると、試料液に多孔体２
４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。この還元された電子受容体を電気化学的に酸化し、
この時得られる酸化電流値から試料中の基質濃度を求め
る。When the sample liquid is dropped onto the porous body 24, the porous body 2
The oxidoreductase and electron acceptor in 4 are dissolved, an enzymatic reaction proceeds with the substrate in the sample solution, and the electron acceptor is reduced. This reduced electron acceptor is electrochemically oxidized,
The substrate concentration in the sample is determined from the oxidation current value obtained at this time.
上記のような従来の構成では、多孔体に複数の酵素を固
定化しても、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の
定量しかできなかった。In the conventional configuration described above, even if multiple enzymes are immobilized on a porous material, it is only possible to quantify one type of target substance derived from these enzyme systems or the total amount of multiple types of target substances. could not.
そして、複数の目的物質の濃度を検出するには、目的物
質の数に応したセンサを用意しなければならなかった。In order to detect the concentrations of multiple target substances, it is necessary to prepare sensors corresponding to the number of target substances.
本発明は上記の問題を解消するためになされたもので、
一つの電極系で複数成分を迅速かつ高精度に定量できる
ものを提供することを目的とする。The present invention was made to solve the above problems.
The purpose of the present invention is to provide a system that can quickly and accurately quantify multiple components using one electrode system.
本発明のバイオセンサは、複数の酸化還元酵素と酸化還
元電位の異なる電子メディエータとの複数の組合せを用
い、該複数の組合せと試料溶液中の複数の基質との反応
に際して生成した物質濃度変化を、測定極と対極とから
なる一つの電極系に、生成物質の酸化還元電位の低い方
から順次酸化還元反応が進むよう所定のパルスを印加し
て検出し、複数の基質の濃度を逐次的に計測できるよう
に構成したものである。The biosensor of the present invention uses a plurality of combinations of a plurality of oxidoreductases and an electron mediator having different redox potentials, and detects changes in substance concentration generated when the plurality of combinations react with a plurality of substrates in a sample solution. , a predetermined pulse is applied to one electrode system consisting of a measurement electrode and a counter electrode so that the redox reaction proceeds sequentially from the one with the lowest redox potential of the product substance, and the concentration of multiple substrates is sequentially detected. It is configured so that it can be measured.
〔作 用］
上記のような構成にすると、反応によって特定の酸化還
元電位を有する物質が生成する。[Function] With the above configuration, a substance having a specific redox potential is produced by reaction.
電極上で生成物の酸化還元反応が進行するよう所定の電
位を印加するが、この場合、酸化還元電位の低い生成物
の電位から印加してゆく。こうすると、同一電極上で選
択的に生成物質の酸化還元反応を進行させることができ
る。この結果生じた酸化還元電流値より各基質の濃度を
求めることができる。A predetermined potential is applied so that the redox reaction of the product proceeds on the electrode, but in this case, the voltage is applied starting from the potential of the product having the lowest redox potential. This allows the redox reaction of the product to proceed selectively on the same electrode. The concentration of each substrate can be determined from the resulting redox current value.
第１図は本発明の一実施例を示す。 FIG. 1 shows an embodiment of the invention.
図において１は測定極、２は対極、３はリード線、４は
テフロン隔膜、５ａ、５ｂはｐＦ１７．Ｏのりん酸緩衝
液を含有した吸水性高分子物質、６ａ。In the figure, 1 is a measurement electrode, 2 is a counter electrode, 3 is a lead wire, 4 is a Teflon diaphragm, 5a and 5b are pF17. Water-absorbing polymeric material containing O phosphate buffer, 6a.
６ｂ、６ｃは電子メディエータ層で６ａはフェナジンメ
トサルフェート、６ｂはフェリシアン化カリウム、６ｃ
はｐ−ベンゾキノンである。７ａ。6b and 6c are electron mediator layers, 6a is phenazine methosulfate, 6b is potassium ferricyanide, 6c
is p-benzoquinone. 7a.
７ｂ、７ｃは酵素層で、７ａはグルコースオキシダーゼ
、７ｂは乳酸オキシダーゼ、７ｃはピルビン酸オキシダ
ーゼである。7b and 7c are enzyme layers, 7a is glucose oxidase, 7b is lactate oxidase, and 7c is pyruvate oxidase.
グルコース、乳酸、ピルビン酸を含有する試料液を作用
させると、試料液は吸水性高分子物質５ａに吸収され、
さらに、電子メディエータ層６ａ、６ｂ、６ｃを通過し
てメディエータとともに酵素層７ａ、７ｂ、７ｃに到達
する。When a sample solution containing glucose, lactic acid, and pyruvic acid is applied, the sample solution is absorbed by the water-absorbing polymer substance 5a,
Furthermore, the electrons pass through the electron mediator layers 6a, 6b, and 6c and reach the enzyme layers 7a, 7b, and 7c together with the mediator.
酵素層７ａではグルコースオキシダーゼとグルコースが
反応し、これにともないメディエータの酸化型フェナジ
ンメトサルフェートが還元型フェナジンメトサルフェー
トとなる。In the enzyme layer 7a, glucose oxidase and glucose react, and as a result, the mediator, oxidized phenazine methosulfate, becomes reduced phenazine methosulfate.
同様に、酵素層７ｂでは乳酸オキシダーゼと乳酸が反応
し、これにともないメディエータの酸化型フェリシアン
化カリウムが還元型フェリシアン化カリウムとなり、酵
素ＪＷ７Ｃではピルビン酸オキシダーゼとピルビン酸が
反応し、これにともないメディエータの酸化型ｐ−ベン
ゾキノンが還元型ｐ−ベンゾキノンとなる。Similarly, in the enzyme layer 7b, lactate oxidase and lactic acid react, and as a result, the mediator oxidized potassium ferricyanide becomes reduced potassium ferricyanide.In the enzyme JW7C, pyruvate oxidase and pyruvate react, and as a result, the mediator oxidizes. Type p-benzoquinone becomes reduced type p-benzoquinone.
このようにして生成されたそれぞれの還元型メディエー
タが電極上部の吸水性高分子物質５ｂに到達する。Each of the reduced mediators thus generated reaches the water-absorbing polymer substance 5b above the electrode.
電極に還元型フェナジンメトサルフェートを酸化する電
位＋〇、 ０５ Ｖをパルスで印加し、その時の酸化電
流値からグルコースを定量する。次に、還元型フェリシ
アン化カリウムを酸化する電位＋０．３０Ｖをパルスで
印加する。この際還元型フェナジンメトサルフェートも
酸化されるため、この時生ずる酸化電流値は、グルコー
スと乳酸の総量を示す。さらに、還元型ｐ−ベンゾキノ
ンを酸化する電位＋〇、 ５０ Ｖをパルスで印加する
。この際還元型フェナジンメトサルフェート還元型ｐ−
ベンゾキノンも同時に酸化されるため、この時生ずる酸
化電流値は、グルコース、乳酸、ピルビン酸の総量を示
す。これらの電流値の差からそれぞれグルコース、乳酸
、ピルビン酸の量が計測できる。A potential of +0.05 V for oxidizing reduced phenazine methosulfate is applied in pulses to the electrode, and glucose is quantified from the oxidation current value at that time. Next, a potential of +0.30 V that oxidizes the reduced potassium ferricyanide is applied in a pulse manner. Since the reduced phenazine methosulfate is also oxidized at this time, the oxidation current value generated at this time indicates the total amount of glucose and lactic acid. Furthermore, a potential of 50 V, which oxidizes the reduced p-benzoquinone, is applied in pulses. At this time, reduced phenazine methosulfate and reduced p-
Since benzoquinone is also oxidized at the same time, the oxidation current value generated at this time indicates the total amount of glucose, lactic acid, and pyruvic acid. The amounts of glucose, lactic acid, and pyruvic acid can be measured from the difference in these current values.
第２図は本発明の他の実施例を示す。FIG. 2 shows another embodiment of the invention.
図において１１は測定極、１２は対極、１３はリード線
、１４はｐＨ７，０りん酸緩衝液を含有する吸水性高分
子物質、１５はグルコースオキシダーゼ分子内に電子メ
ディエータのフェナジンメトサルフェートを固定化した
グルコースオキシダーゼ、１６は乳酸オキシダーゼ分子
内に電子メディエータのｐ−ベンゾキノンを固定化した
乳酸オキシダーゼである。In the figure, 11 is a measurement electrode, 12 is a counter electrode, 13 is a lead wire, 14 is a water-absorbing polymer material containing a pH 7.0 phosphate buffer, and 15 is an electron mediator phenazine methosulfate immobilized within a glucose oxidase molecule. Glucose oxidase 16 is a lactate oxidase in which p-benzoquinone, an electron mediator, is immobilized within the lactate oxidase molecule.
固定化方法は、尿素３．６ｇ、シアノアミド２ｍｇ、イ
オン交換水１０ｍｊ２に酵素とメディエータを熔解し、
固定化する。この後、透析膜により不要の尿素を取り除
く。上記のようにして分子内にメディエータを固定化し
た酵素を測定極表面上に配置する。The immobilization method was to dissolve the enzyme and mediator in 3.6 g of urea, 2 mg of cyanoamide, and 10 mj2 of ion-exchanged water.
to be fixed. After this, unnecessary urea is removed using a dialysis membrane. The enzyme having the mediator immobilized in its molecule as described above is placed on the surface of the measurement electrode.
グルコースと乳酸を含有する試料を作用させると、試料
が吸水性高分子物質１４に吸収されて、測定極１１表面
上の酵素層に到達し、試料中のグルコースはグルコース
オキシダーゼと、乳酸は乳酸オキシダーゼと反応する。When a sample containing glucose and lactic acid is reacted, the sample is absorbed by the water-absorbing polymer substance 14 and reaches the enzyme layer on the surface of the measuring electrode 11, and the glucose in the sample is converted into glucose oxidase and the lactic acid is converted into lactate oxidase. reacts.
この反応の結果それぞれの酵素内に固定化したメディエ
ータが酸化型から還元型に変化する。これを測定極１１
表面上で酸化電位を印加して酸化する。As a result of this reaction, the mediator immobilized within each enzyme changes from an oxidized form to a reduced form. Measure this at pole 11
Oxidation occurs by applying an oxidizing potential on the surface.
グルコースオキシダーゼ内に固定化されたフェナジンメ
トサルフェートに対しては＋〇、 ０５ Ｖのパルス電
位を印加する。この時流れた酸化電流値からグルコース
量を求める。A pulse potential of +0.05 V is applied to phenazine methosulfate immobilized within glucose oxidase. The amount of glucose is determined from the value of the oxidation current flowing at this time.
次に、乳酸オキシダーゼ内に固定化されたｐ −ベンゾ
キノンに対しては、＋ ０．５ Ｖのパルス電位を印加
する。この時グルコースオキシダーゼ内の還元型フェナ
ジンメトサルフェートも同時に酸化される。Next, a pulse potential of +0.5 V is applied to p-benzoquinone immobilized within lactate oxidase. At this time, reduced phenazine methosulfate within glucose oxidase is also oxidized at the same time.
この時流れた酸化電流値と＋〇、 ０５ Ｖのパルス電
位を印加したときの酸化電流値の差から乳酸量を求める
。The amount of lactic acid is determined from the difference between the oxidation current value flowing at this time and the oxidation current value when a pulse potential of +0.05 V is applied.
〔発明の効果］
以上説明したように、本発明によれば、−組の電極上で
選択的に生成物質の酸化還元反応を進行させて、複数の
基質を逐次的に同一センサで計測することができ、作業
能率の向上に寄与する効果が大である。[Effects of the Invention] As explained above, according to the present invention, a plurality of substrates can be sequentially measured with the same sensor by selectively allowing the redox reaction of the product to proceed on the - set of electrodes. This has a great effect on improving work efficiency.
第１図は本発明の一実施例を示す説明図、第２図は本発
明の他の実施例を示す説明図、第３図は従来のバイオセ
ンサ；の−例を示す説明図である。
１・・・測定極、２・・・対極、３・・・リード線、４
・・・テフロン隔膜、５ａ、５ｂ・・・吸水性高分子物
質、６ａ、６ｂ、６ｃｍ・・電子メディエータ層、７ａ
。
７ｂ、７ｃ・・・酵素層、１１・・・測定極、１２・・
・対極、１３・・・リード線、１４・・・吸水性高分子
物質、１５・・・グルコースオキシダーゼ、１６・・・
オキシダーゼ。
特許出願人 新日本無線株式会社
第１図
第２図
第３図FIG. 1 is an explanatory diagram showing one embodiment of the present invention, FIG. 2 is an explanatory diagram showing another embodiment of the present invention, and FIG. 3 is an explanatory diagram showing an example of a conventional biosensor. 1...Measurement electrode, 2...Counter electrode, 3...Lead wire, 4
...Teflon diaphragm, 5a, 5b...Water-absorbing polymer material, 6a, 6b, 6cm...Electron mediator layer, 7a
. 7b, 7c... Enzyme layer, 11... Measuring electrode, 12...
- Counter electrode, 13... Lead wire, 14... Water-absorbing polymeric substance, 15... Glucose oxidase, 16...
oxidase. Patent applicant New Japan Radio Co., Ltd. Figure 1 Figure 2 Figure 3
Claims (2)
メディエータとの複数の組合せを用い、該複数の組合せ
と試料溶液中の複数の基質との反応に際して生成した物
質濃度変化を、測定極と対極とからなる電極系で電気化
学的に検知し、試料中の基質濃度を測定するバイオセン
サで、生成物質の酸化還元電位の低い方から順次酸化還
元反応が進むよう所定のパルス電圧を印加し、複数の基
質の濃度を逐次的に計測できるように構成したことを特
徴とするバイオセンサ。(1) Using multiple combinations of multiple oxidoreductases and electron mediators with different redox potentials, changes in substance concentration generated during the reaction between the multiple combinations and multiple substrates in the sample solution are measured using a measurement electrode. This is a biosensor that electrochemically detects the substrate concentration in a sample with an electrode system consisting of a counter electrode and a counter electrode.A predetermined pulse voltage is applied so that the redox reaction proceeds in order from the one with the lowest redox potential of the product substance. , a biosensor characterized in that it is configured to be able to sequentially measure the concentrations of multiple substrates.
なる電子メディエータを固定化したものを用いることを
特徴とする請求項第１項記載のバイオセンサ。(2) The biosensor according to claim 1, characterized in that a plurality of oxidoreductases each having immobilized electron mediators having different redox potentials are used.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2284173A JPH04160354A (en) | 1990-10-24 | 1990-10-24 | Biosensor |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2284173A JPH04160354A (en) | 1990-10-24 | 1990-10-24 | Biosensor |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH04160354A true JPH04160354A (en) | 1992-06-03 |
Family
ID=17675128
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP2284173A Pending JPH04160354A (en) | 1990-10-24 | 1990-10-24 | Biosensor |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH04160354A (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2009042631A3 (en) * | 2007-09-24 | 2009-05-22 | Bayer Healthcare Llc | Multi-electrode test sensors |
| JP2010054379A (en) * | 2008-08-28 | 2010-03-11 | Tanita Corp | Biosensor, method of manufacturing the same, and method of using the same |
| WO2023054231A1 (en) * | 2021-09-29 | 2023-04-06 | 日東電工株式会社 | Mixed reagent for electrochemical measurement |
-
1990
- 1990-10-24 JP JP2284173A patent/JPH04160354A/en active Pending
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| WO2009042631A3 (en) * | 2007-09-24 | 2009-05-22 | Bayer Healthcare Llc | Multi-electrode test sensors |
| CN101849180A (en) * | 2007-09-24 | 2010-09-29 | 拜尔健康护理有限责任公司 | Multi-region and potential test sensors, methods, and systems |
| JP2010540934A (en) * | 2007-09-24 | 2010-12-24 | バイエル・ヘルスケア・エルエルシー | Multi-region / multi-potential test sensor, method and system |
| JP2014122911A (en) * | 2007-09-24 | 2014-07-03 | Bayer Healthcare Llc | Analyte testing sensor, method, and system in multi-region analysis |
| US9846136B2 (en) | 2007-09-24 | 2017-12-19 | Ascensia Diabetes Care Holdings Ag | Multi-region and potential test sensors, methods and systems |
| US10895550B2 (en) | 2007-09-24 | 2021-01-19 | Ascensia Diabetes Care Holdings Ag | Multi-region and potential test sensors, methods, and systems |
| JP2010054379A (en) * | 2008-08-28 | 2010-03-11 | Tanita Corp | Biosensor, method of manufacturing the same, and method of using the same |
| WO2023054231A1 (en) * | 2021-09-29 | 2023-04-06 | 日東電工株式会社 | Mixed reagent for electrochemical measurement |
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