JPH0572172A - Enzyme electrode - Google Patents
Enzyme electrodeInfo
- Publication number
- JPH0572172A JPH0572172A JP3238177A JP23817791A JPH0572172A JP H0572172 A JPH0572172 A JP H0572172A JP 3238177 A JP3238177 A JP 3238177A JP 23817791 A JP23817791 A JP 23817791A JP H0572172 A JPH0572172 A JP H0572172A
- Authority
- JP
- Japan
- Prior art keywords
- electrode
- enzyme
- sensitive
- insulating
- sensitive portion
- 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.)
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- Apparatus Associated With Microorganisms And Enzymes (AREA)
Abstract
Description
【０００１】[0001]
【産業上の利用分野】この発明は、酵素電極に関し、フ
ォトリソグラフィー技術を使用せずに下地電極の感応部
を形成し得る酵素電極に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an enzyme electrode, and more particularly to an enzyme electrode capable of forming a sensitive portion of a base electrode without using a photolithography technique.
【０００２】[0002]
【従来の技術】図１１は、従来の酵素電極を示す斜視図
である。このプレーナ型酵素電極は、絶縁性電極支持基
板１と、この絶縁性電極支持基板１上に形成された下地
電極２と、この下地電極２を含む絶縁性支持基板１上に
形成される絶縁性保護膜（感光性樹脂）６と、この絶縁
性保護膜６上に形成される固定化酵素膜３とから成る。
上記下地電極２は、リード部２１ｂを介して一端を接続
部２１ｃとし、他端を感応部２１ａとする作用電極２１
と、この作用電極２１に対し平行状に配備される参照電
極２２とから成る。また、前記固定化酵素膜３は、図１
２で示すように、電極２側の第一の高分子膜３１と、中
間層である固定化酵素層３２と、表面側の第二の高分子
膜３３の三層で構成されている。2. Description of the Related Art FIG. 11 is a perspective view showing a conventional enzyme electrode. This planar type enzyme electrode includes an insulating electrode supporting substrate 1, an underlying electrode 2 formed on the insulating electrode supporting substrate 1, and an insulating property formed on the insulating supporting substrate 1 including the underlying electrode 2. It comprises a protective film (photosensitive resin) 6 and an immobilized enzyme film 3 formed on the insulating protective film 6.
The base electrode 2 has a working electrode 21 having one end as a connecting portion 21c and the other end as a sensitive portion 21a via a lead portion 21b.
And a reference electrode 22 arranged in parallel with the working electrode 21. In addition, the immobilized enzyme membrane 3 is shown in FIG.
As shown by 2, it is composed of three layers of a first polymer film 31 on the electrode 2 side, an immobilized enzyme layer 32 as an intermediate layer, and a second polymer film 33 on the surface side.
【０００３】[0003]
【発明が解決しようとする課題】上記、従来のプレーナ
型酵素電極は、絶縁性電極支持基板１と固定化酵素膜
（第一の高分子膜）３との間に、絶縁性保護膜６が介在
させてある。この絶縁性保護膜６は、電極支持基板１上
に感光性樹脂を塗布し、フォトマスクをかけて露光し、
現像、リンスすることにより電極支持基板１の接続部２
１ｃ、２２ｃ及び作用電極２１の感応部２１ａと参照電
極２２の感応部２２ａを除いて形成される。In the conventional planar type enzyme electrode described above, the insulating protective film 6 is provided between the insulating electrode supporting substrate 1 and the immobilized enzyme film (first polymer film) 3. Intervened. The insulating protective film 6 is formed by applying a photosensitive resin on the electrode supporting substrate 1 and exposing it with a photomask.
The connecting portion 2 of the electrode supporting substrate 1 by developing and rinsing
1c, 22c and the sensitive portion 21a of the working electrode 21 and the sensitive portion 22a of the reference electrode 22 are formed.
【０００４】ところで、図１０は、作用電極２１の感応
部２１ａと参照電極２２の感応部２２ａの面積比の応答
速度に対する影響を示す説明図である。図示例では、作
用電極の感応部２１ａを「１」としたときの参照電極の
感応部２２ａの面積比を横軸にとり、応答速度を縦軸に
とっている。この説明図より、作用電極の感応部２１ａ
と参照電極の感応部２２ａの面積比が、１：１の時は応
答速度が約４０秒と遅く、作用電極の感応部２１ａの面
積が「１」に対し参照電極の感応部２２ａの面積が
「２」以上である時、応答速度が約２０秒と速いことが
明らかとなっている。したがって、迅速な応答速度を得
るためには、作用電極感応部の面積に対し参照電極感応
部の面積比を「２」以上とする必要がある。そこで、従
来の酵素電極では、微細な感応部を定めるのに最適とさ
れるフォトリソグラフィー技術を採用している。By the way, FIG. 10 is an explanatory diagram showing the influence of the area ratio of the sensitive portion 21a of the working electrode 21 and the sensitive portion 22a of the reference electrode 22 on the response speed. In the illustrated example, the horizontal axis represents the area ratio of the sensitive portion 22a of the reference electrode when the sensitive portion 21a of the working electrode is "1", and the response speed is the vertical axis. From this illustration, the sensitive portion 21a of the working electrode
When the area ratio of the sensitive area 22a of the reference electrode is 1: 1, the response speed is as slow as about 40 seconds, and the area of the sensitive area 22a of the reference electrode is smaller than that of the sensitive area 21a of the working electrode. It is clear that when the value is "2" or more, the response speed is as fast as about 20 seconds. Therefore, in order to obtain a quick response speed, the area ratio of the reference electrode sensitive portion to the area of the working electrode sensitive portion needs to be "2" or more. Therefore, the conventional enzyme electrode employs a photolithography technique that is most suitable for defining a fine sensitive portion.
【０００５】ところが、このフォトリソグラフィ技術を
用いる場合は、工程が非常に煩雑で時間を要する。更
に、専用の製造装置が必要となる許かりでなく、フォト
リソグラフィー工程が歩留り劣化の一因をなし、コスト
ダウンの妨げとなる。また、従来の作用電極では、リー
ド部と感応部との幅が同一に設定してある（単位長さ当
たりのパターン幅が同一に設定してある）。従って、仮
に作用電極感応部を形成する際（感応部設定時）に僅か
な差異が生じた場合、露出するリード部により電極出力
に大きな影響を与えることとなる。また、リンスの不徹
底による作用電極感応部面への各種物質付着により、電
極出力の低下や電極間の特性のバラツキを増大させ、測
定精度に悪影響を及ぼす等の不利があった。However, when this photolithography technique is used, the process is very complicated and time-consuming. Further, a dedicated manufacturing apparatus is not required, and the photolithography process contributes to yield deterioration, which hinders cost reduction. Further, in the conventional working electrode, the lead portion and the sensitive portion have the same width (the pattern width per unit length is the same). Therefore, if a slight difference occurs when the working electrode sensitive portion is formed (when the sensitive portion is set), the exposed lead portion greatly affects the electrode output. Further, due to various substances adhering to the sensitive surface of the working electrode due to imperfect rinsing, there are disadvantages such as a decrease in electrode output and an increase in variation in characteristics between electrodes, which adversely affects measurement accuracy.
【０００６】この発明では、以上のような課題を解消さ
せ、感応部の形成にフォトリソグラフィー技術を使用せ
ず、専用の製造装置が不要であり、電極出力のバラツキ
が少なく、応答速度が速く、且つ測定精度の高い安価な
酵素電極を提供することを目的とする。In the present invention, the above problems are solved, the photolithography technique is not used for forming the sensitive portion, a dedicated manufacturing apparatus is not required, the variation in electrode output is small, and the response speed is fast, Moreover, it is an object to provide an inexpensive enzyme electrode with high measurement accuracy.
【０００７】[0007]
【課題を解決するための手段及び作用】この目的を達成
させるために、この発明の酵素電極では、次のような構
成としている。酵素電極は、絶縁性電極支持基板と、こ
の絶縁性電極支持基板上に形成された作用電極及び参照
電極とから成る下地電極と、この下地電極を含む絶縁性
電極支持基板上に形成された固定化酵素膜とから成る酵
素電極において、少なくとも作用電極のリード部パター
ン幅を感応部パターン幅より小さく設定したことを特徴
としている。To achieve this object, the enzyme electrode of the present invention has the following constitution. The enzyme electrode includes an insulating electrode supporting substrate, a base electrode composed of a working electrode and a reference electrode formed on the insulating electrode supporting substrate, and a fixed electrode formed on the insulating electrode supporting substrate including the base electrode. In the enzyme electrode composed of the modified enzyme membrane, at least the lead portion pattern width of the working electrode is set smaller than the sensitive portion pattern width.
【０００８】このような構成を有する酵素電極では、絶
縁性電極支持基板上に形成した下地電極（作用電極及び
参照電極）上に、直接、固定化酵素膜を形成している。
また、少なくとも作用電極（リード部の一端に接続部、
他端に感応部をもつ）は、リード部のパターン幅を感応
部のパターン幅より極端に小さく設定している。従っ
て、作用電極感応部の形成において、感応部面積（感応
部設定時における感応部対応窓孔面積）に誤差が生じた
としても、露出するリード部の面積が極めて小さく、電
極出力に大きな影響を与えることが防止できる。これに
より、従来のように感応部の形成に時間がかかり作業が
煩瑣で、専用の装置を必要とするフォトリソグラフィー
技術を使用する必要がない。従って、作用電極感応部面
への各種物質の付着がない。また、作用電極の感応部の
面積に対し、参照電極の感応部の面積比率を予め２倍以
上にパターニングしておくことで、極めて迅速な応答速
度を得ることができる。In the enzyme electrode having such a structure, the immobilized enzyme membrane is directly formed on the base electrode (working electrode and reference electrode) formed on the insulating electrode supporting substrate.
Also, at least the working electrode (the connecting portion at one end of the lead portion,
Has a sensitive portion at the other end), the pattern width of the lead portion is set extremely smaller than the pattern width of the sensitive portion. Therefore, even if an error occurs in the area of the sensitive portion (the area of the window corresponding to the sensitive portion when the sensitive portion is set) in forming the working electrode sensitive portion, the area of the exposed lead portion is extremely small and the electrode output is greatly affected. Can be given. As a result, it takes time and labor to form the sensitive portion, unlike the conventional case, and it is not necessary to use a photolithography technique that requires a dedicated device. Therefore, there is no adhesion of various substances on the surface of the working electrode sensitive section. Further, by patterning the area ratio of the sensitive portion of the reference electrode with respect to the area of the sensitive portion of the working electrode in advance to twice or more, an extremely quick response speed can be obtained.
【０００９】[0009]
【実施例】図１は、この発明に係る酵素電極の具体的な
一実施例を示す斜視図である。EXAMPLE FIG. 1 is a perspective view showing a specific example of the enzyme electrode according to the present invention.
【００１０】実施例の酵素電極は、血液中のグルコース
濃度測定用のもので、絶縁性電極支持基板１と、この電
極支持基板１上に形成された下地電極２と、絶縁性支持
基板１上に対し、下地電極２の接続部を除いて直接一体
に被覆形成された固定化酵素膜３とから成る。この酵素
電極は、下地電極２の感応部２１ａ、２２ａを露出させ
る窓孔５を備えた、且つ接続部２１ｃ、２２ｃを露出さ
せる長さの保持部材４に収納される。The enzyme electrode of the embodiment is for measuring glucose concentration in blood, and includes an insulating electrode supporting substrate 1, a base electrode 2 formed on the electrode supporting substrate 1, and an insulating supporting substrate 1. On the other hand, it is composed of the immobilized enzyme membrane 3 which is directly and integrally formed except the connecting portion of the base electrode 2. This enzyme electrode is housed in a holding member 4 having a window hole 5 for exposing the sensitive portions 21a, 22a of the base electrode 2 and having a length for exposing the connecting portions 21c, 22c.
【００１１】図３乃至図５は、実施例酵素電極の製造工
程を示す説明図である。絶縁性電極支持基板１は、例え
ば５０×５０ｍｍ、厚さ１００μのポリイミドフィルム
が用いられる。このプラスチックフィルム等の絶縁性電
極支持基板１上に、作用電極２１と参照電極２２が形成
され、作用電極２１と参照電極２２とで一対の下地電極
２が構成され、この下地電極２が多数絶縁性支持基板１
上に形成される。この下地電極２は、スパッタリング、
真空蒸着、イオンプレーティング等の手段を用いて、白
金を帯状に膜形成する。実施例では、下地電極２は２ｍ
ｍ×２０ｍｍ、厚さ１５００Åの膜形成が行われてい
る。この下地電極２の電極材料としては、白金に限定さ
れず、且つ形成手段もメッキや箔の粘着等で実施ても良
い。更に、電極支持基板１上には、接続部２１ｃ、２２
ｃを除いて酵素膜３が形成される。この酵素膜３は、図
５で示すように、電極２側の第一の高分子膜３１と、中
間層である固定化酵素層３２と、表面側の第二の高分子
膜３３を積層した三層構造とされる。実施例では、第一
の高分子膜３１及び第二の高分子膜３３は、ナフィオン
を採用している。ナフィオン（Ｎａｆｉｏｎ）は、アメ
リカ・デュポン車の商品名で、陽イオン交換性の高分
子、Ｐｏｌｙｐｅｒｆｌｕｏｒｏｓｕｌｆｕｒｉｃ ａ
ｃｉｄである。このナフィオンは、５％溶液（溶媒は低
級アルコール）が市販されており、膜形成が容易であ
る。本実施例では、ディップコーティングにより膜形成
している。この際、図４のように、電極支持基板１を半
分に切断してディップコーテティングする。また、酵素
膜３２は酵素液よりディップコーティングして膜形成さ
れる。酵素液は、０．１モルのリン酸緩衝液（ｐＨ７．
０）に、酵素グルコースオキシダーゼ（ＧＯＤ）１０
％、牛血清アルブミン７．５％及びグルタルアルデヒド
０．５％の濃度になるように調整して実施される。酵素
膜３装着後、一個の酵素電極に切り取って使用する（図
１参照）。3 to 5 are explanatory views showing the manufacturing process of the enzyme electrode of the embodiment. For the insulating electrode supporting substrate 1, for example, a polyimide film having a size of 50 × 50 mm and a thickness of 100 μ is used. A working electrode 21 and a reference electrode 22 are formed on an insulating electrode supporting substrate 1 such as a plastic film, and the working electrode 21 and the reference electrode 22 form a pair of base electrodes 2, and a large number of the base electrodes 2 are insulated. Support substrate 1
Formed on. The base electrode 2 is formed by sputtering,
A film of platinum is formed into a band using a means such as vacuum deposition or ion plating. In the embodiment, the base electrode 2 is 2 m
A film of m × 20 mm and a thickness of 1500Å is formed. The electrode material of the base electrode 2 is not limited to platinum, and the forming means may be plating or adhesion of foil. Further, on the electrode supporting substrate 1, the connecting portions 21c, 22
The enzyme membrane 3 is formed except for c. As shown in FIG. 5, the enzyme membrane 3 is formed by laminating a first polymer membrane 31 on the electrode 2 side, an immobilized enzyme layer 32 as an intermediate layer, and a second polymer membrane 33 on the surface side. It has a three-layer structure. In the embodiment, Nafion is used for the first polymer film 31 and the second polymer film 33. Nafion is a trade name of DuPont cars in the United States, and is a cation-exchangeable polymer, Polyfluorosulfurica.
cid. A 5% solution (solvent is lower alcohol) of this Nafion is commercially available, and it is easy to form a film. In this embodiment, the film is formed by dip coating. At this time, as shown in FIG. 4, the electrode supporting substrate 1 is cut in half and dip coated. The enzyme film 32 is formed by dip coating with an enzyme solution. The enzyme solution was 0.1 molar phosphate buffer solution (pH 7.
0) to the enzyme glucose oxidase (GOD) 10
%, Bovine serum albumin 7.5% and glutaraldehyde 0.5%. After mounting the enzyme membrane 3, it is cut into one enzyme electrode for use (see FIG. 1).
【００１２】図６乃至図９は、作用電極２１と参照電極
２２のパターン例を示している。図６に示す電極パター
ン例では、図１と同様に、作用電極２１及び参照電極２
２が共に、一本の細いリード部（リード線状）２１ｂ、
２２ｂを介して、それぞれ感応部２１ａ、２２ａと接続
部２１ｃ、２２ｃを導通させている。そして、参照電極
２２の感応部２２ａ面積を、作用電極２１の感応部２１
ａ面積の２倍に設定してある。図７に示す電極パターン
例は、作用電極２１のリード部２１ｂを一本のリード線
状とし、感応部２１ａと接続部２１ｃを導通させ、参照
電極２２については、感応部２２ａとリード２２ｂ、リ
ード部２２ｂと接続部２２ｃの境においてパターン幅の
変化がない例を示している。参照電極２２の場合は、リ
ード部２２ｂと感応部２２ａとのパターン幅に差異がな
くとも殆ど精度に影響を与えないため、これで充分であ
ることによる。また、図８に示す電極パターン例では、
作用電極２１のリード部２１ｂを感応部２１ａに接続す
る部分を幅狭に設定し、感応部２１ａと接続部２１ｃと
を導通している。参照電極については、感応部２２ａと
リード部２２ｂ、リード部２２ｂと接続部２２ｃの境に
おいてパターン幅の変化のない例を示している。更に、
図９の電極パターン例は、作用電極２１については、二
本の細いリード部（リード線状）２１ｂ、２１ｂで感応
部２１ａと接続部２１ｃを導通させ、参照電極について
は感応部２２ａとリード部２２ｂ、リード部２２ｂと接
続部２２ｃとの境においてパターン幅の変化のない例を
示している。図７乃至図９の例は、いずれも参照電極２
２の感応部２２ａが、作用電極２１の感応部２１ａの面
積の二倍以上となるように設定してある。6 to 9 show pattern examples of the working electrode 21 and the reference electrode 22. In the example of the electrode pattern shown in FIG. 6, the working electrode 21 and the reference electrode 2 are the same as in FIG.
2 is one thin lead portion (lead wire) 21b,
The sensitive portions 21a and 22a and the connecting portions 21c and 22c are electrically connected to each other via 22b. Then, the area of the sensitive portion 22 a of the reference electrode 22 is set to the sensitive portion 21 a of the working electrode 21.
The area is set to twice the area. In the example of the electrode pattern shown in FIG. 7, the lead portion 21b of the working electrode 21 is formed into a single lead wire, and the sensitive portion 21a and the connecting portion 21c are electrically connected. For the reference electrode 22, the sensitive portion 22a, the lead 22b, and the lead An example is shown in which the pattern width does not change at the boundary between the portion 22b and the connecting portion 22c. In the case of the reference electrode 22, the accuracy is hardly affected even if there is no difference in the pattern width between the lead portion 22b and the sensitive portion 22a, and this is sufficient. In addition, in the electrode pattern example shown in FIG.
The portion connecting the lead portion 21b of the working electrode 21 to the sensitive portion 21a is set to be narrow, and the sensitive portion 21a and the connecting portion 21c are electrically connected. Regarding the reference electrode, an example in which the pattern width does not change at the boundary between the sensitive portion 22a and the lead portion 22b and between the lead portion 22b and the connection portion 22c is shown. Furthermore,
In the example of the electrode pattern of FIG. 9, for the working electrode 21, two thin lead portions (lead wire shapes) 21b, 21b connect the sensitive portion 21a and the connecting portion 21c to each other, and for the reference electrode, the sensitive portion 22a and the lead portion. 22b shows an example in which the pattern width does not change at the boundary between the lead portion 22b and the connecting portion 22c. In each of the examples of FIGS. 7 to 9, the reference electrode 2 is used.
The second sensitive portion 22a is set to be twice the area of the sensitive portion 21a of the working electrode 21 or more.
【００１３】この酵素電極は、図１及び図２で示すよう
に、各感応部２１ａ、２２ａが露出した状態で保持部材
４に封入される。As shown in FIGS. 1 and 2, the enzyme electrode is enclosed in the holding member 4 with the sensitive portions 21a and 22a exposed.
【００１４】このような構成を有する酵素電極では、絶
縁性電極支持基板１上に形成した下地電極（作用電極２
１及び参照電極２２）２上に、直接、固定化酵素膜３を
形成している。従って、作用電極の感応部２１ａ面と酵
素層３がより密着し迅速な応答速度が得られる。また、
少なくとも作用電極２１は、リード部２１ｂのパターン
幅を感応部２１ａのパターン幅より極端に小さく設定し
ている。従って、作用電極感応部２１ａの形成におい
て、感応部２１ａに対応する開口部面積（保持部材４の
開口窓孔５面積）に誤差が生じたとしても、露出するリ
ード部２１ｂの面積が極めて小さく、電極出力に大きな
影響を与えることを防止できる。これにより、従来のよ
うに感応部２１ａの形成に時間がかかり作業が煩瑣で、
専用の装置を必要とするフォトリソグラフィー技術を使
用する必要がない。従って、作用電極感応部２１ａ面へ
の各種物質の付着がない。また、作用電極２１の感応部
２１ａの面積に対し、参照電極２２の感応部２２ａの面
積比率を予め２倍以上にパターニングしておくことで、
極めて迅速な応答速度を得ることができる。In the enzyme electrode having such a structure, the base electrode (working electrode 2) formed on the insulating electrode supporting substrate 1 is used.
Immobilized enzyme membrane 3 is directly formed on 1 and reference electrode 22) 2. Therefore, the surface of the sensitive portion 21a of the working electrode and the enzyme layer 3 are more closely attached, and a quick response speed can be obtained. Also,
At least the working electrode 21 sets the pattern width of the lead portion 21b to be extremely smaller than the pattern width of the sensitive portion 21a. Therefore, in forming the working electrode sensitive portion 21a, even if an error occurs in the opening area corresponding to the sensitive portion 21a (the area of the opening window hole 5 of the holding member 4), the exposed area of the lead portion 21b is extremely small, It is possible to prevent a great influence on the electrode output. As a result, it takes time and labor to form the sensitive portion 21a as in the conventional case.
There is no need to use photolithography techniques that require specialized equipment. Therefore, various substances are not attached to the surface of the working electrode sensitive portion 21a. Further, by patterning the area ratio of the sensitive portion 22a of the reference electrode 22 with respect to the area of the sensitive portion 21a of the working electrode 21 in advance to twice or more,
An extremely quick response speed can be obtained.
【００１５】[0015]
【発明の効果】この発明では、以上のように、絶縁性電
極支持基板上に形成される膜状の下地電極の少なくとも
作用電極のリード部幅を感応部の幅よりも小さく設定
し、この下地電極の上面に接続部を除いて直接固定化酵
素膜を形成することとしたから、フォトリソグラフィー
工程が省略でき、製造時間の短縮は勿論、専用の製造装
置が不要であり、大幅なコストダウンを実現できる。ま
た、作用電極感応部面への各種物質の付着がなく、電極
出力の低下や電極間の特性のバラツキがなくなり、測定
精度を向上させ得る。更に、作用電極感応部面と酵素層
がより密着するため、迅速な応答速度が得られる。ま
た、作用電極のリード部幅は感応部幅に比較して小さい
ため、仮に保持部材の開口部にリード部が露出しても、
電極出力に対するリード部の与える影響は非常に小さく
無視できる。しかも、作用電極の感応部の面積に対し参
照電極の面積比率を二倍以上としたから、極めて迅速な
応答速度を得られる許かりでなく、この面積比を得るた
めに複数の参照電極を採用しても良く、適用範囲の広い
測定系が設定できる等、発明目的を達成した優れた効果
を有する。As described above, according to the present invention, at least the lead portion width of the working electrode of the film-shaped base electrode formed on the insulating electrode supporting substrate is set to be smaller than the width of the sensitive portion. Since the immobilized enzyme membrane was directly formed on the upper surface of the electrode except for the connection part, the photolithography process can be omitted, the manufacturing time can be shortened, and a dedicated manufacturing device is not required, resulting in a significant cost reduction. realizable. In addition, various substances do not adhere to the surface of the working electrode sensitive portion, the electrode output is not reduced and the characteristics of the electrodes are not varied, and the measurement accuracy can be improved. Furthermore, since the surface of the sensitive part of the working electrode and the enzyme layer are in close contact with each other, a quick response speed can be obtained. Further, since the width of the lead portion of the working electrode is smaller than the width of the sensitive portion, even if the lead portion is exposed in the opening of the holding member,
The influence of the lead portion on the electrode output is very small and can be ignored. Moreover, because the area ratio of the reference electrode to the area of the sensitive part of the working electrode is more than doubled, it is not possible to obtain an extremely quick response speed, and multiple reference electrodes are used to obtain this area ratio. However, it is possible to set a measuring system having a wide range of application, and it has an excellent effect of achieving the object of the invention.
【図１】実施例酵素電極を示す斜視図である。FIG. 1 is a perspective view showing an example enzyme electrode.
【図２】実施例酵素電極を示す断面図である。FIG. 2 is a cross-sectional view showing an example enzyme electrode.
【図３】実施例酵素電極の製造工程を示す説明図であ
る。FIG. 3 is an explanatory view showing a manufacturing process of the enzyme electrode of the example.
【図４】実施例酵素電極の製造工程を示す説明図であ
る。FIG. 4 is an explanatory view showing a manufacturing process of the enzyme electrode of the example.
【図５】実施例酵素電極の製造工程を示す断面図であ
る。FIG. 5 is a cross-sectional view showing the manufacturing process of the enzyme electrode of the example.
【図６】実施例酵素電極の下地電極のパターン例を示す
説明図である。FIG. 6 is an explanatory diagram showing an example of a pattern of a base electrode of the enzyme electrode of Example.
【図７】実施例酵素電極の下地電極の他のパターン例を
示す説明図である。FIG. 7 is an explanatory view showing another pattern example of the base electrode of the example enzyme electrode.
【図８】実施例酵素電極の下地電極の更に他のパターン
例を示す説明図である。FIG. 8 is an explanatory view showing still another pattern example of the base electrode of the example enzyme electrode.
【図９】実施例酵素電極の下地電極のパターン例を示す
説明図である。FIG. 9 is an explanatory diagram showing a pattern example of a base electrode of an example enzyme electrode.
【図１０】感応部の面積比による応答速度に対する影響
を示す説明図である。FIG. 10 is an explanatory diagram showing the influence of the area ratio of the sensitive section on the response speed.
【図１１】従来の酵素電極を示す斜視図である。FIG. 11 is a perspective view showing a conventional enzyme electrode.
【図１２】従来の酵素電極を示す断面図である。FIG. 12 is a cross-sectional view showing a conventional enzyme electrode.
１ 絶縁性電極支持基板 ２ 下地電極 ３ 固定化酵素膜 ２１ 作用電極 ２１ ａ感応部 ２１ ｂリード部 1 Insulating Electrode Support Substrate 2 Base Electrode 3 Immobilized Enzyme Membrane 21 Working Electrode 21 a Sensitive Part 21 b Lead Part
───────────────────────────────────────────────────── フロントページの続き (72)発明者 遠藤 英樹 京都市下京区中堂寺南町17番地 サイエン スセンタービル 株式会社オムロンライフ サイエンス研究所内 (72)発明者 滝沢 耕一 京都市下京区中堂寺南町17番地 サイエン スセンタービル 株式会社オムロンライフ サイエンス研究所内 ─────────────────────────────────────────────────── ─── Continuation of the front page (72) Inventor Hideki Endo 17 Nakadoji-Minami-cho, Shimogyo-ku, Kyoto Science Center Building Co., Ltd. inside the Omron Life Science Research Institute (72) Inventor Koichi Takizawa 17-City, Minami-cho, Shimogyo-ku, Kyoto Saien Center Center Omron Life Science Research Institute
Claims (1)
持基板上に膜状に形成された作用電極及び参照電極とか
ら成る下地電極と、この下地電極を含む絶縁性電極支持
基板上に形成された固定化酵素膜とから成る酵素電極に
おいて、 少なくとも作用電極のリード部パターン幅を感応部パタ
ーン幅より小さく設定したことを特徴とする酵素電極。1. A base electrode comprising an insulating electrode supporting substrate, a working electrode and a reference electrode formed in a film on the insulating electrode supporting substrate, and an insulating electrode supporting substrate including the base electrode. An enzyme electrode comprising a formed immobilized enzyme membrane, wherein at least the lead portion pattern width of the working electrode is set smaller than the sensitive portion pattern width.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP3238177A JPH0572172A (en) | 1991-09-18 | 1991-09-18 | Enzyme electrode |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP3238177A JPH0572172A (en) | 1991-09-18 | 1991-09-18 | Enzyme electrode |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH0572172A true JPH0572172A (en) | 1993-03-23 |
Family
ID=17026322
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP3238177A Pending JPH0572172A (en) | 1991-09-18 | 1991-09-18 | Enzyme electrode |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH0572172A (en) |
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH07159366A (en) * | 1993-12-07 | 1995-06-23 | Omron Corp | Portable measuring instrument |
| WO2001036953A1 (en) * | 1999-11-15 | 2001-05-25 | Matsushita Electric Industrial Co., Ltd. | Biosensor, method of forming thin-film electrode, and method and apparatus for quantitative determination |
| US7294246B2 (en) * | 2003-11-06 | 2007-11-13 | 3M Innovative Properties Company | Electrode for electrochemical sensors |
| US8529742B2 (en) | 2010-02-24 | 2013-09-10 | Matthew K. Musho | Electrochemical sensor with controlled variation of working electrode |
| US9046480B2 (en) | 2006-10-05 | 2015-06-02 | Lifescan Scotland Limited | Method for determining hematocrit corrected analyte concentrations |
| US10041901B2 (en) | 2013-03-15 | 2018-08-07 | Roche Diabetes Care, Inc. | Electrode configuration for a biosensor |
-
1991
- 1991-09-18 JP JP3238177A patent/JPH0572172A/en active Pending
Cited By (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH07159366A (en) * | 1993-12-07 | 1995-06-23 | Omron Corp | Portable measuring instrument |
| WO2001036953A1 (en) * | 1999-11-15 | 2001-05-25 | Matsushita Electric Industrial Co., Ltd. | Biosensor, method of forming thin-film electrode, and method and apparatus for quantitative determination |
| US6875327B1 (en) | 1999-11-15 | 2005-04-05 | Matsushita Electric Industrial Co., Ltd. | Biosensor, method of forming thin-film electrode, and method and apparatus for quantitative determination |
| US7998325B2 (en) | 1999-11-15 | 2011-08-16 | Panasonic Corporation | Biosensor, thin film electrode forming method, quantification apparatus, and quantification method |
| US8025780B2 (en) | 1999-11-15 | 2011-09-27 | Panasonic Corporation | Biosensor, thin film electrode forming method, quantification apparatus, and quantification method |
| US8142629B2 (en) | 1999-11-15 | 2012-03-27 | Panasonic Corporation | Biosensor, thin film electrode forming method, quantification apparatus, and quantification method |
| US8349157B2 (en) | 1999-11-15 | 2013-01-08 | Panasonic Corporation | Biosensor, thin film electrode forming method, quantification apparatus, and quantification method |
| US7294246B2 (en) * | 2003-11-06 | 2007-11-13 | 3M Innovative Properties Company | Electrode for electrochemical sensors |
| US9046480B2 (en) | 2006-10-05 | 2015-06-02 | Lifescan Scotland Limited | Method for determining hematocrit corrected analyte concentrations |
| US8529742B2 (en) | 2010-02-24 | 2013-09-10 | Matthew K. Musho | Electrochemical sensor with controlled variation of working electrode |
| US10041901B2 (en) | 2013-03-15 | 2018-08-07 | Roche Diabetes Care, Inc. | Electrode configuration for a biosensor |
| US10996184B2 (en) | 2013-03-15 | 2021-05-04 | Roche Diabetes Care, Inc. | Electrode configuration for a biosensor |
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