JPH0340335B2 - - Google Patents
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- Publication number
- JPH0340335B2 JPH0340335B2 JP3979882A JP3979882A JPH0340335B2 JP H0340335 B2 JPH0340335 B2 JP H0340335B2 JP 3979882 A JP3979882 A JP 3979882A JP 3979882 A JP3979882 A JP 3979882A JP H0340335 B2 JPH0340335 B2 JP H0340335B2
- Authority
- JP
- Japan
- Prior art keywords
- electrode
- liquid
- measurement cell
- enzyme reaction
- enzyme
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
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- 238000005259 measurement Methods 0.000 claims description 40
- 239000007788 liquid Substances 0.000 claims description 31
- 238000006911 enzymatic reaction Methods 0.000 claims description 20
- 239000000126 substance Substances 0.000 claims description 15
- 108090000790 Enzymes Proteins 0.000 claims description 14
- 102000004190 Enzymes Human genes 0.000 claims description 14
- 239000005515 coenzyme Substances 0.000 claims description 3
- 210000004027 cell Anatomy 0.000 description 25
- 229940088598 enzyme Drugs 0.000 description 13
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 description 12
- 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 7
- 238000001514 detection method Methods 0.000 description 7
- 239000008103 glucose Substances 0.000 description 7
- 239000012528 membrane Substances 0.000 description 6
- 229910052697 platinum Inorganic materials 0.000 description 6
- 230000000694 effects Effects 0.000 description 5
- 239000000758 substrate Substances 0.000 description 5
- 108010015776 Glucose oxidase Proteins 0.000 description 4
- 239000004366 Glucose oxidase Substances 0.000 description 4
- 239000007864 aqueous solution Substances 0.000 description 4
- 229940116332 glucose oxidase Drugs 0.000 description 4
- 235000019420 glucose oxidase Nutrition 0.000 description 4
- 230000007423 decrease Effects 0.000 description 3
- 230000003647 oxidation Effects 0.000 description 3
- 238000007254 oxidation reaction Methods 0.000 description 3
- 102000007698 Alcohol dehydrogenase Human genes 0.000 description 2
- 108010021809 Alcohol dehydrogenase Proteins 0.000 description 2
- LFQSCWFLJHTTHZ-UHFFFAOYSA-N Ethanol Chemical compound CCO LFQSCWFLJHTTHZ-UHFFFAOYSA-N 0.000 description 2
- BAWFJGJZGIEFAR-NNYOXOHSSA-N NAD zwitterion Chemical compound NC(=O)C1=CC=C[N+]([C@H]2[C@@H]([C@H](O)[C@@H](COP([O-])(=O)OP(O)(=O)OC[C@@H]3[C@H]([C@@H](O)[C@@H](O3)N3C4=NC=NC(N)=C4N=C3)O)O2)O)=C1 BAWFJGJZGIEFAR-NNYOXOHSSA-N 0.000 description 2
- 229910021607 Silver chloride Inorganic materials 0.000 description 2
- 239000011148 porous material Substances 0.000 description 2
- 230000035945 sensitivity Effects 0.000 description 2
- HKZLPVFGJNLROG-UHFFFAOYSA-M silver monochloride Chemical compound [Cl-].[Ag+] HKZLPVFGJNLROG-UHFFFAOYSA-M 0.000 description 2
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 1
- PHOQVHQSTUBQQK-SQOUGZDYSA-N D-glucono-1,5-lactone Chemical compound OC[C@H]1OC(=O)[C@H](O)[C@@H](O)[C@@H]1O PHOQVHQSTUBQQK-SQOUGZDYSA-N 0.000 description 1
- SXRSQZLOMIGNAQ-UHFFFAOYSA-N Glutaraldehyde Chemical compound O=CCCCC=O SXRSQZLOMIGNAQ-UHFFFAOYSA-N 0.000 description 1
- 239000008280 blood Substances 0.000 description 1
- 210000004369 blood Anatomy 0.000 description 1
- 230000003197 catalytic effect Effects 0.000 description 1
- 210000005056 cell body Anatomy 0.000 description 1
- 239000000919 ceramic Substances 0.000 description 1
- 238000010276 construction Methods 0.000 description 1
- 238000000835 electrochemical detection Methods 0.000 description 1
- 238000003487 electrochemical reaction Methods 0.000 description 1
- 235000012209 glucono delta-lactone Nutrition 0.000 description 1
- 229960003681 gluconolactone Drugs 0.000 description 1
- 239000010439 graphite Substances 0.000 description 1
- 229910002804 graphite Inorganic materials 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 238000000465 moulding Methods 0.000 description 1
- 229950006238 nadide Drugs 0.000 description 1
- 229940101270 nicotinamide adenine dinucleotide (nad) Drugs 0.000 description 1
- 229930027945 nicotinamide-adenine dinucleotide Natural products 0.000 description 1
- BOPGDPNILDQYTO-NNYOXOHSSA-N nicotinamide-adenine dinucleotide Chemical compound C1=CCC(C(=O)N)=CN1[C@H]1[C@H](O)[C@H](O)[C@@H](COP(O)(=O)OP(O)(=O)OC[C@@H]2[C@H]([C@@H](O)[C@@H](O2)N2C3=NC=NC(N)=C3N=C2)O)O1 BOPGDPNILDQYTO-NNYOXOHSSA-N 0.000 description 1
- 238000012856 packing Methods 0.000 description 1
- 239000008363 phosphate buffer Substances 0.000 description 1
- 239000008055 phosphate buffer solution Substances 0.000 description 1
- 229920000515 polycarbonate Polymers 0.000 description 1
- 239000004417 polycarbonate Substances 0.000 description 1
- 239000000843 powder Substances 0.000 description 1
- 238000001179 sorption measurement Methods 0.000 description 1
Landscapes
- Apparatus Associated With Microorganisms And Enzymes (AREA)
Description
【発明の詳細な説明】
本発明は、酵素あるいは補酵素を固定化してな
る酵素電極を備え、基質の濃度あるいは酵素活性
を迅速かつ簡便に測定することのできる連続送液
式の酵素反応測定セルに関する。DETAILED DESCRIPTION OF THE INVENTION The present invention provides a continuous liquid-feeding enzyme reaction measurement cell that is equipped with an enzyme electrode on which an enzyme or coenzyme is immobilized and that can quickly and easily measure substrate concentration or enzyme activity. Regarding.
酵素の有する特異的触媒作用の工業的利用の一
例として、酵素反応系と電気化学反応系を結びつ
けたいわゆる酵素電極により、基質の濃度や酵素
活性を測定することが試みられている。例えば、
酵素反応にともなつて生成、増減するH2O2，
NH3，CO2，O2などの物質について、各々の物
質に対応した特定物質検出電極を用いて電気化学
的に検出し、基質濃度や酵素活性を測定すること
ができる。 As an example of industrial use of the specific catalytic action of enzymes, attempts have been made to measure substrate concentration and enzyme activity using a so-called enzyme electrode that combines an enzyme reaction system and an electrochemical reaction system. for example,
H 2 O 2 is produced, increases and decreases as a result of enzymatic reactions,
Substances such as NH 3 , CO 2 , and O 2 can be electrochemically detected using specific substance detection electrodes corresponding to each substance, and the substrate concentration and enzyme activity can be measured.
その一例として、グルコース濃度の測定につい
て以下の(1)，(2)式に示す。すなわちグルコースオ
キシダーゼの作用により基質であるグルコースが
酸化されH2O2が生成する（(1)式）。次にこの
H2O2を(2)式に示す様に白金電極を用いて酸化し、
この時得られる酸化電流値から試料中のグルコー
ス濃度を知ることができる。あるいはまた、
グルコース＋O2グルコースオキシターゼ
――――――――――――――→
グルコノラクトン＋H2O2 …(1)
H2O2→2H+＋2e＋O2 …(2)
１式におけるO2の減少量を酵素濃度検出用電
極で測定してもよい。 As an example, the measurement of glucose concentration is shown in the following equations (1) and (2). That is, the substrate glucose is oxidized by the action of glucose oxidase to generate H 2 O 2 (formula (1)). Then this
Oxidize H 2 O 2 using a platinum electrode as shown in equation (2),
The glucose concentration in the sample can be determined from the oxidation current value obtained at this time. Alternatively, glucose + O 2 glucose oxidase ――――――――――――→ Gluconolactone + H 2 O 2 …(1) H 2 O 2 →2H + +2e+O 2 …(2) In formula 1 The amount of decrease in O 2 may be measured using an enzyme concentration detection electrode.
この様な測定を実用的な方法で行うためには、
酵素の繰り返し使用を可能にするために固定化
し、さらに特定物質検出用の電極と一体化して適
当な酵素反応測定セルに装着する必要がある。測
定セルの方式としては回分式と連続送液式がある
が、臨床分析における血糖分析の様に多数の試料
について迅速、簡便な測定が要求される場合に
は、連続送液式のものが好都合である。 In order to carry out such measurements in a practical manner,
In order to enable repeated use of the enzyme, it is necessary to immobilize it, integrate it with an electrode for detecting a specific substance, and attach it to a suitable enzyme reaction measurement cell. There are two types of measurement cells: batch type and continuous liquid feeding type, but continuous liquid feeding type is preferable when quick and easy measurement of a large number of samples is required, such as blood sugar analysis in clinical analysis. It is.
従来、連続送液式の酵素反応測定セルとして
は、第１図および第２図に概略を示す構造のもの
が考案されている。第１図に示すセル構造につい
て説明すると、セル本体１の内部に管状の流路２
を設け、その液入口側に管３を、液出口側に管４
をそれぞれ接続し、矢印の方向に連続的に送液す
る（以下、同様に矢印で送液方向を示す）。酵素
反応に対応した電気化学的な検出は、一例として
示したが本体の流路２の内壁面に設けた特定物質
検出用電極（作用極）５、参照極６、対極７の電
極系を用いて行うことができる。この場合、円滑
な流れを得るためには、各電極の構造を円筒状と
する必要がある。しかし、この様な構造とするた
めには、実用的見地からは、工作上の難しさや、
膜に固定化した酵素の場合には、これを装着する
のが大変困難であるという欠点を有する。 BACKGROUND ART Conventionally, a continuous liquid feeding type enzyme reaction measurement cell has been devised having a structure schematically shown in FIGS. 1 and 2. To explain the cell structure shown in FIG. 1, there is a tubular flow path 2 inside the cell body 1.
A pipe 3 is provided on the liquid inlet side and a pipe 4 is provided on the liquid outlet side.
are connected to each other, and the liquid is continuously fed in the direction of the arrow (hereinafter, the direction of liquid feeding is similarly indicated by the arrow). Electrochemical detection corresponding to the enzyme reaction is shown as an example, but an electrode system including a specific substance detection electrode (working electrode) 5, a reference electrode 6, and a counter electrode 7 provided on the inner wall surface of the channel 2 of the main body is used. It can be done by In this case, in order to obtain smooth flow, each electrode must have a cylindrical structure. However, from a practical point of view, creating such a structure requires a lot of difficulty in construction and
Enzymes immobilized on membranes have the disadvantage that they are very difficult to attach.
第２図に示した構造は上記の欠点を改良したも
のであり、本体１の液流入口側に接続された管３
から本体内の管状流路２を通つて測定室８に流入
し、流路２′から管４へと流出する。この構造に
おいては、特定物質検出用電極５として、例えば
先述のグルコースの場合の様にH2O2を検出する
場合には、円板状の白金電極上にグルコースオキ
シダーゼを固定化した膜を重ね合わせて装着し、
使用することは容易である。またその着脱も構造
上容易である。 The structure shown in FIG. 2 improves the above-mentioned drawbacks, and the structure shown in FIG.
It flows into the measuring chamber 8 through the tubular channel 2 in the main body, and flows out into the tube 4 through the channel 2'. In this structure, when detecting H 2 O 2 as the specific substance detection electrode 5, for example in the case of glucose mentioned above, a membrane on which glucose oxidase is immobilized is stacked on a disc-shaped platinum electrode. Wear it together,
It is easy to use. Moreover, its structure makes it easy to attach and detach.
しかし、第２図に示した構造においては、測定
室８を必要とするため、第１図に示した構造の場
合の様な円滑な液の流れは得られない。すなわ
ち、連続的な液流に試料を注入し、これを測定室
に流入させ場合、試料を含む液は測定室に滞まり
易くなるため、測定室から完全に流出するまでに
長時間を要することになる。すなわち、電極の応
答にテーリングが生ずる。このことは、多数の試
料について連続的にかつ迅速に測定を行う場合に
は大変不利なことである。 However, in the structure shown in FIG. 2, since the measurement chamber 8 is required, smooth liquid flow cannot be obtained as in the case of the structure shown in FIG. In other words, when a sample is injected into a continuous liquid stream and allowed to flow into the measurement chamber, the liquid containing the sample tends to stay in the measurement chamber, so it takes a long time for it to completely flow out of the measurement chamber. become. That is, tailing occurs in the response of the electrode. This is very disadvantageous when measuring a large number of samples continuously and rapidly.
この欠点を改良するために、測定室の形状を半
管状とするなども考えられるが、これは、特定物
質検出用電極の有効面積（被検液に接する面の面
積）の減少となり、応答感度の低下を招くことに
なり、また第１図に示した構造の場合と同様な円
滑な流れは得られない。 In order to improve this drawback, it is possible to make the measurement chamber semi-tubular, but this will reduce the effective area (area of the surface in contact with the sample liquid) of the electrode for detecting a specific substance, resulting in a decrease in response sensitivity. In addition, the same smooth flow as in the structure shown in FIG. 1 cannot be obtained.
本発明者は、以上のような従来の不都合を解消
し、優れた特性を有する連続送液式の酵素反応測
定セルを提供するものである。本発明の酵素反応
測定セルの特徴は、酵素又は補酵素の少なくとも
一方を固定化した特定物質検出用の電極を備え、
この電極の被検液と接する側の電極面の中心部近
傍に液流入口を設け、かつ電極面のすべての外周
方向に液流出口を設けたことである。 The present inventor solves the above-mentioned conventional disadvantages and provides a continuous liquid feeding type enzyme reaction measurement cell having excellent characteristics. The enzyme reaction measurement cell of the present invention is characterized by comprising an electrode for detecting a specific substance on which at least one of an enzyme or a coenzyme is immobilized,
A liquid inlet is provided near the center of the electrode surface on the side of the electrode that is in contact with the test liquid, and a liquid outlet is provided along the entire outer periphery of the electrode surface.
第３図に本発明のセルの実施例を断面模式図で
示す。被検液は矢印で示すごとく、管３より本体
部１１に設けた管状の流路２を通り測定室８に流
れ込む。すなわち、円板状の特定物質検出用電極
５の中心部近傍に液が流入し、続いて電極面の中
心部より外周方向へ流れ、この後、本体部１１と
もう一方の本体部１３との間隙からなる円錐状の
液流出路１４を通り、最終的に管４から流出す
る。第４図に測定室８の付近の構造について断面
斜視図で示す。上記に説明した様に、液は流路２
から被検液と接する電極面５′の中心部へ流入し、
この後、電極面上をその外周方向へ拡がり流出路
１４を通つて流出する。 FIG. 3 shows a schematic cross-sectional view of an embodiment of the cell of the present invention. The test liquid flows into the measurement chamber 8 from the tube 3 through the tubular flow path 2 provided in the main body 11, as shown by the arrow. That is, the liquid flows into the vicinity of the center of the disk-shaped specific substance detection electrode 5, then flows from the center of the electrode surface toward the outer circumference, and then flows between the main body 11 and the other main body 13. The liquid passes through a conical outflow path 14 consisting of a gap and finally flows out from the pipe 4. FIG. 4 shows a cross-sectional perspective view of the structure around the measurement chamber 8. As explained above, the liquid flows through the flow path 2.
Flows into the center of the electrode surface 5' in contact with the test liquid,
Thereafter, it spreads on the electrode surface in the direction of its outer periphery and flows out through the outflow path 14.
この様に、特定物質検出用の電極の中心部近傍
に液流入口を設け、流出口を電極面のすべての外
周方向に設けることにより、円滑な流れを得るこ
とができる。これにより、本発明の酵素反応測定
セルにおいては、測定室に流入した試料は速やか
に流出するため、迅速な応答が得られかつ先述の
様なテーリングは起こらない。 In this way, a smooth flow can be obtained by providing the liquid inlet near the center of the electrode for detecting a specific substance and providing the outlet in the entire outer circumferential direction of the electrode surface. As a result, in the enzyme reaction measurement cell of the present invention, the sample that flows into the measurement chamber quickly flows out, so that a rapid response can be obtained and the above-mentioned tailing does not occur.
本発明について、さらに以下に述べる実施例で
説明する。 The present invention will be further explained in the following examples.
実施例 １
特定物質検出用電極（作用極）として次のもの
を作製した。電極担体としてポリカーボネート多
孔質膜（膜厚10μm，孔径2000Å）を用い、この
膜の片側面に白金をスパツタリングしてH2O2検
出用の作用極を形成した。次にこの膜に、グルコ
ースオキシダーゼ水溶液（100mg／ml）を20μ
／cm2の割合いで展開した後、乾燥し、グルタル
アルデヒドを用いて酵素相互間を架橋し、膜面上
および孔内に固定化した。Example 1 The following electrode for detecting a specific substance (working electrode) was prepared. A polycarbonate porous membrane (film thickness 10 μm, pore diameter 2000 Å) was used as an electrode carrier, and platinum was sputtered on one side of this membrane to form a working electrode for H 2 O 2 detection. Next, 20μ of glucose oxidase aqueous solution (100mg/ml) was applied to this membrane.
/ cm2 , dried, and the enzymes were cross-linked using glutaraldehyde to be immobilized on the membrane surface and in the pores.
上記で得られた電極を第３図に示す酵素反応測
定セルに組み込んだ。この場合、上記電極５の白
金スパツタ面は白金板からなるリード９に接し、
内径５mmのパツキン１０を介して本体部１３に装
置されている。また本体部１１と１３はゴムリン
グ１２を介在させることにより密閉された測定セ
ル内部の液流路を構成している。電極系は、白金
対極７、および測定室８との境界部に多孔質セラ
ミツク層を有するAg／AgCl参照極６からなる。
流路２の内径は１mm、測定室は直径５mm、高さ
0.8mmの円柱状となる様に構成した。 The electrode obtained above was incorporated into the enzyme reaction measurement cell shown in FIG. In this case, the platinum spattered surface of the electrode 5 is in contact with the lead 9 made of a platinum plate,
The device is attached to the main body 13 via a packing 10 having an inner diameter of 5 mm. Furthermore, the main bodies 11 and 13 constitute a liquid flow path inside the measurement cell which is sealed with a rubber ring 12 interposed therebetween. The electrode system consists of a platinum counter electrode 7 and an Ag/AgCl reference electrode 6 with a porous ceramic layer at the interface with the measurement chamber 8.
The inner diameter of channel 2 is 1 mm, and the measurement chamber has a diameter of 5 mm and a height.
It was configured to have a cylindrical shape of 0.8 mm.
測定は、作用極の電位を＋0.60V vsAg／AgCl
に設定しておき、別に外部に備えた送液ポンプと
試料注入装置により、グルコース水溶液（５×
10-3モル／）の一定量をPH5.6のリン酸緩衝液
の流れに注入し、管３より測定セル内に導入し
た。この様にして得られた電極の応答について、
応答電流と時間の関係を第５図のＡに実線で示
す。 For measurement, set the potential of the working electrode to +0.60V vsAg/AgCl
A glucose aqueous solution (5×
A fixed amount of 10 -3 mol/) was injected into a flow of phosphate buffer at pH 5.6 and introduced into the measuring cell through tube 3. Regarding the response of the electrode obtained in this way,
The relationship between response current and time is shown by a solid line in A of FIG.
比較のために、従来の測定セルとして第２図に
示す構造のものを用い、これに上記と全く同様の
作用極を装着してグルコースに対する応答を測定
した。第２図に示すところの流路２の内径、測定
室の形状をはじめとして測定条件は上記と全く同
様にした。得られた電極の応答を第５図のＢに破
線で示す。図より明らかなごとく、本発明の酵素
反応測定セルによる応答ＡにおいてはＢと比較し
てH2O2の酸化電流の立上りが速やかであり、テ
ーリングもほとんどなく約10秒後にもとの電流値
のレベルとなるなど、高感度で迅速な応答を有す
ることが判かる。これは、すでに述べた様に、本
発明の酵素反応測定セルにおいては、測定室にお
ける液の流出が円滑であることによるものであ
る。 For comparison, a conventional measurement cell having the structure shown in FIG. 2 was used, and a working electrode similar to that described above was attached to the cell to measure the response to glucose. The measurement conditions, including the inner diameter of the flow path 2 and the shape of the measurement chamber shown in FIG. 2, were exactly the same as above. The response of the electrode obtained is shown by the broken line in FIG. 5B. As is clear from the figure, in response A by the enzyme reaction measurement cell of the present invention, the rise of the H 2 O 2 oxidation current is faster than in response B, and there is almost no tailing, and the current value returns to the original value after about 10 seconds. It can be seen that it has a high sensitivity and quick response. This is because, as already mentioned, in the enzyme reaction measurement cell of the present invention, the liquid flows out smoothly in the measurement chamber.
実施例 ２
アルコール脱水素酵素の活性測定を行うための
特定物質検出用の電極として以下のものを作製し
た。まず導電性担体として、高純度の黒鉛を主成
分とする粉末を成形して直径10mm、厚さ約１mmの
デイスク状の電極を作製し、この平面上に、補酵
素としてニコチンアミドアデニンジヌクレオチド
（NAD）の水溶液（200mg／ml）を15μ展開、
乾燥して吸着固定し、次に洗浄して余分のNAD
を除去した。この電極を実施例１と同様にして、
第３図、第２図に示す構造の酵素反応測定セルに
装着し、送液ポンプで0.01モル／のエタノール
を含むPH7.0のリン酸緩衝液を測定セルに流し、
この流れに試料としてアルコール脱水素酵素水溶
液を注入し、電極の応答を測定した。実施例１の
結果と同様に、NADHの酸化電流に基づく応答
は本発明の測定セルにおいては従来の測定セルに
比べて迅速かつ高感度であつた。Example 2 The following electrode was prepared for detecting a specific substance for measuring the activity of alcohol dehydrogenase. First, a disc-shaped electrode with a diameter of 10 mm and a thickness of about 1 mm was prepared by molding powder mainly composed of high-purity graphite as a conductive carrier, and on this flat surface nicotinamide adenine dinucleotide ( NAD) aqueous solution (200mg/ml) was developed at 15μ,
Dry and fix by adsorption, then wash to remove excess NAD
was removed. This electrode was made in the same manner as in Example 1,
It was installed in an enzyme reaction measurement cell with the structure shown in Figures 3 and 2, and a phosphate buffer solution of pH 7.0 containing 0.01 mol/ethanol was flowed into the measurement cell using a liquid pump.
An alcohol dehydrogenase aqueous solution was injected as a sample into this flow, and the response of the electrode was measured. Similar to the results of Example 1, the response based on the oxidation current of NADH was faster and more sensitive in the measurement cell of the present invention than in the conventional measurement cell.
以上、実施例に示した様に、本発明の連続送液
式の酵素反応測定セルを用いることにより、多数
の試料について基質濃度や酵素活性を迅速に、連
続的に測定することができる。 As shown in the Examples above, by using the continuous liquid feeding enzyme reaction measurement cell of the present invention, the substrate concentration and enzyme activity of a large number of samples can be rapidly and continuously measured.
特定物質検出用の電極および、対極、参照極な
どの電極系については実施例に示したものに限定
されることはなく、酵素反応系、使用条件、目的
等に応じたものを選択すればよい。また、電極の
構成、装着方法、およびこれに関連した測定セル
の構造については、本発明の主旨を損なわないも
のであれば実施例に限定されることはない。 Electrodes for detecting specific substances and electrode systems such as counter electrodes and reference electrodes are not limited to those shown in the examples, and may be selected according to the enzyme reaction system, usage conditions, purpose, etc. . Further, the structure of the electrode, the mounting method, and the structure of the measurement cell related thereto are not limited to the embodiments as long as they do not impair the gist of the present invention.
第１図および第２図は、酵素反応測定セルの従
来例を示す断面模式図、第３図は本発明による酵
素反応測定セルの一実施例を示す断面模式図、第
４図は第３図に示す酵素反応測定セルの部分断面
斜視図、第５図は酵素反応測定セルにおけるグル
コースに対する応答電流と時間の関係を示す図で
ある。
２……液流入路、５……特定物質検出用電極、
１４……液流出路。
1 and 2 are schematic cross-sectional views showing a conventional example of an enzyme reaction measurement cell, FIG. 3 is a schematic cross-sectional view showing an embodiment of an enzyme reaction measurement cell according to the present invention, and FIG. FIG. 5 is a partial cross-sectional perspective view of the enzyme reaction measurement cell shown in FIG. 2...Liquid inflow path, 5...Specific substance detection electrode,
14...Liquid outflow path.
Claims (1)
酵素反応測定セルであつて、前記電極が少なくと
も酵素又は補酵素のいずれか固定化してなる電極
からなり、この電極の被検液と接する側の電極面
の中心部近傍に液流入口を設け、かつ電極面のす
べての外周方向に液流出口を設けたことを特徴と
する酵素反応測定セル。1. A continuous liquid feeding type enzyme reaction measurement cell equipped with an electrode for detecting a specific substance, where the electrode is composed of an electrode on which at least either an enzyme or a coenzyme is immobilized, and the electrode is in contact with the test liquid. An enzyme reaction measurement cell characterized in that a liquid inlet is provided near the center of a side electrode surface, and a liquid outlet is provided in the entire outer circumferential direction of the electrode surface.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57039798A JPS58155081A (en) | 1982-03-12 | 1982-03-12 | Cell for measuring enzymatic reaction |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP57039798A JPS58155081A (en) | 1982-03-12 | 1982-03-12 | Cell for measuring enzymatic reaction |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS58155081A JPS58155081A (en) | 1983-09-14 |
| JPH0340335B2 true JPH0340335B2 (en) | 1991-06-18 |
Family
ID=12562970
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP57039798A Granted JPS58155081A (en) | 1982-03-12 | 1982-03-12 | Cell for measuring enzymatic reaction |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS58155081A (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2001281198A (en) | 2000-03-28 | 2001-10-10 | Nec Corp | Apparatus and method for measuring liquid sample |
| JP7825622B2 (en) * | 2021-07-16 | 2026-03-06 | 株式会社 堀場アドバンスドテクノ | Electrochemical measurement device and electrochemical measurement method |
-
1982
- 1982-03-12 JP JP57039798A patent/JPS58155081A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS58155081A (en) | 1983-09-14 |
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