JPH02120655A - Glucose sensor - Google Patents
Glucose sensorInfo
- Publication number
- JPH02120655A JPH02120655A JP63273130A JP27313088A JPH02120655A JP H02120655 A JPH02120655 A JP H02120655A JP 63273130 A JP63273130 A JP 63273130A JP 27313088 A JP27313088 A JP 27313088A JP H02120655 A JPH02120655 A JP H02120655A
- Authority
- JP
- Japan
- Prior art keywords
- electrode
- enzyme
- hollow needle
- immobilized
- glucose
- 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
- 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 title claims abstract description 24
- 239000008103 glucose Substances 0.000 title claims abstract description 24
- 235000019420 glucose oxidase Nutrition 0.000 claims abstract description 8
- 238000000034 method Methods 0.000 abstract description 13
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 abstract description 8
- 230000003100 immobilizing effect Effects 0.000 abstract description 7
- 108090000790 Enzymes Proteins 0.000 abstract description 6
- 102000004190 Enzymes Human genes 0.000 abstract description 6
- 229940088598 enzyme Drugs 0.000 abstract description 6
- 239000010410 layer Substances 0.000 abstract description 5
- 238000004519 manufacturing process Methods 0.000 abstract description 5
- 108010015776 Glucose oxidase Proteins 0.000 abstract description 4
- 239000004366 Glucose oxidase Substances 0.000 abstract description 4
- 229940116332 glucose oxidase Drugs 0.000 abstract description 4
- 229910052697 platinum Inorganic materials 0.000 abstract description 4
- 239000012790 adhesive layer Substances 0.000 abstract description 3
- 239000008280 blood Substances 0.000 abstract description 3
- 210000004369 blood Anatomy 0.000 abstract description 3
- 239000003822 epoxy resin Substances 0.000 abstract description 3
- 229920000647 polyepoxide Polymers 0.000 abstract description 3
- 239000000243 solution Substances 0.000 description 5
- 239000000463 material Substances 0.000 description 4
- -1 ferrocene compound Chemical class 0.000 description 3
- 239000000126 substance Substances 0.000 description 3
- 108091006149 Electron carriers Proteins 0.000 description 2
- XEEYBQQBJWHFJM-UHFFFAOYSA-N Iron Chemical compound [Fe] XEEYBQQBJWHFJM-UHFFFAOYSA-N 0.000 description 2
- RTAQQCXQSZGOHL-UHFFFAOYSA-N Titanium Chemical compound [Ti] RTAQQCXQSZGOHL-UHFFFAOYSA-N 0.000 description 2
- 229920002678 cellulose Polymers 0.000 description 2
- 235000010980 cellulose Nutrition 0.000 description 2
- 238000006243 chemical reaction Methods 0.000 description 2
- 239000011521 glass Substances 0.000 description 2
- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 description 2
- 229910052737 gold Inorganic materials 0.000 description 2
- 239000010931 gold Substances 0.000 description 2
- 238000005259 measurement Methods 0.000 description 2
- 229920000642 polymer Polymers 0.000 description 2
- 229910052719 titanium Inorganic materials 0.000 description 2
- 239000010936 titanium Substances 0.000 description 2
- POSZUTFLHGNLHX-KSBRXOFISA-N tris maleate Chemical compound OCC(N)(CO)CO.OCC(N)(CO)CO.OC(=O)\C=C/C(O)=O POSZUTFLHGNLHX-KSBRXOFISA-N 0.000 description 2
- IXPNQXFRVYWDDI-UHFFFAOYSA-N 1-methyl-2,4-dioxo-1,3-diazinane-5-carboximidamide Chemical compound CN1CC(C(N)=N)C(=O)NC1=O IXPNQXFRVYWDDI-UHFFFAOYSA-N 0.000 description 1
- YVXDRFYHWWPSOA-BQYQJAHWSA-N 1-methyl-4-[(e)-2-phenylethenyl]pyridin-1-ium Chemical group C1=C[N+](C)=CC=C1\C=C\C1=CC=CC=C1 YVXDRFYHWWPSOA-BQYQJAHWSA-N 0.000 description 1
- 229920000936 Agarose Polymers 0.000 description 1
- 108010088751 Albumins Proteins 0.000 description 1
- 102000009027 Albumins Human genes 0.000 description 1
- 108091003079 Bovine Serum Albumin Proteins 0.000 description 1
- 229920002101 Chitin Polymers 0.000 description 1
- SXRSQZLOMIGNAQ-UHFFFAOYSA-N Glutaraldehyde Chemical compound O=CCCCC=O SXRSQZLOMIGNAQ-UHFFFAOYSA-N 0.000 description 1
- 239000004372 Polyvinyl alcohol Substances 0.000 description 1
- 239000000853 adhesive Substances 0.000 description 1
- 230000001070 adhesive effect Effects 0.000 description 1
- 239000007864 aqueous solution Substances 0.000 description 1
- 230000015572 biosynthetic process Effects 0.000 description 1
- 229940098773 bovine serum albumin Drugs 0.000 description 1
- 150000001718 carbodiimides Chemical class 0.000 description 1
- 235000010418 carrageenan Nutrition 0.000 description 1
- 239000000679 carrageenan Substances 0.000 description 1
- 229920001525 carrageenan Polymers 0.000 description 1
- 229940113118 carrageenan Drugs 0.000 description 1
- 239000001913 cellulose Substances 0.000 description 1
- 229920002301 cellulose acetate Polymers 0.000 description 1
- 238000004132 cross linking Methods 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 125000000664 diazo group Chemical group [N-]=[N+]=[*] 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- KTWOOEGAPBSYNW-UHFFFAOYSA-N ferrocene Chemical compound [Fe+2].C=1C=C[CH-]C=1.C=1C=C[CH-]C=1 KTWOOEGAPBSYNW-UHFFFAOYSA-N 0.000 description 1
- 150000002303 glucose derivatives Chemical class 0.000 description 1
- 239000003292 glue Substances 0.000 description 1
- 238000007654 immersion Methods 0.000 description 1
- 229910052742 iron Inorganic materials 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 230000003647 oxidation Effects 0.000 description 1
- 238000007254 oxidation reaction Methods 0.000 description 1
- 229920002492 poly(sulfone) Polymers 0.000 description 1
- 229920002037 poly(vinyl butyral) polymer Polymers 0.000 description 1
- 229920002451 polyvinyl alcohol Polymers 0.000 description 1
- 239000013464 silicone adhesive Substances 0.000 description 1
- 235000010413 sodium alginate Nutrition 0.000 description 1
- 239000000661 sodium alginate Substances 0.000 description 1
- 229940005550 sodium alginate Drugs 0.000 description 1
- 239000002904 solvent Substances 0.000 description 1
- 238000001179 sorption measurement Methods 0.000 description 1
- UHVMMEOXYDMDKI-JKYCWFKZSA-L zinc;1-(5-cyanopyridin-2-yl)-3-[(1s,2s)-2-(6-fluoro-2-hydroxy-3-propanoylphenyl)cyclopropyl]urea;diacetate Chemical compound [Zn+2].CC([O-])=O.CC([O-])=O.CCC(=O)C1=CC=C(F)C([C@H]2[C@H](C2)NC(=O)NC=2N=CC(=CC=2)C#N)=C1O UHVMMEOXYDMDKI-JKYCWFKZSA-L 0.000 description 1
Landscapes
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
- Apparatus Associated With Microorganisms And Enzymes (AREA)
Abstract
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は、グルコースセンサに関する。更に詳しくは、
アンペロメトリ型のグルコースセンサに関する。DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to a glucose sensor. For more details,
The present invention relates to an amperometric glucose sensor.
従来のアンペロメトリ型グルコースセンサにおいては、
2個の電極を必要としており、その内の1個は対極であ
り、他の1個は作用極であって、4作用極にはグルコー
スオキシダーゼ酵素(COD)カ固定化されている。こ
のセンサの原理は、グルコースとCODとの反応に伴な
い作用極上で発生する電極検知物質を定量することによ
り、グルコース濃度を決定し得る点にある。In conventional amperometric glucose sensors,
Two electrodes are required, one of which is a counter electrode and the other is a working electrode, and glucose oxidase enzyme (COD) is immobilized on the four working electrodes. The principle of this sensor is that the glucose concentration can be determined by quantifying the electrode detection substance generated on the working electrode as a result of the reaction between glucose and COD.
ところで、グルコースセンサの一つの形態として、針状
構造のものが挙げられるが、従来のアンペロメトリ型グ
ルコースセンサでは、これら2個の電極が例えばガラス
板などの平板状のものを平行に並べて構成させたものが
代表的であり、生体内に挿入し易く血糖値などの測定に
好適に使用し得る針状電極としたものは未だ実用化され
ていない。これは、形状そのものに基因する製作の困難
さや酵素固定化の困難さに由来しているものと考えられ
る。Incidentally, one type of glucose sensor is one with a needle-like structure, but in the conventional amperometric glucose sensor, these two electrodes are constructed by arranging flat plate-shaped objects such as glass plates in parallel. A needle-shaped electrode that is easy to insert into a living body and can be suitably used for measuring blood sugar levels, etc., has not yet been put into practical use. This is thought to be due to the difficulty in manufacturing due to the shape itself and the difficulty in immobilizing the enzyme.
本発明の目的は、このような問題点を克服し、酵素固定
化や製作の容易性が得られるアンペロメトリ型グルコー
スセンサを提供することにある。An object of the present invention is to overcome such problems and to provide an amperometric glucose sensor that allows enzyme immobilization and ease of production.
かかる目的を達成せしめる本発明のグルコースセンサは
、長さ方向に半截された中空針状対極の切断面に絶縁層
を介してグルコースオキシダーゼ酵素固定化平板状作用
極を酵素固定化面側を内側に向けて接着してなる。The glucose sensor of the present invention that achieves this object has a flat working electrode with glucose oxidase enzyme immobilized on the cut surface of a hollow needle-shaped counter electrode that has been cut in half in the length direction with an insulating layer interposed therebetween, with the enzyme-immobilized surface side facing inside. Glue it to the right direction.
図面の第1図には、本発明に係るグルコースセンサの一
態様が接着前の状態で斜視図として示されている。即ち
、針状対極1は、一般に外径が約1m以下の白金、金、
チタンなどの中空針の長さ方向の半截物2であって、そ
の先端部3が挿入し易いように注射針状に斜切されてい
る。そして、半截さ九た切断面には、一般に接着剤層を
兼ねた絶縁層4,4′、例えばエポキシ樹脂接着剤、シ
リコーン系接着剤あるいはガラスなどが塗布されている
。FIG. 1 of the drawings shows one embodiment of the glucose sensor according to the present invention as a perspective view in a state before adhesion. That is, the acicular counter electrode 1 is generally made of platinum, gold, or gold having an outer diameter of about 1 m or less.
It is a longitudinal half-cut piece 2 of a hollow needle such as titanium, and its tip 3 is cut obliquely into the shape of a hypodermic needle so that it can be easily inserted. The half-cut surface is generally coated with an insulating layer 4, 4' which also serves as an adhesive layer, such as an epoxy resin adhesive, a silicone adhesive, or glass.
一方、この絶縁層を介して中空針状対極に接着されるグ
ルコースオキシダーゼ酵素固定化平板状作用極5は、厚
さ約0.05〜1m程度の白金、チタンなどの平板6で
あって、一般にその長さが対極切断面の長さ以下で、幅
が切断面間隔に等しいものの片面側にGODを固定化7
せしめている。On the other hand, the glucose oxidase enzyme-immobilized flat working electrode 5, which is adhered to the hollow needle-like counter electrode through this insulating layer, is a flat plate 6 made of platinum, titanium, etc. with a thickness of approximately 0.05 to 1 m, and is generally GOD is immobilized on one side of which the length is less than the length of the opposite electrode cut surface and the width is equal to the cut surface interval 7
It's forcing me.
CODの作用極上への固定化に際しては、膜形成材料、
例えば酢酸セルロースなどのセルロース類。When immobilizing COD on the working electrode, a film-forming material,
For example, celluloses such as cellulose acetate.
ポリビニルブチラール、ポリスルホンなどの合成高分子
物質、あるいはセルロース、キチン、アルブミン、アル
ギン酸ナトリウム、アガロース、カラギーナンなどの天
然高分子物質が用いられ、それらを可溶性溶媒に溶解さ
せたドープ液として調製した後、浸漬法、ドロップ法、
スピナ法などにより作用極面上に適用する。また、膜形
成材料として、分子中に光架橋性基としてスチルバゾリ
ウム基、ジアゾ基などの感光性基を有するポリビニルア
ルコールなどの水溶性光架橋性重合体なども水溶液とし
て用いることができる。Synthetic polymeric substances such as polyvinyl butyral and polysulfone, or natural polymeric substances such as cellulose, chitin, albumin, sodium alginate, agarose, and carrageenan are used, and after preparing them as a dope solution by dissolving them in a soluble solvent, immersion is performed. method, drop method,
Apply it on the working electrode surface using the spinner method or the like. Further, as a film-forming material, a water-soluble photocrosslinkable polymer such as polyvinyl alcohol having a photosensitive group such as a stilbazolium group or a diazo group as a photocrosslinkable group in the molecule can also be used in the form of an aqueous solution.
これらの膜形成材料によって形成される眼上へのGOD
の固定化は、グルタルアルデヒド、カルボジイミドなど
を用いる共有結合法、イオン結合法、吸着法、架橋法な
ど一般的に用いられている方法によって行われる。ある
いは、膜形成材料の溶液中などにGODを混合しておき
、膜形成時にこれらの固定化方法により固定化させるこ
ともできる。GOD on the eye formed by these film-forming materials
The immobilization is carried out by commonly used methods such as a covalent bonding method using glutaraldehyde, carbodiimide, etc., an ionic bonding method, an adsorption method, and a crosslinking method. Alternatively, GOD can be mixed in a solution of a film-forming material or the like, and then immobilized by one of these immobilization methods during film formation.
この場合、光架橋性重合体が用いられたときには、それ
の光架橋はCODを失活させない波長である約350〜
450nmの近紫外線による光照射によって行われる。In this case, when a photocrosslinkable polymer is used, its photocrosslinking occurs at a wavelength of about 350 to 350 nm, which is a wavelength that does not deactivate COD.
This is carried out by light irradiation with near ultraviolet light of 450 nm.
このような固定化CODによるグルコースの定量なる反
応により、生成した1(20□を作用極での酸化電流値
変化として検出する。As a result of such a reaction of quantifying glucose using immobilized COD, the generated 1(20□) is detected as a change in the oxidation current value at the working electrode.
また、Wi子ツメデイエータ電子伝達体)であるフェロ
セン化合物、具体的にはフェロセン[ビス(シクロペン
タジェニル)鉄(■)]またはその誘導体。Also, a ferrocene compound which is an electron carrier (electron carrier), specifically ferrocene [bis(cyclopentagenyl)iron (■)] or a derivative thereof.
例えばl、1′−ジメチルフェロセンなどを用い、それ
を作用極面上に真空蒸着させた後、この蒸着面にCOD
を一般的に用いられる固定化法によって固定化せしめ、
あるいはCODを固定化させた後フェロセン化合物をそ
こに滴下法などで重層し。For example, using l,1'-dimethylferrocene, etc., it is vacuum-deposited on the working electrode surface, and then COD is applied to this vapor-deposited surface.
is immobilized by a commonly used immobilization method,
Alternatively, after immobilizing COD, a ferrocene compound is layered thereon by a dropping method or the like.
j@
この場合には、グルコース1分子が酸化されるのに、2
電子の作用極への移動が行われるので、これを電流値変
化として検出することができる。j@ In this case, for one molecule of glucose to be oxidized, 2
Since electrons move to the working electrode, this can be detected as a change in current value.
かかるGOD固定化平板状作用極の中空針状対極への接
着は、酵素固定化面側が内側に向けられるようにして行
われる。なお、対極および作用極からは、それぞれリー
ド線8,8′が引き出されており、測定時には、これら
の電極とは別に参照極も用いられる。The GOD-immobilized plate-like working electrode is adhered to the hollow needle-like counter electrode with the enzyme-immobilized surface facing inward. Note that lead wires 8 and 8' are drawn out from the counter electrode and the working electrode, respectively, and a reference electrode is also used in addition to these electrodes during measurement.
本発明に係る針状のアンペロメトリ型グルコースセンサ
は、グルコースオキシダーゼ酵素の固定化が平板状の作
用極面上に対して行われるのでそこに困難性はなく、ま
た針状i’l!極という形状に基因する製作上の困難性
も格別認められず、生体内に挿入し易く血糖値などの測
定に好適に使用し得るグルコースセンサとして提供され
る。In the needle-shaped amperometric glucose sensor according to the present invention, since the glucose oxidase enzyme is immobilized on the plate-shaped working electrode surface, there is no difficulty therein, and the needle-shaped i'l! There are no particular difficulties in manufacturing due to the polar shape, and the glucose sensor is provided as a glucose sensor that can be easily inserted into a living body and can be suitably used for measuring blood sugar levels and the like.
次に、実施例について本発明を説明する。 Next, the present invention will be explained with reference to examples.
実施例 第1図に示された態様のグルコースセンサを製作した。Example A glucose sensor of the embodiment shown in FIG. 1 was manufactured.
中空針状対極は、内径0.8mm、外径1.Onwn、
長さ31の白金中空針を半截し、先端部を斜切したもの
であり、平板状作用極としては、1.OX 2.5X0
.2+nmの寸法のものが用いられ、その片面側にCO
Dを固定化させた。The hollow needle-shaped counter electrode has an inner diameter of 0.8 mm and an outer diameter of 1. Onwn,
A platinum hollow needle with a length of 31 mm is cut in half and the tip is cut obliquely.As a flat working electrode, 1. OX2.5X0
.. A size of 2+nm is used, and one side of it is coated with CO.
D was immobilized.
GODの固定化は、GO030■および牛血清アルブミ
ン30■をpH7,0の5InMトリスーマレイン酸緩
衝液0.4mΩに溶解し、その4μQを平板状作用極面
上に滴下し、4℃で4時間放置した後、そこに1,1′
−ジメチルフェロセンのアセトン溶液4μQを滴下し、
再び4℃で4時間放置することにより行われた。For immobilization of GOD, GO030■ and bovine serum albumin 30■ were dissolved in 0.4 mΩ of 5 InM tris-maleate buffer at pH 7.0, 4 μQ of the solution was dropped onto the plate-like working electrode surface, and the solution was incubated at 4°C for 4 hours. After leaving it for a while, there 1,1'
-Drop 4μQ of dimethylferrocene acetone solution,
This was carried out by leaving the mixture at 4° C. for 4 hours again.
このCOD固定化平板状作用極を、酵素固定化面側を内
側に向けて、中空針状対極にその切断面に塗布されたエ
ポキシ樹脂接着剤層を介して接着し、4℃で48時間放
置した。This COD-immobilized flat working electrode was adhered to a hollow needle-like counter electrode with the enzyme-immobilized side facing inward through an epoxy resin adhesive layer applied to its cut surface, and left at 4°C for 48 hours. did.
これらの各電極をポテンショスタットに接続し。Connect each of these electrodes to a potentiostat.
対極−作用極間電位50mV、作用極−参照極(Ag/
AgCQ電極)間電位200mVとして、グルコースに
対する応答を測定した゛。測定は、37℃でpH7,0
の5mMトリス−マレイン酸緩衝液を使用して行われた
。Potential between counter electrode and working electrode 50 mV, working electrode and reference electrode (Ag/
The response to glucose was measured at a potential of 200 mV between the AgCQ electrodes. Measurements were carried out at 37°C and pH 7.0.
5mM Tris-maleate buffer.
その結果は、第2図のグラフに示されるように、グルコ
ース濃度50〜300mg/d Qの範囲内で、応答電
流の定常値との間に直線的な相関関係が認められた。As shown in the graph of FIG. 2, the results showed a linear correlation with the steady-state value of the response current within the glucose concentration range of 50 to 300 mg/dQ.
第1図は、本発明のグルコースセンサの一態様を接着前
の状態で示した斜視図である。また、第2図は、このグ
ルコースセンサを用いた場合のグルコース濃度と出力電
流との関係を示すグラフである。
(符号の説明)
1・・・・・・針状対極
2・・・・・・中空針の半截物
4・・・・・・絶縁層
5・・・・・・GOD固定化平板状作用極6・・・・・
・平板
7・・・・・・固定化CODFIG. 1 is a perspective view showing one embodiment of the glucose sensor of the present invention in a state before adhesion. Moreover, FIG. 2 is a graph showing the relationship between glucose concentration and output current when this glucose sensor is used. (Explanation of symbols) 1... Needle-like counter electrode 2... Half-cut hollow needle 4... Insulating layer 5... GOD-immobilized plate-like working electrode 6...
・Flat plate 7...immobilized COD
Claims (1)
層を介してグルコースオキシダーゼ酵素固定化平板状作
用極を酵素固定化面側を内側に向けて接着してなるグル
コースセンサ。1. A glucose sensor in which a flat plate-like working electrode with glucose oxidase enzyme immobilized is adhered to the cut surface of a hollow needle-like counter electrode that has been cut in half in the length direction via an insulating layer, with the enzyme-immobilized surface facing inward.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP63273130A JP2689531B2 (en) | 1988-10-31 | 1988-10-31 | Glucose sensor |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP63273130A JP2689531B2 (en) | 1988-10-31 | 1988-10-31 | Glucose sensor |
Publications (2)
Publication Number | Publication Date |
---|---|
JPH02120655A true JPH02120655A (en) | 1990-05-08 |
JP2689531B2 JP2689531B2 (en) | 1997-12-10 |
Family
ID=17523545
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP63273130A Expired - Fee Related JP2689531B2 (en) | 1988-10-31 | 1988-10-31 | Glucose sensor |
Country Status (1)
Country | Link |
---|---|
JP (1) | JP2689531B2 (en) |
Cited By (34)
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US5437999A (en) * | 1994-02-22 | 1995-08-01 | Boehringer Mannheim Corporation | Electrochemical sensor |
US6071391A (en) * | 1997-09-12 | 2000-06-06 | Nok Corporation | Enzyme electrode structure |
WO2007119853A1 (en) | 2006-04-17 | 2007-10-25 | Sumitomo Electric Industries, Ltd. | Biosensor chip |
US7288073B2 (en) | 2001-07-20 | 2007-10-30 | Roche Diagnostics Operations, Inc. | System for withdrawing small amounts of body fluid |
WO2008056598A1 (en) | 2006-11-10 | 2008-05-15 | National Institute Of Advanced Industrial Science And Technology | Biosensor cartridge, biosensor device, specimen sampling method, manufacturing method for biosensor cartridge, and needle-integrated sensor |
JP2008113769A (en) * | 2006-11-01 | 2008-05-22 | Sumitomo Electric Ind Ltd | Sensor cartridge |
WO2008075651A1 (en) | 2006-12-19 | 2008-06-26 | National Institute Of Advanced Industrial Science And Technology | Biosensor cartridge, method of using biosensor cartridge, biosensor device and needle-integrated sensor |
US7629172B2 (en) | 2002-01-04 | 2009-12-08 | Becton, Dickinson And Company | Entrapped binding protein as biosensors |
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