JP3297623B2 - Biosensor - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a biosensor capable of accurately quantifying a substrate such as glucose contained in a sample.

[0002]

2. Description of the Related Art A glucose sensor will be described as an example of a biosensor. As a method of electrochemically determining glucose, glucose oxidase (EC
A method combining 1.1.3.4) with an oxygen electrode or a hydrogen peroxide electrode is generally known (for example, Shuichi Suzuki, "Biosensor", Kodansha). Glucose oxidase uses oxygen as an electron acceptor and β-
Selectively oxidizes D-glucose to D-glucono-δ-lactone. With this reaction, oxygen is reduced to hydrogen peroxide. Glucose can be quantified by measuring the amount of oxygen consumed at this time using an oxygen electrode or measuring the amount of generated hydrogen peroxide using a hydrogen peroxide electrode. However, this type of sensor is greatly affected by the concentration of oxygen dissolved in the sample liquid, and has a problem that the measurement itself cannot be performed under the condition where there is no oxygen.

Therefore, without using oxygen as an electron acceptor,
A new type of glucose sensor using an organic compound such as potassium ferricyanide, a ferrocene derivative, a quinone derivative or a metal complex as an electron acceptor has been developed. In this type of sensor, a reduced form of an electron acceptor generated as a result of an enzymatic reaction is oxidized by an electrode, and the glucose concentration is determined from the oxidation current value. This type of sensor enables a known amount of glucose oxidase and an electron acceptor to be stably and accurately carried on an electrode. Further, the electrode system and the reaction layer can be integrated in a state close to a dry state. The disposable gluco-produced in this way
Sensors have received much attention in recent years because glucose concentrations can be easily measured simply by introducing a sample into a sensor chip inserted into a measuring instrument. This technique is applicable not only to the quantification of glucose but also to the quantification of other specific compounds.

[0004]

In the above biosensors, potassium ferricyanide which is excellent in stability and suitable for mass production is often used as an electron acceptor. However, the second-order rate constant between ferricyanide ion and glucose oxidase is about one thousandth lower than that between oxygen and glucose oxidase. Therefore, when the glucose in the sample solution is in a low concentration range, particularly in the range of 0 to 20 mg / dl, the response of the sensor to glucose is significantly affected, and the response characteristic (linearity of response) of the sensor is deteriorated. was there.

[0005]

In view of the above-mentioned problems, a biosensor according to the present invention comprises an electrode system having at least a working electrode and a counter electrode provided on an insulating substrate, and at least an oxidation system formed on the electrode system. A reaction layer containing a reductase and an electron acceptor, and a layer containing a substrate of the oxidoreductase provided separately from the reaction layer are provided.

[0006]

BEST MODE FOR CARRYING OUT THE INVENTION A sample solution usually contains about 0.25 mM
Contains dissolved oxygen. Therefore, when the sample solution is introduced into the sensor, the enzyme reaction between oxygen and glucose oxidase proceeds simultaneously with the enzyme reaction between ferricyanide ion and glucose oxidase. That is, dissolved oxygen consumes about 0.25 mM glucose. In addition, about 0.25 produced as a result of the oxygen-glucose oxidase reaction.
mM mM hydrogen peroxide oxidizes about 0.5 mM ferrocyanide ions to ferricyanide ions. By this series of reactions, the current response value corresponding to a total of about 1 mM ferrocyanide ions is reduced, and this is the main factor that deteriorates the response characteristics of the sensor in the low concentration region. Therefore, when glucose in an amount corresponding to glucose consumed by dissolved oxygen and ferrocyanide ion oxidized by hydrogen peroxide was previously arranged in the sensor, the decrease in the current response value due to the influence of dissolved oxygen was suppressed, The response characteristics could be improved.

There are two types of glucose sensors according to the present invention. The first type is a sensor having an electrode system formed on an insulating substrate and a reaction layer containing at least an oxidoreductase and an electron acceptor formed on the electrode system. An electrode system formed on a conductive substrate, a reaction layer containing at least an oxidoreductase and an electron acceptor formed on the electrode system, and a sample liquid applied to the electrode system between the substrate and the substrate combined with the substrate. This is a type of sensor having a cover member that forms a sample liquid supply path for supplying the liquid. In each type of sensor, a layer containing a substrate for oxidoreductase in the reaction layer is provided separately from the reaction layer. This layer can be dissolved by the sample liquid introduced to the side of the reaction layer formed on the insulating substrate or to the surface exposed to the sample liquid supply path formed by the cover member combined with the substrate. It is preferable to be provided so that it can be performed.

[0008] The reaction layer may be dissolved in the sample solution or may be immobilized to be insoluble in the sample solution. In addition, coating the electrode system on the insulating substrate with a hydrophilic polymer layer so that enzymes and electron acceptors do not come into contact with the electrode system surface can prevent protein adsorption on the electrode system surface, etc. preferable. Further, when a layer containing lipid such as lecithin is provided on the reaction layer, the sample solution can be smoothly introduced onto the reaction layer.
Examples of the oxidoreductase include glucose oxidase, lactate oxidase, cholesterol oxidase, cholesterol esterase, uricase, invertase, and mutarotase. By including such an oxidoreductase in the reaction layer, a glucose sensor, a lactic acid sensor, a cholesterol sensor, a uric acid sensor, a sucrose sensor, and the like can be manufactured. Examples of the hydrophilic polymer include carboxymethyl cellulose, polyvinyl pyrrolidone, polyvinyl alcohol, gelatin and its derivatives, acrylic acid and its salts, methacrylic acid and its salts, starch and its derivatives, maleic anhydride and its salts, and hydroxypropyl. Cellulose derivatives such as cellulose, methylcellulose, ethylcellulose, hydroxyethylcellulose, ethylhydroxyethylcellulose and carboxymethylethylcellulose can be used. As a method for measuring the oxidation current, there are a two-electrode system including only a measurement electrode and a counter electrode, and a three-electrode system including a reference electrode. The three-electrode system enables more accurate measurement.

[0009]

The present invention will be described below in more detail with reference to specific examples. FIG. 1 is a schematic plan view of a first type of biosensor according to the present invention, from which a reaction layer has been removed. Silver paste is printed by screen printing on an insulating substrate 1 made of polyethylene terephthalate to form leads 2 and 3. Next, the working electrode 4 is formed by printing a conductive carbon paste containing a resin binder on the substrate 1. The working electrode 4 is in contact with the lead 2. Further, an insulating paste is printed on the substrate 1 to form an insulating layer 6. The insulating layer 6 covers the outer periphery of the working electrode 4, thereby keeping the area of the exposed portion of the working electrode 4 constant. Then, a conductive carbon paste containing a resin binder is printed on the substrate 1 so as to be in contact with the leads 3 to form a ring-shaped counter electrode 5. FIG. 2 is a longitudinal sectional view of a first type of biosensor according to the present invention. An electrode system is formed on an insulating substrate 1 in the same manner as in FIG. 1, and a reaction layer 8 containing an oxidoreductase and an electron acceptor is formed on the electrode system. The layer 10 containing glucose is formed separately from the reaction layer 8.

FIG. 3 is an exploded perspective view of a second type of biosensor according to the present invention, from which a reaction layer is removed. An insulating substrate 1 having an electrode system formed in the same manner as in FIG.
The cover 14 and the spacer 13 provided with are bonded in a positional relationship as shown by a dashed line in FIG. 1 to produce a biosensor. Reference numeral 18 denotes an opening of a sample liquid supply path formed by the slit 15 of the spacer 13, the cover 14, and the insulating substrate 1. FIG. 4 is a perspective view of a cover member in which the spacer 13 and the cover 14 are overlapped,
It is arranged upside down from FIG. By combining the cover member and the substrate, a space that forms a sample liquid supply path is formed. Reference numeral 17 denotes a cover-side surface exposed to a space constituting the sample liquid supply path. FIG. 5 is a longitudinal sectional view of a second type of biosensor according to the present invention. An electrode system was formed on an insulating substrate 1 in the same manner as in FIG. A hydrophilic polymer layer 7 is formed so as to cover this electrode system,
Further, a reaction layer 8 containing an oxidoreductase and an electron acceptor is formed on the hydrophilic polymer layer 7. A lecithin layer 9 is formed so as to cover the reaction layer 8. Further, a layer 11 containing glucose is formed on the surface 17 on the cover side exposed to the space constituting the sample liquid supply path.

Example 1 A mixed aqueous solution of glucose oxidase (hereinafter abbreviated as GOD) and potassium ferricyanide was dropped on the electrode system of the insulating substrate 1 in FIG. 1 and dried to form a reaction layer 8. . Next, an aqueous solution of glucose was dropped at a position isolated from the reaction layer 8 and dried to form a layer 10 containing glucose. The glucose-containing layer 10 was formed by adjusting the glucose concentration in the sensor to 0.5 mM by dissolving the sample solution when the sample solution was dropped. Glucose was added as a sample solution on the sensor thus produced.
5 μl of a standard aqueous solution of glucose was added dropwise to dissolve the reaction layer 8 and the layer 10 containing glucose. After a certain time from the supply of the sample liquid, a pulse voltage of +0.5 V is applied to the working electrode 4 in the anode direction with reference to the counter electrode 5 of the electrode system, and the current value after 5 seconds is measured. The response characteristics of were investigated. As a result, in the low concentration range (0 to 20 mg / dl), the response of the sensor showed excellent linearity.

Comparative Example 1 Layer 10 Containing Glucose
A sensor was fabricated in the same manner as in Example 1 except that no was formed, and the response characteristics of the sensor were examined. As a result, the response of the sensor in the low concentration range was not as good as in Example 1.

Example 2 An aqueous solution of carboxymethylcellulose (hereinafter abbreviated as CMC) was dropped on the electrode system of the insulating substrate 1 in FIG. 3 and dried to form a CMC layer 7. Next, a mixed aqueous solution of GOD and ferrocene hexafluorophosphate was dropped on the CMC layer 7 and dried to form a reaction layer 8. Further, a toluene solution of lecithin was dropped on the reaction layer 8 and dried to form a lecithin layer 9.
Next, a glucose aqueous solution was dropped and dried on the cover-side surface 17 exposed in the space constituting the sample liquid supply path in FIG. 4 to form a layer 11 containing glucose. The glucose-containing layer 11 was prepared such that when the sample liquid was introduced through the opening 18 of the sample liquid supply path, the layer was dissolved so that the glucose concentration in the sensor was increased by 0.5 mM. Formed. Finally, the insulating substrate 1, the spacer 13, and the cover 14 were adhered in a positional relationship as shown by a dashed line in FIG. 3 to produce a glucose sensor. To the sensor thus prepared, 3 μl of a standard aqueous solution of glucose was supplied as a sample liquid from the sample supply hole 18. The sample liquid reached the air holes 14 and the reaction layer 8 and the glucose-containing layer 11 on the electrode system were dissolved. In the same manner as in Example 1, the response characteristics of the sensor were examined. As a result, in the low concentration range (0 to 20 mg / dl), the response of the sensor showed excellent linearity.

[0014]

As described above, according to the present invention, it is possible to provide a biosensor in which the influence of dissolved oxygen in a sample solution can be reduced, and in particular, the precision of quantification of a substrate in a low concentration range is improved.

[Brief description of the drawings]

FIG. 1 is a plan view of a substrate provided with an electrode system of a biosensor according to one embodiment of the present invention.

FIG. 2 is a longitudinal sectional view of the biosensor.

FIG. 3 is an exploded perspective view of a biosensor according to another embodiment of the present invention, excluding a reaction layer.

FIG. 4 is a perspective view of a cover member in which a cover and a spacer of the biosensor are superimposed and arranged upside down from FIG. 3;

FIG. 5 is a longitudinal sectional view of a main part of the biosensor.

[Explanation of symbols]

REFERENCE SIGNS LIST 1 insulating substrate 2 lead 3 lead 4 working electrode 5 counter electrode 6 insulating layer 7 CMC layer 8 layer containing oxidoreductase and electron acceptor 9 lecithin layer 10 layer containing glucose 11 layer containing glucose 13 spacer 14 cover 15 Spacer slit 16 Air hole 17 Cover-side surface exposed to space constituting sample liquid supply path 18 Opening of sample liquid supply path

──────────────────────────────────────────────────続 き Continuation of the front page (56) References JP-A-10-232219 (JP, A) JP-A-9-297121 (JP, A) JP-A-10-197473 (JP, A) JP-A-7-297 92138 (JP, A) JP-A-7-83871 (JP, A) JP-A-6-88805 (JP, A) (58) Fields investigated (Int. Cl. ⁷ , DB name) G01N 27/327

Claims (3)

(57) [Claims] An electrode system having at least a working electrode and a counter electrode provided on an insulating substrate, a reaction layer containing at least an oxidoreductase and an electron acceptor formed on the electrode system, and the reaction layer Separated from the substrate
A biosensor comprising a layer containing the substrate for the oxidoreductase, which is provided so as to be dissolved by a sample solution introduced into the reaction layer . 2. An electrode system having at least a working electrode and a counter electrode provided on an insulating substrate, a reaction layer containing at least an oxidoreductase and an electron acceptor formed on the electrode system, and being combined with the substrate. and isolated from the cover member, and said reaction layer is to form a sample solution supply pathway for supplying a sample solution to said electrode system between the substrate, the sample solution supply
A biosensor comprising: a layer containing a substrate of the oxidoreductase provided on a surface exposed to a road . 3. The biosensor according to claim 2, wherein the layer containing the substrate of the oxidoreductase is disposed on a surface of the cover member forming the sample liquid supply path, the surface being exposed to the sample liquid supply path.