KR100757297B1 - Sample injection time improved biosensor and measurement method - Google Patents

Abstract

A sample injection time-improved biosensor is provided to inject the sample into an enzyme reaction layer rapidly by rapidly releasing the air produced from the enzyme reaction layer upon injecting the sample, so that the results are obtained rapidly. A sample injection time-improved biosensor(20) comprises: an insulating substrate(200); an electrode part(210) containing an operation electrode(211), a reference electrode(212) and a subsidiary electrode(213) and being formed on a certain region on the insulating substrate; a lead terminal part(220) containing an operation electrode lead(221), a reference electrode lead(222) and a subsidiary electrode lead(223) connected to the electrodes; an insulating layer(230) located on the electrode part and lead terminal part, insulating the electrodes and lead terminals and having an exposure groove(232) for exposing a part of the electrode part; an enzyme reaction layer(240) formed on the exposed region of the electrode part and containing materials causing electrochemical reaction with the sample; a spacer(250) formed on the insulating layer and enzyme reaction layer and having a sample inlet(252) at the same position as the exposure groove; an air-releasing layer(260) formed on the spacer and having an air-releasing pathway(262) connecting from a corner of one side to an opposite corner; and a cover part(270) located on the air-releasing layer, wherein the air-releasing pathway is positioned at the identical line to the sample inlet so that the air-releasing direction is identical to the sample-injecting direction.

Description

Biosensor capable of rapid sample injection and blood glucose measurement method using the sensor {Sample injection time improved biosensor and measurement method}

1 is a block diagram showing an overall configuration of a blood glucose measurement system to which a biosensor according to a preferred embodiment of the present invention is applied.

FIG. 2A is an exploded perspective view illustrating a biosensor according to a first preferred embodiment of the present invention, and FIG. 2B is a cross-sectional view thereof.

FIG. 3A is an exploded perspective view illustrating a biosensor according to a second exemplary embodiment of the present invention, and FIG. 3B is a cross-sectional view thereof.

4 is a flowchart sequentially illustrating an operation of a blood glucose measurement system for measuring blood glucose using a biosensor according to the present invention.

<Explanation of symbols for main parts of the drawings>

10: blood glucose measurement system

20, 30: biosensor

50: blood sugar measuring device

200: insulating substrate

210: electrode portion

220: lead terminal portion

230: insulation layer

240: enzyme reaction layer

250: spacer

260: air discharge layer

270 cover part

500: control unit

502: sensor insertion unit

510: resistance measurement unit

520: A / D converter

522: amplification unit

530: display unit

540: memory

The present invention relates to a biosensor for measuring blood glucose with improved sample injection rate, and to a biosensor capable of rapidly injecting a sample of the biosensor to accurately measure and provide a blood glucose value within a short time. It is about.

In recent years, the need to periodically measure the amount of glucose (blood sugar) in the blood is increasing in diagnosing and preventing diabetes. The blood glucose measurement can be easily measured using a blood glucose measurement device. The blood glucose measurement apparatus collects a sample from a patient using a strip-type biosensor and measures blood glucose values by using an electrical signal generated through an electrochemical reaction between the sample and a chemical in the biosensor.

As described above, the operating principle and structure of the biosensor and the blood glucose measurement apparatus using the biosensor are variously developed and developed.

Biosensors typically form an electrode system including a plurality of electrodes on an insulating substrate by screen printing or the like, and form an enzyme reaction layer made of a hydrophilic polymer, a redox enzyme, and an electron acceptor on the formed electrode system. .

When a sample including a substrate (glucose) is injected into the enzyme reaction layer through the sample inlet of the biosensor, the enzyme reaction layer dissolves it, and the substrate and the enzyme react with each other to oxidize the substrate. The electron acceptor is thus reduced.

By measuring the oxidation current obtained by electrochemically oxidizing the reduced electron acceptor through a measuring device, the concentration of the substrate contained in the sample can be obtained.

In this process, the measurement time and measurement accuracy of the biosensor depend on how quickly and accurately the sample is sucked into the sample reaction layer, and the enzyme reaction layer suction rate of the sample is determined by how quickly the air of the enzyme reaction layer is discharged and the enzyme. It depends on how short and small the reaction bed is.

As a prior patent related to the suction rate of the sample, in the case of the prior patent, the biosensor presented in Korean Patent Application No. 2001-40690 (2001. 07. 07) separates the resin plate (spacer) and is perpendicular to the enzyme reaction layer. The air outlet is formed in one direction, and the air is discharged to the outside through the air outlet.

In the case of the biosensor proposed in the patent, the sample injection direction injected into the enzyme reaction layer and the air outlet through which the air is discharged are formed in a vertical form, and thus the air discharge rate is injected through the enzyme reaction layer. It depends on the speed, thereby increasing the amount of sample had a disadvantage.

Therefore, the present inventors have conducted research on biosensors having various structures to improve the rate at which the sample is sucked into the enzyme reaction layer.

An object of the present invention for solving the above problems is to provide a blood glucose measurement biosensor capable of measuring the blood glucose value quickly and accurately by providing a sample injection into the sample inlet quickly and smoothly.

The biosensor with improved sample injection rate according to the present invention for achieving the object is characterized in that it comprises an air outlet in the same horizontal direction as the direction in which the sample is sucked into the enzyme reaction layer.

The present invention relates to a blood glucose measurement biosensor for generating and outputting an electrical signal for measuring blood glucose from a sample injected from the outside.

Dielectric substrate,

An electrode part formed on a predetermined region of an upper portion of the insulating substrate, the electrode part comprising a working electrode, a reference electrode, and an auxiliary electrode;

A lead terminal portion including a working electrode lead, a reference electrode lead, and an auxiliary electrode lead connected to each electrode of the electrode portion;

An insulating layer disposed on the electrode part and the lead terminal part to electrically insulate the electrodes and the lead terminals, and having an exposed groove exposing a part of the electrode part;

An enzymatic reaction layer formed on an upper portion of a corresponding region of an electrode portion exposed by an exposure groove of the insulating layer, and including an substance causing an electrochemical reaction with a sample;

A spacer disposed on the insulation layer and the enzyme reaction layer and having a sample injection hole formed at the same position as the exposed groove of the insulation layer;

An air exhaust layer disposed on an upper portion of the spacer and having an air exhaust passage connecting an opposite edge from an edge of one side;

A cover part disposed on the air exhaust layer

The air discharge passage of the air discharge layer is disposed in the same line as the longitudinal direction of the sample inlet of the spacer, so that the discharge direction of the air and the injection direction of the sample is the same, thereby increasing the suction rate of the sample. It can be characterized by.

One end of the air discharge passage of the air discharge layer of the blood glucose measurement biosensor having the above-described characteristics is preferably arranged to protrude from the distal end of the sample inlet.

Biosensor for measuring blood glucose according to another feature of the present invention

Dielectric substrate,

An electrode part formed on a predetermined region of an upper portion of the insulating substrate, the electrode part comprising a working electrode, a reference electrode, and an auxiliary electrode;

A lead terminal portion including a working electrode lead, a reference electrode lead, and an auxiliary electrode lead connected to each electrode of the electrode portion;

An insulating layer disposed on the electrode part and the lead terminal part to electrically insulate the electrodes and the lead terminals, and having an exposed groove exposing a part of the electrode part;

An enzymatic reaction layer formed on an upper portion of a corresponding region of an electrode portion exposed by an exposure groove of the insulating layer, and including an substance causing an electrochemical reaction with a sample;

It is disposed on the insulating layer and the enzyme reaction layer, and formed in the sample injection port formed in the same position as the exposed groove of the insulating layer, the air discharge passage for discharging the air generated from the sample injection port and the air discharge passage A spacer having an air outlet,

A cover part disposed on the spacer

The air discharge passage of the spacer is arranged on the same line as the longitudinal direction of the sample injection port of the spacer, but arranged to be spaced apart by a predetermined distance, so that the discharge direction of the air and the injection direction of the sample to be the same, the suction of the sample It is characterized in that the speed can be improved.

The cover portion of the blood glucose measurement biosensor having the above-mentioned characteristics further includes a protrusion for close contact with the air discharge passage of the spacer, the protrusion is formed in a portion of the sample inlet and the upper portion of the air discharge passage ,

One end of the protruding portion formed in the cover portion is preferably arranged to protrude from the distal end of the sample inlet.

Blood glucose measurement method according to another aspect of the present invention, in the biosensor having the above-described structure, counting the time between the measurement of the resistance between the reference electrode and the auxiliary electrode and the change in resistance at the auxiliary electrode after the sample injection By determining whether or not the sample injection is abnormal, the measured blood glucose value is corrected, and finally the blood glucose value is detected.

Hereinafter, with reference to the accompanying drawings will be described in detail the configuration and operation of the blood glucose measurement biosensor according to a preferred embodiment of the present invention.

1 is a block diagram showing an overall configuration of a blood glucose measurement system 10 to which a biosensor according to a preferred embodiment of the present invention is applied. Referring to FIG. 1, the blood sugar measuring system 10 includes a blood sugar measuring device 50 and a biosensor 20, and the blood sugar measuring device 50 uses an electrical signal transmitted from a lead terminal of the biosensor. Blood glucose is measured and displayed on the display.

First preferred embodiment

2 is an exploded perspective view illustrating a biosensor according to a first embodiment of the present invention. Referring to FIG. 2, the biosensor 20 includes an insulating substrate 200, an electrode unit 210, a lead terminal unit 220, an insulating layer 230, an enzyme reaction layer 240, a spacer 250, and air discharge. Layer 260 and cover 270.

The insulating substrate 200 is a base substrate for forming the biosensor on the upper surface, and is formed using a polymer resin of a non-conductive material. The polymer resin having the non-conductive material may include polyester, polycarbonate, polystyrene, polyimide, polyvinyl chloride, polyethylene, polyethylene terephthalate, and polyethylene. polymer compounds such as terephthalate).

The electrode unit 210 includes a working electrode 211, a reference electrode 212, and an auxiliary electrode 213, and detects an electrical signal generated by an enzyme reaction with blood glucose in a sample in the enzyme reaction layer 240. do.

The lead terminal unit 220 includes three working electrode lead terminals 221, a reference electrode lead terminal 222, and an auxiliary electrode lead terminal 223, and are disposed in an area adjacent to an edge of the upper surface of the insulating substrate. Each lead terminal is electrically connected to a blood glucose meter.

Each electrode of the electrode portion and each lead terminal of the lead terminal portion are formed on the insulating substrate, and respective lead wires for connecting each electrode of the electrode portion and each of the lead terminals of the lead terminal portion include an electrode on the insulating substrate. It is formed between each electrode of a part and each lead terminal of a lead terminal part.

The lead terminals and lead wires may use a paste of platinum (Pt), gold (Au), silver (Ag), silver and silver chloride (Ag / AgCl), and the electrode part may include platinum (Pt) and gold ( Au) Silver (Ag), a mixed dough of silver and silver chloride (Ag / AgCl), and a conductive carbon dough can be used to form by conventional methods such as etching, screen printing, spattering and the like.

The working electrode 211 and the reference electrode 212 constituting the electrode part must have the same electrical resistance value and area. In addition, it should be formed to be arranged at the same distance to the left and right about the long axis of the reference electrode 212 of the electrode portion. This is to detect the amount of current between the reference electrode and the adjacent working electrode under the same electrochemical conditions. These electrodes serve to detect the amount of current generated by the redox reaction generated in the enzyme reaction layer.

The insulating layer 230 is an insulating layer formed on the electrode portion 210 and the lead terminal portion 220, and insulates each of the lead wires adjacent to each other and the lead terminals of the lead terminal portion. An exposed groove 232 is formed on one side of the insulating layer, and the exposed groove is formed on the electrode part to expose only a portion of the electrode part. The insulating material used in the insulating layer is preferably a non-conductive dough or an insulating dough, and the insulating materials are formed using a conventional method such as screen printing.

The exposure grooves 232 serve to expose only a predetermined portion of the electrode portion, thereby always reacting with the same area when an oxidation current is generated by an enzyme reaction between the enzyme reaction layer introduced into the electrode portion and the sample. In addition, when the enzyme reaction layer is introduced into the exposure groove, the amount of the enzyme reaction layer can be adjusted according to the thickness of the exposure groove. At this time, by generating a fine vibration from the outside can be made so that the enzyme reaction layer is always formed in the exposed groove.

Enzyme reaction layer 240 is formed on the upper surface of the electrode portion exposed by the exposure groove of the insulating layer, the enzyme reaction layer includes glucose oxidase (glucose oxidase), and the electron transfer medium for mediating electron transfer . Specifically, the enzyme reaction layer is dried after coating a predetermined amount of a solution prepared by mixing a water-soluble polymer, the enzyme, a stabilizer, an electron transfer medium and the like in an electrolyte solution in an exposed area of the electrode portion exposed by the exposure groove. It can be formed by.

As the electron transfer medium included in the enzyme reaction layer, ferrocene, ferrocene derivative, quinone, quinone derivative, and the like, which have been widely used in the prior art, are preferably hexaamineruthenium (III) chloride (hexaammineruthenium (III)). chloride), potassium ferricyanide and the like can be used.

In the enzyme reaction layer formed in a predetermined region in the electrode unit, glucose in blood detects a current generated through a redox reaction with glucose oxidase and an electron transfer medium, and transmits the current to a blood glucose measurement apparatus through a lead terminal. After converting the current transmitted through the electrode portion of the biosensor into a concentration value, it is possible to quantitatively calculate the concentration of glucose present in the blood, that is, the blood glucose value.

Hereinafter, look at the enzyme reaction occurring in the enzyme reaction layer. As shown in Scheme 1 below, glucose in blood is oxidized by the catalysis of glucose oxidase and glucose oxidase is reduced. Thereafter, the reduced glucose oxidase is oxidized through the redox reaction with the electron transfer medium, and the glucose oxidase is reduced. The reduced electron transfer medium formed as described above is diffused to the electrode surface, and the current generated by applying the oxidation potential to the reduced electron transfer medium is measured. Since glucose in the blood is proportional to the amount of current generated during the oxidation of the electron transfer medium, blood glucose can be measured by measuring the amount of current.

The spacer 250 includes a sample inlet 252 through which the blood is injected and is disposed on the insulating layer. The sample injection hole 252 is formed in the spacer so as to be located vertically above the enzyme reaction layer, so that the sample injected through the sample injection hole contacts the enzyme reaction layer. The thickness of the spacer should be thicker than the thickness of the enzyme reaction layer. This is to facilitate the injection of the sample when the blood flowing into the sample injection unit is injected back into the enzyme reaction layer. That is, it is because the injection of the sample by the capillary phenomenon is an easy space generated when the thickness of the spacer is thicker than the thickness of the enzyme reaction layer.

In addition, the spacer may be made of the same material as the insulating substrate, it is preferable to use a hydrophobic (hydrophobic) material to prevent the sample from seeping into the adhesive for bonding the spacer and the insulating layer.

The air discharge layer 260 includes an air discharge passage 262 and is disposed above the spacer, so that the sample introduced through the sample inlet is injected into the enzyme reaction layer and is present in the enzyme reaction layer. Make sure that you can effectively discharge the air you are doing.

The air discharge layer 260 is preferably formed to cover the end region of the sample inlet of the spacer and the remaining area of the spacer except for the sample inlet. The air discharge passage 262 is formed of a passage of a predetermined size penetrating from the edge of the sample inlet 252 side of the air discharge layer 260 to the opposite edge, is formed in the same direction as the longitudinal direction of the sample inlet It is preferable.

The air discharge passage is formed in a section in which blood and the enzyme reaction layer cannot exist, through which only air escapes. The angle formed by the air discharge passage and the spacer formed in this way is not limited, but the air discharge passage is preferably formed in a direction parallel to the direction of the sample inlet. This is because the suction speed of the sample can be improved by making the advancing direction of the blood to the sample inlet and discharge direction of the air the same.

The operation of the air discharge passage is as follows. When the sample starts to be sucked into the sample inlet of the spacer, air existing around the enzyme reaction layer is gradually pushed to the end of the sample inlet by pressure, and the sample is provided through the air discharge passage formed at the end of the sample inlet. Air is discharged to the outside in the same direction as the longitudinal direction of the inlet, and as a result, the sample suction rate to the enzyme reaction layer is improved.

By separating the spacer and the air discharge layer in which the air discharge passage is formed as in this embodiment, there is no fear that the sample will get on the patient's hand when removing the biosensor from the blood glucose measurement apparatus after blood glucose measurement. In addition, by arranging the edge of the front end portion of the air outlet passage more protruding than the edge of the inner distal end of the sample inlet of the spacer, the air can be discharged before the injected blood reaches the distal end of the sample inlet of the spacer, the overall efficient Air exhaust is possible. Further, by designing the width of the air discharge passage to be the same as or smaller than the width of the sample inlet, the air discharge speed is improved because the movement of air, which is gas, is much faster than the movement of the sample which is liquid.

In addition, the air discharge layer may be made of the same material as the insulating substrate and the spacer, it is preferable to use a hydrophobic material for preventing the sample from seeping into the adhesive for bonding the air discharge layer and the spacer.

The cover part 270 is formed on the air discharge layer to prevent foreign matter from entering into the air outlet, and the material may be made of the same material as the insulating substrate, the spacer, and the air discharge layer. In addition, it is preferable to use a hydrophobic material for preventing the sample from seeping into the adhesive for bonding the cover portion and the air discharge layer.

In the biosensor having the above-described configuration, the sample is injected through the sample inlet, the injected sample is absorbed into the enzyme reaction layer, and the enzyme is reacted, and the resulting electrical signal is transmitted to the blood glucose measurement apparatus through the electrode unit.

Second embodiment

Hereinafter, the configuration and operation of the biosensor according to the second embodiment of the present invention will be described. 3 is an exploded perspective view showing the biosensor 30 according to the second embodiment of the present invention.

Referring to FIG. 3, the biosensor 30 according to the second embodiment includes an insulating substrate 300, an electrode unit 310, a lead terminal unit 320, an insulating layer 330, an enzyme reaction layer 340, and a spacer. 350, and a cover 370. Among the above-described components, the insulating substrate 300, the electrode portion 310, the lead terminal portion 320, the insulating layer 330, and the enzyme reaction layer 340 are the same as those of the first embodiment, and thus description thereof is omitted. .

The spacer 350 according to the present exemplary embodiment includes a sample inlet 352, an air outlet passage 354, and an air outlet 356. Since the sample injection hole 352 has the same configuration and operation as the sample injection hole 252 in the first embodiment, description thereof will be omitted.

The air discharge passage 354 is formed from a position spaced a predetermined distance from the edge of the inner end portion of the sample inlet 352 is formed a passage of a predetermined size to the edge of one side of the spacer. In addition, the air discharge passage 354 is formed to protrude from the surface of the spacer, it is possible to form a space in which air can be easily discharged. In addition, the air discharge passage 354 is preferably arranged in the same line as the longitudinal direction of the sample inlet 352, so as to be formed in the same direction as the sample travel direction in the sample inlet 352.

The air outlet 356 is formed on one side of the air outlet passage 354 at a position facing the air outlet passage 354 and the sample inlet.

The cover part 370 includes a protrusion 372 to be in close contact with the air discharge passage of the spacer, and is disposed on the spacer 350. The distal end of the protrusion 372 is formed to protrude more than the inner edge of the sample inlet of the spacer 350 to cover a portion of the inner distal end of the sample inlet of the spacer 350. Accordingly, a predetermined exposure space A is formed between the distal end of the protrusion 372 of the lid 370 and the distal end of the air discharge passage 354 of the spacer 350, and a sample is provided below the exposed space. A portion of the inlet is exposed, and an enzyme reaction layer is disposed below the exposed sample inlet.

Hereinafter, operations of the spacer 350 and the cover part 370 of the biosensor 30 according to the present embodiment will be described in detail. When the sample is injected into the enzyme reaction layer through the sample injection hole of the spacer 350, air is discharged from the enzyme reaction layer to the exposed space A by the sample injection. Air discharged to the exposed space is discharged to the air outlet 356 of the spacer 350. The air discharged through the air outlet 356 of the spacer 350 is discharged to the outside through the air discharge passage 354. Here, the air discharge passage 354 is formed to be in the same direction as the sample inlet, it is possible to quickly discharge the air.

Since the material of the cover part 370 is the same as the cover part of the first embodiment described above, overlapping description thereof will be omitted.

Blood glucose measurement system

Hereinafter, the configuration and operation of the blood glucose measurement system using the biosensor according to the present invention will be described in detail.

As shown in FIG. 1, the blood glucose measurement apparatus 50 includes a control unit 500, a sensor insertion unit 502, a resistance measurement unit 510, an A / D converter 520, an amplifier 522, and a display unit. 530 and a memory unit 540, and receives electrical signals from the working electrode lead, the reference electrode lead, and the auxiliary electrode lead through the sensor insertion unit 502 of the biosensor 52 to measure blood glucose levels. Display on the display.

 The amplifier 522 is an operational amplifier used as a current-voltage converter, and a DC voltage source is connected to the non-inverting terminal (+) of the amplifier and a working electrode lead is connected to the inverting terminal (-). The amplifier supplies power to the working electrode, and detects the amount of current flowing through the working electrode according to the power supply, and outputs the voltage value.

The A / D converter 520 converts an analog voltage value output from the amplifier into a digital signal and transmits the converted digital signal to the controller 500.

The reference electrode of the biosensor is used as a reference electrode by being grounded through the reference electrode lead.

The resistance measuring unit 510 measures the resistance value between the auxiliary electrode and the reference electrode and transmits the resistance value to the control unit 500.

The controller 500 controls the overall operation of the blood sugar measuring apparatus to display the finally measured blood sugar value on the display unit. Hereinafter, an operation of the control unit 500 of the blood glucose measurement apparatus according to the present invention will be described in detail with reference to FIG. 4.

4 is a flowchart sequentially illustrating operations of a control unit of a blood glucose measurement apparatus.

Referring to FIG. 4, first, a biosensor is inspected to perform an operation after the biosensor is inserted (step 500). Here, the control unit detects a short circuit of the switch located in the biosensor insertion unit in the blood glucose measurement apparatus, and determines that the biosensor is inserted into the apparatus when the input power drops to 0 Volt by the short circuit of the switch.

When the insertion of the biosensor is detected, the controller switches the operation mode to the enzyme reaction result detection mode of the sample and supplies power to the working electrode lead of the biosensor (step 520).

On the other hand, when a sample is injected into the sample inlet of the biosensor, the sample reaches the reference electrode via the working electrode, and at this time, an electric current flows between the working electrode and the reference electrode by the enzymatic reaction.

The current flowing through the working electrode of the biosensor flows into the blood glucose measurement apparatus through the working electrode lead, is converted into a voltage in the form of a digital signal through an amplifier and an A / D converter, and transmitted to the controller. Accordingly, the controller detects the voltage value and detects the amount of current at the working electrode of the biosensor using the detected voltage value (step 520).

Next, time counting is performed from the moment when the amount of current in the working electrode is detected (step 530). This is for counting the time until a change in resistance at the auxiliary electrode is sensed, and the counted time value can be used to determine whether the sample is injected abnormally.

Next, the resistance between the reference electrode and the auxiliary electrode is measured (step 540).

If it is determined that an error has occurred by checking the reaction time of the working electrode and the change value of the resistance, it indicates that the error state is displayed through the display unit and ends (step 560). If it is determined that it is normal, after a predetermined incubation time, the amount of current in the working electrode lead is detected (step 570), the blood sugar value is calculated according to the detected amount of current (step 580), and the measured resistance value And calculating a correction value according to the temperature (step 590). After correcting the blood glucose value using the correction value, the corrected blood sugar value is displayed on the display unit and then terminated (step 570). In this case, the incubation time is to make the reaction on the electrode uniform, but it is not necessarily required.

Although the present invention has been described above with reference to preferred embodiments thereof, this is merely an example and is not intended to limit the present invention, and those skilled in the art do not depart from the essential characteristics of the present invention. It will be appreciated that various modifications and applications which are not illustrated above in the scope are possible. And differences relating to such modifications and applications should be construed as being included in the scope of the invention defined in the appended claims.

By the air discharge layer and the air discharge passage of the biosensor according to the present invention, it is possible to quickly discharge the air generated in the enzyme reaction layer during the sample injection of the biosensor of the blood glucose measurement system. As a result, the sample can be injected rapidly into the enzyme reaction layer, and as a result, the measurement result can be obtained quickly.

Claims (6)

In the biosensor for measuring blood glucose, which generates and outputs an electrical signal for measuring blood glucose from an externally injected sample, Dielectric substrate, An electrode part formed on a predetermined region of an upper portion of the insulating substrate, the electrode part comprising a working electrode, a reference electrode, and an auxiliary electrode; A lead terminal portion including a working electrode lead, a reference electrode lead, and an auxiliary electrode lead connected to each electrode of the electrode portion; An insulating layer disposed on the electrode part and the lead terminal part to electrically insulate the electrodes and the lead terminals, and having an exposed groove exposing a part of the electrode part; An enzymatic reaction layer formed on an upper portion of a corresponding region of an electrode portion exposed by an exposure groove of the insulating layer, and including an substance causing an electrochemical reaction with a sample; A spacer disposed on the insulation layer and the enzyme reaction layer and having a sample injection hole formed at the same position as the exposed groove of the insulation layer; An air exhaust layer disposed on an upper portion of the spacer and having an air exhaust passage connecting an opposite edge from an edge of one side; A cover part disposed on the air exhaust layer The air discharge passage of the air discharge layer is disposed in the same line as the longitudinal direction of the sample inlet of the spacer, so that the discharge direction of the air and the injection direction of the sample is the same, thereby increasing the suction rate of the sample. Biosensor for measuring blood glucose, characterized in that to enable. The blood glucose measurement biosensor according to claim 1, wherein one end of the air discharge passage of the air discharge layer protrudes from the distal end of the sample inlet.  In the biosensor for measuring blood glucose, which generates and outputs an electrical signal for measuring blood glucose from a sample injected from the outside, Dielectric substrate, An electrode part formed on a predetermined region of an upper portion of the insulating substrate, the electrode part comprising a working electrode, a reference electrode, and an auxiliary electrode; A lead terminal portion including a working electrode lead, a reference electrode lead, and an auxiliary electrode lead connected to each electrode of the electrode portion; An insulating layer disposed on the electrode part and the lead terminal part to electrically insulate the electrodes and the lead terminals, and having an exposed groove exposing a part of the electrode part; An enzymatic reaction layer formed on an upper portion of a corresponding region of an electrode portion exposed by an exposure groove of the insulating layer, and including an substance causing an electrochemical reaction with a sample; It is disposed on the insulating layer and the enzyme reaction layer, and formed in the sample injection port formed in the same position as the exposed groove of the insulating layer, the air discharge passage for discharging the air generated from the sample injection port and the air discharge passage A spacer having an air outlet, A cover part disposed on the spacer The air discharge passage of the spacer is arranged on the same line as the longitudinal direction of the sample inlet of the spacer, but arranged to be spaced apart a predetermined distance, so that the discharge direction of the air and the injection direction of the sample is the same, the suction of the sample Biosensor for blood glucose measurement, characterized in that the speed can be improved. The blood sugar of claim 3, wherein the cover part further includes a protrusion to be in close contact with the air discharge passage of the spacer, and the protrusion is formed on a portion of the sample inlet and an upper portion of the air discharge passage. Biosensor for measurement. The biosensor for measuring blood glucose according to claim 3, wherein one end of the protrusion formed on the cover part protrudes from the distal end of the sample inlet. In the blood glucose measurement method using the biosensor having the structure of claim 1, (a) measuring the resistance between the reference electrode and the auxiliary electrode after sample injection; (b) counting a time from the moment the current amount is detected at the working electrode until the change of the resistance between the reference electrode and the auxiliary electrode is detected; (c) determining whether the sample is injected abnormally according to the time counted in step (b); (d) detecting an amount of current at the working electrode and measuring a blood glucose level using the detected amount of current; (e) correcting the measured blood glucose value according to the measured resistance value between the reference electrode and the auxiliary electrode.

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