KR100586828B1 - Biosensor improved the absorption speed of sample liquid - Google Patents

Abstract

The present invention relates to a biosensor which improves the sample suction rate, and the air is external to the sample when the sample is sucked into the enzyme reaction layer through an air discharge tunnel formed in the cover at the end of the enzyme reaction layer injection port in a direction perpendicular to the direction of injection of the enzyme reaction layer. It is possible to improve the sample suction speed of the biosensor by implementing a very effective discharge, and minimize the possibility of sample leakage and contamination of the enzyme reaction layer.

Biosensor, sample, enzyme reaction, oxidation current

Description

Biosensor improved the absorption speed of sample liquid}

1 is an exploded perspective view of a biosensor with improved sample suction rate according to the present invention;

2 is a plan view of a biosensor with improved sample suction rate according to the present invention;

<Explanation of symbols for the main parts of the drawings>

100: biosensor 110: insulating substrate

120: conductive layer 121: lead wire

122 electrode 130 dielectric layer

131: exposure groove 140: enzyme reaction layer

150: spacer 151: injection hole

160: cover 161: air discharge tunnel

162: sample injection groove

The present invention relates to a biosensor with improved sample inhalation rate, and in particular, an improved structure for improving sample inhalation rate of a biosensor such as a disposable blood glucose sensor that can quickly and easily measure blood glucose levels contained in blood. Relates to a biosensor.

Biosensors, such as blood glucose measurement sensors, which are essential for the early detection and control of glucose absorption during the treatment of diabetics, typically form an electrode system including a plurality of electrodes on an insulating substrate by screen printing, and the like. An enzymatic reaction layer consisting of a hydrophilic polymer, an oxidoreductase, and an electron acceptor is formed on the system.

When the sample containing the substrate is dropped in the enzyme reaction layer of the biosensor, the enzyme reaction layer dissolves it and the substrate and the enzyme (Enzyme) react to oxidize the substrate, thereby reducing the electron acceptor.

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

However, the measurement time in the biosensor depends on how quickly the sample is sucked into the enzyme reaction layer, and the suction rate of the enzyme reaction layer of the sample depends on how fast the air of the enzyme reaction layer escapes and how much of the enzyme reaction layer is released. It depends on how short and small the volume is.

The biosensor presented in the patent application No. 2001-40690 (Jul. 07, 2001) filed by the applicant of the present invention forms an outlet in a direction perpendicular to the enzyme reaction layer by separating the resin plate (spacer), This releases air to the outside.

In addition, the biosensor presented in the patent application No. 2002-59612 (September 30, 2002) filed by the applicant of the present invention is a slit in a direction parallel to the enzyme reaction layer from the curved groove for sample injection formed on the cover. To form air through the air.

In the case of the biosensor proposed in the above-mentioned patent application 2001-40690 (2001. 07. 07), the air inlet of the enzymatic reaction layer and the air outlet are discharged in a 'T' shape. Since this is achieved through the enzyme reaction layer, the air discharge rate depends on the injection rate of the sample, so that the sample suction rate is slow, and for the rapid sample suction rate, the outlet must be large, so that the amount of the sample has to be increased.

On the other hand, the method of discharging air to the outside through the groove formed in the cover as shown in Patent Application No. 2002-59612 (September 30, 2002) is likely to contaminate the enzyme reaction layer, It is more likely to flow through the grooves and get on the hands, the amount of sample to be sucked is not constant, and because the grooves can not be largely enlarged to minimize contamination of the enzyme reaction layer, the sample suction speed is slow.

Therefore, the present inventors follow the method of discharging the air to the outside through the outlet formed in the cover in a direction perpendicular to the enzyme reaction layer so that the suction rate of the enzyme reaction layer of the sample is excellent, but the spacer is not separated to configure the sensor The research has been conducted on biosensors that can eliminate the inconvenience.

The present invention has been invented under the above-mentioned purpose, and can efficiently discharge air to the outside to improve the sample suction rate, less likely to contaminate the enzyme reaction layer, and remove the sample to the hand when removing the strip after measurement. It is an object of the present invention to provide a biosensor that improves the rate of suction of a sample that does not come off.

The biosensor with improved sample suction rate according to the present invention for achieving the above object is an air discharge tunnel formed in a direction perpendicular to the direction in which the enzyme reaction layer is inserted on the cover of the end of the inlet opening into which the enzyme reaction layer is inserted. Characterized in that provided.

Therefore, when the sample is sucked into the enzyme reaction layer through the air discharge tunnel, the air is discharged to the outside very effectively, so that the suction speed is improved, the amount of the sample can be effectively reduced, and the groove is located at the upper part of the cover having a relatively large area than the side. There is no possibility of sample leakage and contamination of the enzyme reaction layer.

Hereinafter, the present invention will be described in detail with reference to the accompanying drawings so that those skilled in the art can easily understand and reproduce the present invention.

1 is an exploded perspective view of a biosensor improving the sample suction rate according to the present invention;

2 is a plan view of a biosensor with improved sample suction rate according to the present invention.

As shown in the figure, the biosensor 100 having an improved sample suction rate according to the present invention includes an insulating substrate 110, a conductive layer 120, a dielectric layer 130, an enzyme reaction layer 140 and And a spacer 150 and a cover 160.

The insulating substrate 110 is a base substrate formed using a material having a material such as non-conductive polyethylene terephthalate (PET).

The conductive layer 120 is a layer in which a lead wire 121 in contact with a measuring device (not shown in the drawing) and an electrode 122 connected to the lead wire 121 but detecting an electrical signal flowing in a sample collected are printed. The upper surface of the insulating substrate 110 is formed.

The arrangement of the lead wire 121 and the electrode 122 is described in Patent Application Nos. 2001-40690 (Jul. 07, 2001) and Patent Application Nos. 2002-59612 (Sep. 30, 2002) filed by the applicant of the present invention. Since it is described in detail in the present invention, a detailed description thereof will be omitted.

The dielectric layer 130 includes an exposed groove 131 for exposing an electrode printed on the conductive layer 120, and simultaneously measures an end portion of the lead wire 121 printed on the conductive layer 120. The end of the lead wire 121 printed on the conductive layer 120 is exposed to a predetermined portion so as to contact the conductive layer 120, and is formed on the conductive layer 120.

That is, the dielectric layer 130 has a function of exposing a part of the lead wire 121 to be partially exposed, and the electrode 122 is exposed to a certain part so that the same area is always used when the oxidation current is generated by contacting the enzyme reaction layer 140. Has the ability to react in

The enzyme reaction layer 140 is a layer for inhaling a sample, and includes a hydrophilic polymer, a redox enzyme, and an electron acceptor. The enzyme reaction layer 140 includes an exposed groove 131 formed in the dielectric layer 130. The electrode 122 of the conductive layer 120 is contacted, and when the sample including the substrate is dropped into the enzyme reaction layer 140, the enzyme reaction layer 140 dissolves it and the substrate and enzyme of the sample (Enzyme). The reaction results in the oxidation of the substrate, thereby reducing the electron acceptor. Substrate contained in the sample by measuring the oxidation current value obtained by electrochemically oxidizing the reduced electron acceptor after the end of the enzymatic reaction through a measuring device (not shown) in contact with the lead wire 121 connected to the electrode 122. Find the concentration.

Since the configuration of the measuring device is described in detail in the invention disclosed in Patent Application No. 2002-59612 (2002. 09. 30) filed by the applicant of the present invention, a detailed description thereof will be omitted.

The spacer 150 has an injection hole 151 into which the enzyme reaction layer 140 is inserted, and is formed on the dielectric layer 130.

The thickness of the spacer 150 should be at least equal to or thicker than the thickness of the enzyme reaction layer 140. The reason for this is to facilitate sample injection when the sample is sucked into the enzyme reaction layer 140. That is, when the thickness of the spacer 150 is larger than the thickness of the enzyme reaction layer 140, sample injection into the free space becomes easy.

The cover 160 is provided with an air discharge tunnel 161 formed at a direction perpendicular to the direction in which the enzyme reaction layer 140 is inserted at the end of the injection hole 151 into which the enzyme reaction layer 140 is inserted. It is formed on the spacer 150.

That is, the air discharge tunnel 161 is formed in a section in which the sample and the enzyme reaction layer 140 cannot exist, through which only air escapes.

In this case, the air discharge tunnel 161 is preferably a semi-cylindrical shape, in addition to that can be implemented in various shapes.

Therefore, when the sample begins to be sucked into the enzyme reaction layer 140 while the enzyme reaction layer 140 is inserted into the injection hole 151 of the spacer 150, air existing around the enzyme reaction layer 140 is It is gradually pushed toward the end of the injection port 151, and the direction in which the enzyme reaction layer 140 is inserted through the air discharge tunnel 161 formed at the end of the injection port 151 into which the enzyme reaction layer 140 is inserted by pressure. Air is discharged to the outside in a vertical direction, and the sample suction rate of the enzyme reaction layer 140 is improved as the air is discharged to the outside.

That is, in the case of the present invention, unlike the conventional techniques, the enzyme reaction layer 140 and the air discharge tunnel 161 through which the air is discharged are formed in different layers, so that the sample is removed when the strip is removed after the measurement. There is little to worry about the amount of sample irrespective of the size of the air discharge tunnel 161 can reduce the amount of sample by the size of the enzyme reaction layer 140, the air discharge tunnel 161 to the size of the enzyme reaction layer 140 It can be increased regardless of the efficient air discharge, and the air discharge occurs without passing through the enzyme reaction layer 140, irrespective of the air discharge rate and the sample injection rate, and thus the movement of the sample air liquid is the movement of air It is much faster, and the air exhaust rate is improved.

On the other hand, according to an additional aspect of the present invention, the cover 160 may be further provided with a sample injection groove 162 at the beginning of the injection hole in which the enzyme reaction layer 140 is inserted to facilitate sample injection. . In this case, the enzyme reaction layer 140 may be contaminated by the sample injection groove 162, but the contamination level may be minimized by making the sample injection groove 162 very small.

On the other hand, according to an additional aspect of the present invention, it is preferable to use a hydrophobic (Hydrophobic) material to prevent the penetration of the hydrophilic (Hydrophilic) sample as an adhesive for bonding the spacer 150 and the cover 160. .

In addition, it is preferable to use a hydrophobic (Hydrophobic) material to prevent the hydrophilic (Hydrophilic) sample from seeping into the adhesive for bonding the spacer 150 and the dielectric layer 130.

In addition, the spacer 150 may be made of a hydrophobic material to prevent the hydrophilic (Hydrophilic) sample from penetrating.

That is, in order to prevent the sample from penetrating outside the enzyme reaction layer 140 when the sample is sucked into the enzyme reaction layer 140, it may interfere with the course of the hydrophilic (Hydrophilic) sample that is sucked into the enzyme reaction layer 140. By using a hydrophobic (Hydrophobic) material to implement the enzyme reaction layer 140 around the sample can be prevented from seeping into / out of the sensor.

Meanwhile, according to an additional aspect of the present invention, the spacer 150 and the cover 160 may have a size similar to that of the dielectric layer 130 so that the ends of the lead wires 121 printed on the conductive layer 120 are exposed. desirable.

That is, as shown in FIG. 2, the spacer 150 adhered to the dielectric layer 130, the dielectric layer 130, and the cover 160 adhered to the spacer 150 to expose the printed lead wire ends. ) Is implemented to be smaller than the length of the conductive layer 120 so that the end of the lead wire 121 printed on the conductive layer 120 is exposed. The exposed end of the lead wire 121 is in contact with a measuring device (not shown in the drawing) during measurement, and the measuring device calculates the concentration of the substrate in the sample according to the magnitude of the oxidation current detected by the electrode 122.

Therefore, it is possible to achieve the object of the biosensor with improved sample suction rate according to the present invention as described above.

As described above, the biosensor with improved sample suction rate according to the present invention is a sample in the enzyme reaction layer through the air discharge tunnel formed in the cover in the direction perpendicular to the enzyme reaction layer injection direction at the end of the enzyme reaction layer injection port. When inhaled, the air is discharged to the outside very effectively to improve the intake rate, and has a useful effect that there is little possibility of sample leakage and contamination of the enzyme reaction layer.

Although the present invention has been described with reference to the accompanying drawings, it will be apparent to those skilled in the art that various modifications may be made therein without departing from the scope of the invention, which is covered by the following claims.

Claims (8)

An insulating substrate; A conductive layer printed with a lead wire in contact with the measuring device and an electrode connected to the lead wire and detecting an electrical signal flowing through a sample taken; A dielectric layer having an exposed groove for exposing the printed electrode on the conductive layer, and at the same time, a portion of the lead wire printed on the conductive layer is partially exposed to contact the measuring device with the lead wire end printed on the conductive layer; ; An enzyme reaction layer for inhaling the sample and reacting with the substrate; A spacer having an injection hole into which the enzyme reaction layer is inserted; A cover having an air discharge tunnel formed at an end of an injection hole into which the enzyme reaction layer is inserted; Biosensor with improved sample suction rate, characterized in that comprises. The method of claim 1, The cover is: A sample injection groove at the inlet of the injection hole into which the enzyme reaction layer is inserted to facilitate sample injection; The biosensor with improved sample suction speed, characterized in that further provided. The method of claim 1 Biosensor improved sample suction rate, characterized in that to use a hydrophobic (Hydrophobic) material to prevent the penetration of the hydrophilic (Hydrophilic) sample as an adhesive for bonding the spacer and the cover. The method of claim 1, And a hydrophobic material for preventing penetration of a hydrophilic sample as an adhesive for bonding the spacer and the dielectric layer. The method of claim 1, Biosensor improved sample intake rate, characterized in that the spacer is a hydrophobic (Hydrophobic) material for preventing the penetration of the sample having a hydrophilic (Hydrophilic). The method of claim 1, And a spacer having a size similar to that of the dielectric layer so that the spacer end printed on the conductive layer is exposed. The method of claim 1, And a cover having a size similar to that of the dielectric layer so that the end of the lead wire printed on the conductive layer is exposed. The method of claim 1, Biosensor with improved sample intake rate, characterized in that the air discharge tunnel is a semi-cylindrical shape formed in a direction perpendicular to the insertion direction of the enzyme reaction layer.

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