KR101103682B1 - Biosensor - Google Patents

Abstract

The present invention relates to a biosensor, and more particularly, an enzyme reaction layer and an upper cover are stacked on a substrate on which an electrode is formed, and a blood supply layer is inserted between the enzyme reaction layer and the upper cover, and the blood supply layer is in a longitudinal direction. By allowing the blood to penetrate and react through the blood injection grooves formed in the blood, the amount of blood is uniformly introduced to measure blood glucose easily and accurately, and by forming the enzyme reaction layer in the width direction, in the state of attaching a plurality of sensors It is an object of the present invention to provide a biosensor capable of manufacturing the reaction part continuously in the width direction at once.

To this end, the present invention is a substrate formed with a plurality of electrodes in parallel on the upper surface; A main reaction layer formed in the width direction on the electrode of the substrate; A blood supply layer having a blood injection groove formed in a longitudinal direction to supply blood to the main reaction layer; And an upper cover covering the upper portion of the blood injection groove, wherein the main reaction layer, the blood supply layer, and the upper cover are sequentially stacked on the substrate, and the blood is sucked through the blood injection groove, It provides a biosensor characterized by measuring the amount of current generated by the reaction.

Blood sugar, cover, enzyme, current, biosensor, cholesterol, blood, electrode

Description

Bio-sensor

The present invention relates to a biosensor, and more particularly, to a biosensor capable of measuring blood glucose easily and accurately.

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.

In the case of insulin-dependent patients who need to measure blood glucose in real time 2-3 times a day, the fingertip is usually pierced with a needle-shaped lancet, and the blood glucose measuring device takes a sample from the patient and collects the sample (blood ) Using a strip-type biosensor to measure the blood glucose value by using an electrical signal generated by the electrochemical reaction with the chemicals 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 the 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.

On the other hand, the conventional porous enzyme reaction layer is formed on the electrode, and provides a biosensor consisting of a fixed frame and a cover for fixing it. The biosensor having this structure drops blood in the reaction layer to test blood glucose.

However, in the case of the biosensor, the amount of blood sample introduced into the reaction layer is changed according to the amount of blood dropped, thereby causing a measurement error according to the amount of blood during the blood sugar test.

In addition, although recently developed by the method of inhalation by injecting into the blood injection groove, it is produced by dropping the reaction reagent in the dot method in the manufacturing process of the sensor, there is a problem that the error of the reaction reagent fixation between the sensors occurs.

In this conventional manufacturing method, a structure in which the reaction reagent layers for measuring a plurality of test substances are independently fixed in one sensor and measured through a single sample inlet cannot be manufactured.

The present invention has been made in view of the above, the stack of the enzyme reaction layer and the upper cover on the substrate on which the electrode is formed, inserting a blood supply layer between the enzyme reaction layer and the upper cover, length in the blood supply layer By allowing the blood to penetrate and react through the blood injection groove formed in the direction, the amount of blood is uniformly introduced to measure the blood sugar easily and accurately, and by forming the enzyme reaction layer in the width direction, It is an object of the present invention to provide a biosensor capable of manufacturing the reaction part continuously in the width direction at once.

In addition, the present invention can form the electrode on the back of the substrate to determine whether the sensor is inserted, give a different code to each sensor according to the shape of the electrode, the code recognition electrode is inserted into the insertion space of the blood glucose measurement apparatus The corresponding code is assigned according to the shape of the electrode, so that the corresponding code is determined according to the error of the blood glucose measurement value, and the blood glucose measurement device recognizes and corrects the correction value corresponding to the corresponding code, thereby minimizing the measurement error. Another purpose is to provide a sensor.

The above object in the biosensor,

A substrate having a plurality of electrodes arranged in parallel on an upper surface thereof; A main reaction layer formed in the width direction on the electrode of the substrate; A blood supply layer having a blood injection groove formed in a length direction to supply blood to the main reaction layer; And an upper cover covering the upper portion of the blood injection groove, wherein the main reaction layer, the blood supply layer, and the upper cover are sequentially stacked on the substrate, and the blood is sucked through the blood injection groove, It is achieved by a biosensor characterized by measuring the amount of current generated by the reaction.

The apparatus may further include at least one extended reaction layer formed in parallel with the main reaction layer at regular intervals in a rearward direction of the main reaction layer to measure a plurality of measurement target substances in blood. It is characterized in that it is formed in communication with the main reaction layer and the expansion reaction layer.

Preferably, the number of the electrode is characterized in that it increases in proportion to the type of the object to be measured using blood.

According to one embodiment of the invention, the electrode is characterized in that the first reference electrode and the first working electrode to measure the amount of current generated by the reaction of the blood and the main reaction layer.

According to another embodiment of the present invention, the electrode is a second working electrode shorter than the first working electrode corresponding to the position of the extended reaction layer to measure the amount of current generated by the reaction of the blood and the expansion reaction layer The apparatus further includes blood by using the first reference electrode in common and subtracting the amount of current measured through the first reference electrode and the second working electrode from the amount of current measured through the first reference electrode and the first working electrode. The amount of current generated by the reaction of the main reaction layer is measured, and the amount of current generated by the reaction of the blood and the expansion type reaction layer is measured through the first reference electrode and the second working electrode.

According to another embodiment of the present invention, the electrode is a second working electrode shorter than the first working electrode corresponding to the position of the extended reaction layer to measure the amount of current generated by the reaction of the blood and the expansion reaction layer And a first insulating layer formed on the first reference electrode corresponding to the position of the extended reaction layer to insulate the first working electrode from the extended reaction layer, and using the first reference electrode in common. Measure the amount of current generated by the reaction between the blood and the main reaction layer through the reference electrode and the first working electrode, and measure the amount of current generated by the reaction between the blood and the extended reaction layer through the first reference electrode and the second working electrode. Characterized in that.

According to another embodiment of the present invention, the electrode is shorter than the first reference electrode and the first working electrode corresponding to the position of the extended reaction layer to measure the amount of current generated by the blood and the expanded reaction layer And a second insulating film formed on the second reference electrode and the second working electrode, the first reference electrode and the first working electrode corresponding to the extended reaction layer to insulate the first reference electrode and the first working electrode from the extended reaction layer. And measuring the amount of current generated by the blood and the main reaction layer through the first reference electrode and the first working electrode, and the amount of current generated by the blood and the extended reaction layer through the second reference electrode and the second working electrode. It characterized by measuring the.

In particular, according to an embodiment of the present invention, the main reaction layer is a first enzyme reaction layer containing glucose oxidase and an electron acceptor to measure blood glucose in the blood, and is generated by the reaction of the blood glucose and glucose oxidase It is characterized by obtaining the blood sugar value by measuring the amount of current.

According to another embodiment of the present invention, the extended reaction layer is characterized in that the second enzyme reaction layer containing cholesterol degrading enzymes to measure cholesterol in the blood.

The notch part is formed at the front end of the upper cover and the blood supply layer to prevent the inlet of the blood injection groove from being blocked when the body part contacts.

According to one embodiment of the invention, the upper cover is characterized in that the blood inlet is formed for injecting blood.

On the other hand, another aspect of the present invention is to form a different shape of the electrode on the lower surface of the substrate to determine whether the sensor is inserted or not, and to give a different code to each sensor according to the shape of the electrode Provide a sensor.

According to an embodiment of the present invention, each sensor forms a code recognition electrode having a different shape according to an error of a blood glucose measurement value, and gives a different code to each sensor, and predetermined correction according to each code It is characterized by assigning a value to each sensor to correct the measured value.

According to another embodiment of the present invention, the code recognition electrode is characterized in that the pattern is patterned, the substrate is punched so as to correspond to the shape of the patterned code recognition electrode.

As described above, according to the biosensor according to the present invention, since the blood injection groove is formed in the longitudinal direction at the end of the blood supply layer, the subject of the sensor is inserted into the blood glucose measurement apparatus in the longitudinal direction. The other end can be easily brought to the blood has the advantage of easy blood supply.

In addition, by forming an enzyme reaction layer in the width direction below the blood supply layer so as to communicate with the blood injection groove of the blood supply layer, by making the enzyme reaction layer at a time in the state arranged so that the longitudinal surfaces of the sensor to stick to each other, to produce a sensor This saves you money and time.

In addition, after determining the measurement error for each sensor, by forming an electrode having a different shape on the back of the substrate according to the error, to determine the code according to the shape of the electrode, by varying the correction value according to the corresponding code, When inserted into the measuring device recognizes the code corresponding to each sensor, and by correcting the measured value with the correction value corresponding to the code, it is possible to measure blood glucose more accurately.

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings.

1 is an exploded view illustrating a biosensor according to an exemplary embodiment of the present invention, and FIG. 2 is an assembly view of FIG. 1.

The biosensor according to an embodiment of the present invention includes a substrate 15 having electrodes 16a and 16b formed on an upper surface thereof, an enzyme reaction layer 13 stacked on an upper portion of the substrate 15, and a blood injection groove 12 at one end thereof. ) Includes the blood supply layer 11 and the upper cover 10 formed in the longitudinal direction. At this time, the enzyme reaction layer 13 according to an embodiment of the present invention is a blood glucose measurement enzyme reaction layer 13 for measuring blood glucose in blood.

The substrate 15 is a base substrate for forming a sensor on an upper surface, and is formed using a polymer resin of a non-conductive material.

The electrodes 16a and 16b formed on the substrate 15 are composed of a working electrode 16a and a reference electrode 16b, and the enzyme with the blood glucose in the sample in the enzyme reaction layer 13. Detect the electrical signal generated by the reaction.

The other ends of the electrodes 16a and 16b are disposed in an area adjacent to the edge of the upper surface of the substrate 15 and are inserted into the insertion space of the blood glucose measurement apparatus and electrically connected thereto.

The electrodes 16a and 16b may be formed by using a mixture of platinum (Pt), gold (Au), silver (Ag), silver and silver chloride (Ag / AgCl), etching using a conductive carbon paste, screen printing, and sputtering. It can form by a method.

The type of enzyme reaction layer 13 can be changed depending on the object to be measured. In the case of measuring cholesterol, alcohol, lactate, and the like in blood, cholesterol enzymes, alcoholases, lactate degrading enzymes can be measured by applying the enzyme reaction layer 13. In addition, by applying an oxidoreductase capable of redoxing the analyte to the enzyme reaction layer 13, the analyte in the blood can be quantified.

The enzyme reaction layer 13 is located between the short first insulating layer 14a and the long second insulating layer 14b, and the first insulating layer 14a and the second insulating layer 14b are It is formed on the electrodes 16a and 16b and insulates the adjacent electrodes 16a and 16b.

An air discharge passage 17 is formed between the enzyme reaction layer 13 and the blood supply layer 11. That is, the heights of the enzyme reaction layer are at both sides of the first insulating layer 14a and the second insulating layer 14b. Since it is formed lower than the), when the blood is supplied from the blood supply layer 11 by collecting the internal air already filled in the blood injection groove 12 to be described later through the air discharge passage 17, collected from the subject The blood can be easily sucked through the blood injection groove (12).

The insulating material used for the first insulating layer 14a and the second insulating layer 14b may be formed by stacking a polymer film, or the insulating materials may be formed using a conventional method such as screen printing. .

Here, the present invention by attaching a plurality of sensors to each other in the longitudinal plane, and then applying a reagent containing a glucose oxidase and an electron acceptor on the substrate 15 in the width direction, to produce a number of enzyme reaction layer 13 at a time As a result, the cost and time required to manufacture the sensor can be reduced.

The enzyme reaction layer 13 is formed on the upper surface of the substrate 15 and includes glucose oxidase, and an electron acceptor that mediates electron transfer. Specifically, the enzyme reaction layer 13 is a solution prepared by mixing a water-soluble polymer, glucose oxidase, stabilizer, electron acceptor, etc. in a predetermined ratio in the electrolyte solution between the first and second insulating layers (14a, 14b) It may be formed by coating a certain amount and then drying.

In addition, the present invention provides a blood supply layer (11) stacked between the enzyme reaction layer (13) and the top cover (10). One end of the blood supply layer 11 is formed with a blood injection groove 12 that can supply blood.

At this time, the blood supply layer 11 has a very thin thickness so that the blood is sucked by the capillary phenomenon as soon as the contact with the blood injection groove 12, the blood injection groove 12 is the blood is the enzyme reaction layer ( 13) is installed in communication with the upper portion of the enzyme reaction layer (13) to react with. In addition, the upper cover 10 is laminated on the upper surface of the blood supply layer 11 to cover the blood injection groove 12 of the blood supply layer (11).

Referring to the measuring method and principle of the biosensor according to an embodiment of the present invention by such a configuration as follows.

Blood collected from the fingertip of the subject is injected through the blood injection groove 12, the blood is diffused into the enzyme reaction layer 13 by the capillary phenomenon in the blood injection groove (12). At this time, the enzyme reaction layer 13 dissolves blood and glucose in the blood is oxidized by the glucose oxidase contained in the enzyme reaction layer 13, and the glucose oxidase is reduced.

The reduced glucose oxidase is then oxidized through a redox reaction with the electron acceptor, and the electron acceptor is reduced. The reduced electron acceptor thus formed is diffused to the surfaces of the electrodes 16a and 16b, and the current generated by applying an oxidation potential to the reduced electron acceptor is measured. In this case, since glucose in the blood is proportional to the amount of current generated in the process of oxidizing the electron acceptor, blood glucose may be measured by measuring the amount of current.

The blood glucose measurement apparatus receives the current generated by the redox reaction of glucose in the blood with the glucose oxidase and the electron acceptor through an electrode, converts the current into a concentration value, and then quantitatively measures the concentration of glucose in the blood, that is, the blood glucose value. Can be calculated.

3A to 3C are exploded views illustrating a biosensor according to another exemplary embodiment of the present invention, and FIGS. 4A to 4C are assembled views of each of FIGS. 3A to 3C.

Another embodiment of the present invention provides a biosensor capable of simultaneously measuring two or more substances to be measured in blood. For example, the first enzyme reaction layer 23a for measuring blood sugar and the second enzyme reaction layer 23b for measuring cholesterol in blood may be included.

The biosensor includes a substrate 15 having electrodes 16a and 16b formed thereon, a first enzyme reaction layer 23a for glucose measurement, a second enzyme reaction layer 23b for cholesterol measurement, and a blood supply layer on the substrate 15. 21 and the upper cover 20 are laminated.

At this time, the blood injection groove 22 formed in the blood supply layer 21 extends in the longitudinal direction from one end of the blood supply layer 21 to the upper portion of the second enzyme reaction layer 23b for cholesterol measurement. In addition, the first enzyme reaction layer 23a is positioned between the first insulation layer 24a and the second insulation layer 24b, and the second enzyme reaction layer 23b is the second insulation layer 24b and the third insulation layer. It is located between the insulating layers 24c.

Here, in the substrate 15 according to an embodiment of the present invention, one first reference electrode 16b and two first and second working electrodes 16a and 16a 'commonly used as shown in FIG. 3A are used. ) Is formed. In this case, the first working electrode 16a is formed such that an electrode top surface spans both the first enzyme reaction layer 23a and the second enzyme reaction layer 23b, and the second working electrode 16a 'has an electrode top surface. It is formed short so as to span only the two enzyme reaction layer 23b.

The amount of current generated by the reaction between the first enzyme reaction layer 23a for blood glucose measurement and the blood is transmitted to the blood glucose measurement apparatus through the first working electrode 16a and the first reference electrode 16b, and the second for cholesterol measurement. The amount of current generated by the reaction between the enzyme reaction layer 23b and the blood is transmitted to the cholesterol measuring device through the second working electrode 16a 'and the first reference electrode 16b.

In this case, since the first reference electrode 16b is commonly used, the voltage applied to the first working electrode 16a and the second working electrode 16b is the same, and the first working electrode 16a is the first enzyme. Since it is formed to span both the reaction layer 23a and the second enzyme reaction layer 23b, the blood glucose measurement apparatus uses the second working electrode at the amount of current transmitted through the first working electrode 16a and the first reference electrode 16b. The blood glucose value is obtained by measuring the amount of current generated by the reaction between the first enzyme reaction layer 23a and the blood by subtracting the amount of current transmitted through the 16a 'and the first reference electrode 16b.

{Current amount generated by the reaction of the first enzyme reaction layer 23a with blood} = {current amount transmitted through the first working electrode 16a and the first reference electrode 16b}-{second working electrode 16a ') And the amount of current transmitted through the first reference electrode 16b}

In addition, the cholesterol measuring device may receive the amount of current through the second working electrode 16a 'and the first reference electrode 16b to measure the amount of current generated by the reaction of the second enzyme reaction layer 23b with blood. The cholesterol value is obtained from this amount of current.

At this time, the number of electrodes increases in proportion to the type of the measurement object.

As shown in FIG. 3B, one first reference electrode 16b and two first and second working electrodes 16a and 16a 'are commonly formed on a substrate according to another embodiment of the present invention. In this case, the first working electrode 16a is formed such that an electrode top surface spans both the first enzyme reaction layer 23a and the second enzyme reaction layer 23b, and the second working electrode 16a 'has an electrode top surface. It is formed short so as to span only the two-enzyme reaction layer 23b.

However, as the first insulating film 19a is formed on the first working electrode 16a of the substrate shown in FIG. 3B, the current generated by the reaction between the second enzyme reaction layer 23b and the blood is the first insulating film. It is blocked by 19a and cannot flow to the first working electrode 16a.

Therefore, the blood glucose measurement apparatus may receive the current amount through the first working electrode 16a and the first reference electrode 16b and measure the amount of current generated by the reaction between the first enzyme reaction layer 23a and the blood, The blood glucose value can be obtained from this amount of current. In addition, the cholesterol measuring device may receive the amount of current through the second working electrode 16a 'and the first reference electrode 16b to measure the amount of current generated by the reaction of the second enzyme reaction layer 23b with blood. The cholesterol value is obtained from this amount of current.

As shown in FIG. 3C, the substrate according to another embodiment of the present invention includes a first reference electrode 16b and a first working electrode 16a, a second reference electrode 16b ', and a second working electrode 16a. ') Is formed. In this case, the first reference electrode 16b and the first working electrode 16a are formed such that an upper surface of the electrode covers both the first enzyme reaction layer 23a and the second enzyme reaction layer 23b, and the second reference electrode ( 16b ') and the second working electrode 16a' are formed to be short so that the upper surface of the electrode only covers the second enzyme reaction layer 23b.

However, as the second insulating film 19b is formed on the first reference electrode 16b and the first working electrode 16a of the substrate shown in FIG. 3c, the second enzyme reaction layer 23b reacts with the blood. The generated current is blocked by the second insulating film 19b to prevent flow to the first reference electrode 16b and the first working electrode 16a.

Therefore, the blood glucose measurement apparatus may receive the amount of current through the first reference electrode 16b and the first working electrode 16a and measure the amount of current generated by the reaction between the first enzyme reaction layer 23a and the blood. The blood glucose value can be obtained from this amount of current. In addition, the cholesterol measuring device may receive the amount of current through the second working electrode 16a 'and the second reference electrode 16b' and measure the amount of current generated by the reaction between the second enzyme reaction layer 23b and the blood. The cholesterol value is obtained from this amount of current.

Here, the substrate shown in FIGS. 3A and 3B uses the same first reference electrode 16b, and thus can be used when the reaction conditions and reaction time for measuring blood glucose and cholesterol are the same, and the substrate shown in FIG. 3C. Since the first and second reference electrodes 16b and 16b 'are used as many as the number corresponding to the type of object to be measured, they may be used even when the reaction conditions and reaction time for measuring blood glucose and cholesterol are different.

5 is an exploded view showing a biosensor according to another embodiment of the present invention, and FIG. 6 is an assembled view of FIG. 5.

Another embodiment of the present invention is a notch portion 33 around the inlet to prevent the inlet is blocked when the body part (for example the end of the finger) is contacted when the blood is injected through the blood injection groove 32 Provided is a biosensor formed.

7 to 9 are diagrams showing the shape of the code recognition electrode and the substrate formed in different shapes in accordance with the present invention, Figures 10 to 12 is a pattern of only the code recognition electrode in accordance with the present invention It is a block diagram showing.

On the other hand, the biosensor determines whether the blood glucose measurement is accurate or the error range for each sensor (50 to 52) in the normal production process. Accordingly, in the present invention, electrodes 53 to 55 are provided on the bottom surface of the substrate 15 to give a code so as to give a correction value for each sensor to correct the error according to the range of the error.

For example, when the blood glucose reference value is 100, a code A is assigned when the measured value of the first sensor 50 is 100, and 10 (corrected value) to make 100 when the measured value of the second sensor 51 is 90. Code B is added to add, and if the measured value of the third sensor 52 is 110, code C is assigned to subtract 10 to make 100.

In this way, in order to give a code to each sensor 50 to 52, the shape of the electrodes 53 to 55 corresponding to each cord is determined, and the corresponding electrodes 53 to 55 are formed on the rear surface of the substrate 15. The shapes of the electrodes 53 to 55 may be determined differently according to codes and correction values.

In addition, when the sensors 50 to 52 having different shapes of electrodes 53 to 55 are inserted into the sockets connected to the blood glucose measurement apparatus, the terminals 18a to 18c installed inside the sockets have different shapes of electrodes ( 53 to 55) by code, the blood glucose measurement apparatus corrects the measured value with a correction value corresponding to each code.

At this time, the plurality of terminals 18a to 18c are each numbered, and each terminal is turned on and off according to the shape of each electrode 53 to 55.

For example, in the case of the first sensor 50 having an A code, an off signal is transmitted to the first terminal 18a and an on signal to the second and third terminals 18b and 18c.

In the case of the second sensor 51 to which the B code is assigned, the on signal is transmitted to the first and second terminals 18a and 18b and the off signal to the third terminal 18c.

In the case of the third sensor 52 to which the C code is assigned, the on signal is transmitted to the first and third terminals 18a and 18c and the off signal to the second terminal 18b.

When the sensors 50 to 52 having different codes are inserted into the insertion unit of the blood glucose measurement device as described above, the blood glucose measurement device assigns and corrects a predetermined correction value according to each code to each sensor 50 to 52. The blood sugar level can be measured accurately.

Here, the shapes of the electrodes 53 to 55 may be formed in various forms according to the number of terminals, and for example, the terminals or electrodes 53 to 55 may be patterned in a straight line (FIGS. 7 to 9) or a zigzag pattern. Can be mad.

In addition, in order to recognize the codes of the sensors 50 to 52, the substrates 15 are punched (FIGS. 7 to 9) or patterns only corresponding to the electrodes 53 to 55 and the shapes of the electrodes. 10 to 12, since the blood glucose measurement apparatus gives a correction value according to the characteristics of the sensors 50 to 52 (error of blood glucose measurement value) through a plurality of terminals (for example, three or four), Blood glucose can be measured accurately.

FIG. 13 is an exploded view showing a biosensor according to another embodiment of the present invention, and FIG. 14 is an assembled view of FIG. 13.

In the upper cover 40 according to another embodiment of the present invention, a blood inlet 40a is formed. As described above, in order to measure blood glucose, the subject's fingertip is pierced with a lancet, and blood is collected. When blood is injected through the blood injection groove 42 as shown in FIG. 1, a small amount of blood is collected at the end of the finger. It is not easy to inject blood by contacting the end of).

This is because, when the blood of the subject is injected while the biosensor is kept horizontal, the blood formed at the tip of the finger may flow down by gravity. In addition, when injecting the subject's blood while the finger is turned upside down to prevent blood from flowing down by gravity, the blood injection groove 42 of the biosensor is tilted toward the blood. From the standpoint, the blood injection groove 12 is upwardly inclined so that the blood is not easily penetrated inward. In addition, keeping the biosensor horizontal, it is more difficult to bring the tip of the finger so that blood does not flow.

However, in the present invention, the blood inlet 40a may be formed in the upper cover 40 to easily inject blood. The blood injection hole 40a is formed to penetrate adjacent to one end of the upper cover 40, and the blood injection groove 42 is formed long in the inner longitudinal direction at a portion adjacent to one end of the blood supply layer 41. Therefore, the subject pierced the end of the finger with the lancet with the palms facing upward, and then flipped the finger to contact the blood inlet 40a formed in the upper cover 40 with the blood. It can be injected easily.

15A to 15C are exploded views illustrating a biosensor according to another embodiment of the present invention, and FIGS. 16A to 16C are assembled views of each of FIGS. 15A to 15C.

The configuration and operation of the electrodes in FIG. 3A are similar in that one common first reference electrode 16b and two first and second working electrodes 16a and 16b 'are formed on the substrate shown in FIG. 15A. In addition, a blood injection hole 40a is formed in the middle of the upper cover 40 of FIG. 15A, and the blood injection hole 40a is formed to fall slightly from one end of the blood supply layer 41 so that the first and second enzymatic reactions are performed. 3A is different in that blood is supplied to the layers 153a and 153b. In this case, since the blood injection hole 150a is formed in the middle of the upper cover 150 in FIG. 15A, blood may be injected more easily.

One common first reference electrode 16b and two first and second working electrodes 16a and 16a 'are formed on the substrate shown in FIG. 15B, and a first insulating film (1) is formed on the first working electrode 16a. 19a), the configuration and function of the electrode in FIG. 3b are similar, but the blood inlet 150a is formed in the middle of the upper cover of FIG. 15b, and the blood inlet 150a is the blood supply layer 151. There is a difference from FIG. 3b in that blood is supplied to the first and second enzyme reaction layers 153a and 153b by being slightly separated from one end of the. In this case, since the blood injection hole 150a is formed in the middle of the upper cover 150 in FIG. 15B, blood may be injected more easily.

Two first and second reference electrodes 16b and 16b 'and two first and second working electrodes 16a and 16a' are formed on the substrate shown in FIG. 15C, and the first reference electrode 16b is formed. And in that the second insulating film 19a is formed on the first working electrode (16a) is similar to the configuration and operation of the electrode in Figure 3c, the blood injection hole 150a is formed through the middle of the upper cover of Figure 15c The blood injection hole 150a is formed to be slightly separated from one end of the blood supply layer 151, and thus, blood is supplied to the first and second enzyme reaction layers 153a and 153b. In this case, since the blood injection hole 150a is formed in the middle of the upper cover 150 in FIG. 15C, blood may be injected more easily.

While the invention has been shown and described with respect to certain preferred embodiments, the invention is not limited to these embodiments, and those of ordinary skill in the art claim the invention as claimed in the claims It includes all the various forms of embodiments that can be carried out without departing from the spirit.

1 is an exploded view showing a biosensor according to an embodiment of the present invention.

FIG. 2 is an assembly view of FIG. 1.

3A-3C are exploded views showing various embodiments of electrodes formed on the substrate of the present invention.

4A to 4C are assembled views of each of FIGS. 3A to 3C.

5 is an exploded view showing a biosensor according to another embodiment of the present invention.

6 is an assembly view of FIG. 5.

7 to 9 is a block diagram showing the shape of the code recognition electrode and the substrate formed in different shapes in accordance with the present invention.

10 to 12 is a configuration diagram showing a pattern patterned only the code recognition electrode in accordance with the present invention.

13 is an exploded view showing a biosensor according to another embodiment of the present invention.

14 is an assembly view of FIG. 13.

15A-15C are exploded views showing various embodiments of electrodes formed on the substrate of the present invention.

16A to 16C are assembled views of each of FIGS. 15A to 15C.

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

10,20,30,40,150: upper cover 11,21,31.41,151: blood supply layer

12,22,32,42,152: blood injection groove 13,43: enzyme reaction layer

23a, 153a: first enzyme reaction layer 23b, 153b: second enzyme reaction layer

14a, 24a, 154a: first insulating layer 14b, 24b, 154b: second insulating layer

24c and 154c: third insulating layer 15: substrate

16a: first working electrode 16a ': second working electrode

16b: first reference electrode 16b ': second reference electrode

17: air discharge passage 18a: first terminal

18b: second terminal 18c: third terminal

19a: first insulating film 19b: second insulating film

33: notch 40a, 150a: blood inlet

50 to 52: first to third sensors

53-55: electrode

Claims (14)

In the biosensor, A substrate having a plurality of electrodes arranged in parallel on an upper surface thereof; A main reaction layer formed in the width direction on the electrode of the substrate; A blood supply layer having a blood injection groove formed in a longitudinal direction to supply blood to the main reaction layer; And an upper cover covering the upper portion of the blood injection groove, wherein the main reaction layer, the blood supply layer, and the upper cover are sequentially stacked on the substrate, and the blood is sucked through the blood injection groove, Biosensor, characterized in that for measuring the amount of current generated by the reaction. The method according to claim 1, The main reaction layer further includes at least one extended reaction layer formed in parallel with the main reaction layer at regular intervals in the rear direction to measure a plurality of measurement target substances in the blood, and the blood injection groove has a main reaction. Biosensor, characterized in that formed in communication with the layer and the expandable reaction layer. The method according to claim 1, The number of the electrode is a biosensor, characterized in that to increase in proportion to the type of the object to be measured using blood. The method according to claim 1, The electrode is a biosensor comprising a first reference electrode and a first working electrode for measuring the amount of current generated by the reaction of the blood and the main reaction layer. The method according to claim 4, The electrode further includes a second working electrode having a shorter length than the first working electrode to correspond to the position of the extended reaction layer to measure the amount of current generated by the reaction of the blood and the extended reaction layer, wherein the first reference electrode Is used in common, and the amount of current measured through the first reference electrode and the second working electrode is subtracted from the amount of current measured through the first reference electrode and the first working electrode. And measuring the amount of current and measuring the amount of current generated by the reaction between the blood and the expanded reaction layer through the first reference electrode and the second working electrode. The method according to claim 4, The electrode includes a second working electrode having a shorter length than the first working electrode and corresponding to the position of the extended reaction layer to measure the amount of current generated by the reaction between the blood and the expanded reaction layer, and the extended reaction with the first reference electrode. And a first insulating layer formed to correspond to the position of the layer to insulate the first working electrode from the extended reaction layer, wherein the first reference electrode is used in common and blood is formed through the first reference electrode and the first working electrode. And measuring the amount of current generated by the reaction of the main reaction layer, and measuring the amount of current generated by the reaction of the blood and the expanded reaction layer through the first reference electrode and the second working electrode. The method according to claim 4, The electrode includes a second reference electrode and a second working electrode having a shorter length than the first reference electrode and the first working electrode so as to correspond to the position of the extended reaction layer to measure the amount of current generated by the blood and the extended reaction layer; And a second insulating layer formed on the first reference electrode and the first working electrode to correspond to the extended reaction layer to insulate the first reference electrode and the first working electrode from the extended reaction layer. 1. The biosensor, which measures the amount of current generated by the blood and the main reaction layer through the working electrode, and measures the amount of current generated by the blood and the extended reaction layer through the second reference electrode and the second working electrode. The method according to any one of claims 1 to 7, The main reaction layer is a first enzyme reaction layer including glucose oxidase and an electron acceptor to measure blood glucose in blood, and obtains a blood glucose value by measuring an amount of current generated by the reaction of the blood glucose and glucose oxidase. Biosensor. The method according to any one of claims 2 and 5 to 7, The extended reaction layer is a biosensor, characterized in that the second enzyme reaction layer containing cholesterol degrading enzymes to measure cholesterol in the blood. The method according to claim 1, Biosensor characterized in that the notch portion is formed at the front end of the upper cover and the blood supply layer to prevent the inlet of the blood injection groove when the body portion is in contact. The method according to claim 1, According to the characteristics of each sensor on the lower surface of the substrate it is possible to determine whether the sensor is inserted or not, the biosensor, characterized in that to give a different code to each sensor according to the shape of the electrode. The method of claim 11, Each sensor forms a code recognition electrode having a different shape according to an error of a blood glucose measurement value, assigns a different code to each sensor, and assigns a predetermined correction value to each sensor according to each code to measure the measured value. Biosensor, characterized in that to correct. The method of claim 11, The electrode is patterned in shape, the biosensor characterized in that the substrate is punched to correspond to the shape of the patterned electrode. The method according to claim 1, Biosensor, characterized in that the upper cover is formed with a blood inlet for injecting blood.

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