KR20220008423A - Patch type biosensor - Google Patents

Abstract

The present invention relates to a biosensor. The biosensor comprises: a first basic material unit; a second basic material unit formed on the first basic material unit; a third basic material unit formed on the second basic material unit; a chamber in which a reaction of a sample occurs; and a first sample inflow unit in which the sample flows. The first sample inflow unit is provided on a lower surface of the first basic material unit. A width of the first sample inflow unit is 0.1 to 1 mm.

Description

Patch type biosensor

The present invention relates to a patch type biosensor.

The biosensor reacts a target substance to be analyzed with a bio-receptor with selection specificity, measures the degree of the reaction with a signal transducer, and the presence of the analyte It refers to a device or element that can confirm the quantity.

Biosensors are classified into electrochemical sensors, thermal sensors, and optical sensors according to their conversion methods. Recently, depending on the type of target material to be analyzed, glucose sensors, cell sensors, immune biosensors, DNA chips, etc. are variously named as

Among them, the electrochemical sensor is widely used as a conversion method of the biosensor to date in that it is possible to convert the amount of a biological sample into an electrical signal that is easy to process information.

Patent Registration No. 10-0887632 Also, an electrochemical sensor using blood as a sample, avoiding interference with various blood types, and providing a biosensor that can measure accurately and conveniently.

However, most conventional biosensors as well as the biosensor of Patent No. 10-0887632 collect a sample containing an analyte to be analyzed from the analyte, and inject it into the sensor to measure an electrochemical signal. In this method, the analyte is analyzed, but in this method, there is a disadvantage in that a sample must be artificially collected from the analyte, and in that the analysis of the sample is one-time, it is continuously included in the sample. The disadvantage is that the analyte cannot be measured.

Therefore, it is necessary to develop a biosensor capable of analyzing an analyte by continuously acquiring a sample without artificially collecting a sample.

Registered Patent No. 10-0887632

An object of the present invention is to provide a patch type biosensor.

In addition, an object of the present invention is to provide a biosensor capable of continuous measurement through continuous inflow and outflow of a sample.

The present invention, the first base unit; a second base part formed on the first base part; a third base part formed on the second base part; a chamber in which the reaction of the sample occurs; A biosensor including a first sample inlet through which a sample is introduced, wherein the first sample inlet is provided on a lower surface of the first base part, and the width of the first sample inlet is 100 to 1,000 µm. is about

According to the first aspect of the present invention, the chamber may be formed in the second base unit.

According to the second aspect of the present invention, the height of the chamber may be 50 to 1,000 μm.

In the third aspect of the present invention, the second base unit includes a second sample inlet formed at a position corresponding to the first sample inlet, and a channel connecting the second sample inlet and a chamber (channel) may be further included.

According to the fourth aspect of the present invention, the width of the channel may be 100 to 1,000 μm.

According to the fifth aspect of the present invention, the chamber may be directly connected to the first sample inlet.

According to the sixth aspect of the present invention, the first sample inlet may be one or more.

In the seventh aspect, the present invention may include a first electrode part and a second electrode part formed between the first base part and the second base part.

The present invention, in the eighth aspect, the first base part and the third base part are each independently glass, polyethersulfone (PES), polymethyl (meth)acrylate (PMMA), polycarbonate (PC), Polyethylene (PE), polyethylene naphthalate (PEN), polyphenylene sulfide (PPS), polypropylene (PP), triacetyl cellulose (TAC), cellulose acetate propionate (CAP), polyethylene terephthalate (PET) From the group consisting of imide (PI), polyetherimide (PEI), polyamide (PA), cycloolefin polymer (COP), cycloolefin copolymer (COC), PMMA/PC copolymer and PMMA/PC/PMMA copolymer It may be to include one or more selected.

In the present invention, in the ninth aspect, the second base part may be prepared from a pressure sensitive adhesive (PSA) composition or an optical clear adhesive (OCA) composition.

In the tenth aspect, the present invention may further include a fourth base part on the lower surface of the first base part.

In the eleventh aspect of the present invention, the fourth base unit may include a third sample inlet formed at a position corresponding to the first sample inlet formed on the lower surface of the first base unit.

In the twelfth aspect, the present invention may further include a first sample discharging unit through which the introduced sample is discharged to the outside.

According to the thirteenth aspect of the present invention, the first sample discharging unit may be formed in a third base unit.

According to the fourteenth aspect of the present invention, the width of the first sample outlet may be 100 to 1,000 μm.

The biosensor according to the embodiments of the present invention is a patch type biosensor, and by appropriately adjusting the thickness of the base part, the number and width of the sample inlet and the sample outlet, the sample can be obtained without a separate device. It is possible to improve the inconvenience of artificially collecting a sample from an analyte.

In addition, according to the biosensor according to the present invention, it is possible to continuously measure the analyte contained in the sample through continuous inflow and outflow of the sample.

1 is an exploded perspective view showing a biosensor according to an embodiment of the present invention.
FIG. 2 is a cross-sectional view of the biosensor of FIG. 1 .
3 is a perspective view illustrating a first base unit included in a biosensor according to one or more embodiments of the present invention.
4 is a perspective view illustrating a second base unit included in a biosensor according to one or more embodiments of the present invention.
5 is a perspective view illustrating a third base unit included in a biosensor according to an embodiment of the present invention.
6 is a perspective view illustrating a fourth base unit included in a biosensor according to one or more embodiments of the present invention.

In the present invention, when a biosensor is manufactured in a patch type, the sample is continuously introduced and discharged by the pressure generated by the sample without artificially collecting the sample from the analyte, so that the analysis included in the sample It was focused on being able to measure an analyte continuously, and it relates to a patch-type biosensor.

More specifically, the present invention, the first base unit; a second base part formed on the first base part; a third base part formed on the second base part; a chamber in which the reaction of the sample occurs; A biosensor including a first sample inlet through which a sample is introduced, wherein the first sample inlet is provided on a lower surface of the first substrate, and the width of the first sample inlet is 100 to 1,000 μm.

By manufacturing a patch-type biosensor having a microfluidics structure as described above, the sample can be effectively introduced into the biosensor without generating air bubbles.

Hereinafter, embodiments of the present invention will be described in more detail with reference to the drawings. However, the following drawings attached to the present specification illustrate preferred embodiments of the present invention, and serve to further understand the technical spirit of the present invention together with the above-described content of the present invention, so the present invention is described in such drawings It should not be construed as being limited only to the matters.

<Biosensor>

1 is an exploded perspective view showing a biosensor according to an embodiment of the present invention. FIG. 2 is a cross-sectional view of the biosensor shown in FIG. 1 .

Referring to FIGS. 1 and 2 , the biosensor includes a first base unit 10 , a first sample inlet unit 11 provided on a lower surface of the first base unit 10 and into which a sample is introduced, and A chamber 22 in which the reaction takes place, a second substrate portion 20 formed on the first substrate portion 10, and a third substrate portion 30 formed on the second substrate portion 20. it could be

3 is a perspective view illustrating the first base unit 10 included in the biosensor according to exemplary embodiments.

In an embodiment, the thickness of the first base unit 10 may be 100 to 1,000 μm.

Referring to FIG. 3 , the first base unit 10 may include a first sample inlet 11 formed on the lower surface of the first base unit 10 and penetrating the first base unit 10 . have.

In one embodiment, the first sample inlet 11 may be singular as shown in FIG. 3A .

In some embodiments, there may be a plurality of first sample inlets 11 , and for example, as shown in FIG. 3B , may include three first sample inlets 11 . In this case, when the sample is introduced and moved into the biosensor, bubbles may not be generated, and the sample may be quickly introduced into the chamber 22 .

In an embodiment, the width of the first sample inlet 11 may be 100 to 1,000 μm, preferably, 150 to 600 μm, and more preferably, 200 to 400 μm. . In this case, by the pressure of the sample secreted from the analyte, the sample can be smoothly introduced and moved into the biosensor without a separate device, so that bubbles may not be generated inside the biosensor.

4 is a perspective view showing the second base unit 20 included in the biosensor according to example embodiments.

In an embodiment, the second base unit 20 may be provided as a base layer on which a chamber 22 is formed.

In an embodiment, the second base unit 20 is positioned between the first base unit 10 and the third base unit 30, and may be provided as an adhesive surface, for example, an adhesive and the like, and preferably, may be prepared from a pressure sensitive adhesive (PSA) composition or an optical clear adhesive (OCA) composition.

The chamber 22 may be provided as a space in which a reaction of the introduced sample occurs, and in one embodiment, as shown in FIG. 4A , the second sample inlet 21 and the second sample outlet It may include a part 24 and be connected to the second sample inlet 21 and the second sample outlet 24 by a channel 23 .

In an embodiment, the height of the chamber 22 may be 50 to 1,000 μm, preferably, 50 to 500 μm, and more preferably, 100 to 300 μm. In this case, it is possible to prevent a decrease in the rate at which the sample is filled inside the chamber 22, reduce the minimum amount of sample for measurement, and suppress the generation of bubbles in the process of filling the sample. .

The second sample inlet 21 may be formed at a position corresponding to the first sample inlet 11 to provide a space into which the sample supplied from the first sample inlet 11 is introduced.

In one or a plurality of embodiments, the width of the second sample inlet 21 may be 100 to 1,000 μm, preferably, 150 to 600 μm, and more preferably, 200 to 400 μm. can be

In this case, the inflow and movement of the sample is smooth, and bubbles may not be generated when the sample is introduced into the biosensor and the sample is moved inside the biosensor.

In one embodiment, as shown in FIG. 4A , it may include a single second sample inlet 21 corresponding to the single first sample inlet 11 .

In some embodiments, the second sample inlet 21 may be plural, for example, as shown in FIG. 4B , three first sample inlets 11 formed in the first base unit 10 . ) may be to include three second sample inlet 21 corresponding to. In this case, by receiving the samples from the plurality of first sample inlets 11 , the samples can be quickly supplied to the chamber 22 , and when the samples are introduced and moved in the chamber 22 , Bubbles may not be generated.

The channel 23 guides the sample supplied from the second sample inlet 21 to the chamber 22 , and guides the sample discharged from the chamber to the second sample outlet 24 . May be provided as a guide.

In an embodiment, the width of the channel 23 may be 100 to 1,000 μm, preferably, 150 to 600 μm, and more preferably, 200 to 400 μm. In this case, the movement of the sample is smooth, and bubbles may not be generated when the sample is moved inside the biosensor.

The second sample discharge unit 24 may be provided as a space through which the sample discharged from the chamber 22 is guided by the channel 23 and discharged.

In an embodiment, the second sample discharge unit 24 may include a single second sample discharge unit 24 as shown in FIGS. 4A and 4B . However, the number of the second sample discharging units 24 is not particularly limited, and the user can appropriately select the number of the second sample discharging units 24 in order to adjust the appropriate inflow and outflow of the sample. can

In an embodiment, the width of the second sample discharge unit 24 may be 100 to 1,000 μm, preferably, 150 to 600 μm, and more preferably, 200 to 400 μm. . In this case, the inflow and outflow of the sample in the chamber 22 is smooth, so that when the sample is moved inside the biosensor, bubbles may not be generated.

In some embodiments, the chamber 22 includes a second sample inlet 21 , a second sample outlet 24 and a channel 23 as shown in FIG. 4C . Without it, it may be integrally formed.

In this case, the first sample inlet 11 is directly connected to the chamber 22 to supply the sample to the chamber 22 .

The biosensor of the present invention may include a first electrode part 12 and a second electrode part 13 constituting an electrode part for measuring an electrical signal by reaction of a sample.

In one embodiment, the first electrode part 12 and the second electrode part 13 may be formed on the upper surface of the first base part 10 , and preferably, the second base part 20 . It may be formed on the upper surface of the first base unit 10 in the region corresponding to the region in which the chamber 22 is provided.

In an embodiment, the first electrode unit 12 may be a working electrode, and the second electrode unit 13 may be a reference electrode.

The first electrode part 12 constituting the working electrode is an electrode that reacts with a sample, and may be provided as an electrode that allows a current to flow during the electrode reaction.

In one or more embodiments, the first electrode part 12 constituting the working electrode may include gold (Au); silver (Ag); copper (Cu); platinum (Pt); titanium (Ti); nickel (Ni); tin (Sn); molybdenum (Mo); palladium (Pd); cobalt (Co); and alloys thereof; pyrolytic graphite; Glassy carbon (galssy carbon); carbon paste; perfluorocarbon (PFC); And at least one selected from the group consisting of carbon nanotubes (CNT), etc. may be used, but carbon paste is preferable in consideration of ease of manufacture, excellent reproducibility, and a wide potential window in the oxidation/reduction direction. do. The above materials may be used alone, but are not limited thereto, and may be used as a multi-layer film by using two or more materials.

The second electrode part 13 constituting the reference electrode has a constant potential and may be provided as a reference electrode for obtaining the generated potential of the working electrode.

In one or more embodiments, the second electrode unit 13 constituting the reference electrode includes a silver-silver chloride (Ag/AgCl) electrode, a calomel electrode, and a mercury-mercury sulfate electrode. , and at least one selected from the group consisting of a mercury-oxide mercury electrode, etc., has less hysteresis of the potential with respect to a temperature cycle, and is stable up to a high temperature. -A silver chloride (Ag/AgCl) electrode is preferable. In some embodiments, the carbon paste used for the first electrode part 12 constituting the above-described working electrode may be used in the same manner.

In some embodiments, in addition to the first electrode part 12 and the second electrode part 13, a third electrode part (not shown) to an electrode protective layer may be further included.

The third electrode unit may be a counter electrode, and may serve as an electrode that transmits or receives a current so that a reaction occurs on the surface of the working electrode.

In one or a plurality of embodiments, all materials described in the first electrode part 12 and the second electrode part 13 may be used for the third electrode part constituting the counter electrode, and the process is simplified. And it is preferable to use the same material as the first electrode part 12 and/or the second electrode part 13 in order to improve the manufacturing cost.

The working electrode constituting the first electrode unit 12 , the reference electrode constituting the second electrode unit 13 , and the counter electrode constituting the third electrode unit may be manufactured by a conventional manufacturing method. In one or a plurality of embodiments, screen printing, letterpress printing, engraving printing, lithography, and photolithography (photolithography) may be performed including one or more processes selected from the group consisting of. In one embodiment, it is preferable to perform a photolithography process to form the wiring part, and each electrode is performed by any one selected from the group consisting of screen printing, letterpress printing, engraving printing, and lithographic printing. may be, preferably screen printing.

5 is a perspective view illustrating the third base unit 30 included in the biosensor according to exemplary embodiments.

In an embodiment, the third base unit 30 includes a second sample inlet 21 , a chamber 22 , a channel 23 , and a second sample inlet formed in the second base unit 20 . 2 It may be provided as a cover of the biosensor while blocking the sample discharge unit 24 from the outside.

In an embodiment, the thickness of the third base unit 30 may be 100 to 1,000 μm.

Referring to FIG. 5 , the third base part 30 may include a first sample discharge part 31 formed on the lower surface of the third base part 30 and penetrating the third base part 30 . have.

In one embodiment, the first sample discharge unit 31 is formed at a position corresponding to the second sample discharge unit 24 formed in the second base unit 20 , and is discharged from the second sample discharge unit 24 . The discharged sample may be provided as a passage through which the discharged sample is discharged to the outside.

In one or a plurality of embodiments, the width of the first sample outlet 31 may be 100 to 1,000 μm, preferably, 150 to 600 μm, more preferably, 200 to 400 μm can be In this case, the movement and discharge of the sample inside the biosensor may be smooth, and bubbles may not be generated.

In one embodiment, as shown in FIG. 5 , the first sample discharging unit 31 includes a single number of first sample discharging units 31 corresponding to the single second sample discharging units 24 . can However, the number of the first sample discharging unit 31 is not particularly limited, and in order to adjust the proper inflow and outflow of the sample, the user can appropriately select a plurality of second samples provided in the second base unit 20 . It may include a plurality of first sample discharging units 31 corresponding to the sample discharging unit 24 .

In one or more embodiments, the first base part 10 and the third base part 30 are not particularly limited, but, for example, each independently glass, polyethersulfone (PES), polymethyl ( Meth)acrylate (PMMA), polycarbonate (PC), polyethylene (PE), polyethylene naphthalate (PEN), polyphenylene sulfide (PPS), polypropylene (PP), triacetyl cellulose (TAC), cellulose acetate pro Cypionate (CAP), polyethylene terephthalate (PET), polyimide (PI), polyetherimide (PEI), polyamide (PA), cycloolefin polymer (COP), cycloolefin copolymer (COC), PMMA/PC It may include one or more selected from the group consisting of a copolymer and a PMMA/PC/PMMA copolymer.

In an embodiment, the first base unit 10 and the third base unit 30 may be manufactured using the same material, and in this case, process simplification and manufacturing cost improvement are possible.

In some embodiments, the biosensor may further include a fourth substrate unit 40 on a lower surface of the first substrate unit 10 .

6 is a perspective view illustrating a fourth base unit 40 included in a biosensor according to example embodiments.

In an embodiment, the thickness of the fourth base unit 40 may be 50 to 1,000 μm.

In one embodiment, the fourth base unit 40 is positioned between the patch type biosensor and the analysis target, and may be provided as an adhesive surface, for example, may be an adhesive, etc. , Preferably, it may be prepared from a pressure sensitive adhesive (PSA) composition or an optical clear adhesive (OCA) composition.

In an embodiment, the fourth base unit 40 includes a third sample inlet 41 formed at a position corresponding to the first sample inlet 11 formed on the lower surface of the first base unit 10 . Thus, the sample generated from the analysis target may be provided as a guide for guiding the sample to the first sample inlet 11 through the third sample inlet 41 .

In one embodiment, as shown in FIG. 6A , it may include a single third sample inlet 41 corresponding to the single first sample inlet 11 .

In some embodiments, the third sample inlet 41 may be plural, for example, as shown in FIG. 6B , three first sample inlets 11 formed in the first base unit 10 . ), it may be to include three third sample inlet 41 . In this case, by guiding the sample to the plurality of first sample inlets 11 , bubbles may not be generated when the sample is introduced and moved into the biosensor, and the sample is quickly introduced into the chamber 22 . can do it

In an embodiment, the width of the third sample inlet 41 may be 100 to 3,000 μm.

In one or a plurality of embodiments, the sample containing the analyte to be analyzed may be a liquid sample, for example, a biological sample such as blood, body fluid, urine, saliva, tears, sweat, etc. , but is not limited thereto.

In one or a plurality of embodiments, the analyte to be analyzed may be, for example, glucose, lactate, cholesterol, vitamin C (ascorbic acid), alcohol, various cations, and various anions. However, the present invention is not limited thereto.

<Measuring method of electrochemical signal>

The present invention includes a method for measuring an electrochemical signal of an analyte included in a sample using the biosensor. According to the electrochemical signal measuring method of the present invention, it is possible to obtain a sample even if the sample is not artificially collected from the analyte, and continuous measurement of the analyte included in the sample is possible due to the continuous inflow and discharge of the sample. It is possible.

This is due to the microfluidics structure using the pressure generated when the sample is secreted from the analyte, and unlike the capillary action that occurs even in a capillary without specific restrictions, the table of contents <Biosensor> It can be achieved through appropriate adjustment of the number, width, thickness, etc. of each of the base parts, the sample inlet, and the sample outlet described in .

In this specification, "measuring electrochemically" means measuring by applying an electrochemical measurement method. In one or more embodiments, an electric current measurement method, a potentiometric method, a coulometric analysis method, etc. are mentioned, Preferably it may be an electric current measurement method.

Hereinafter, the method for measuring an electrochemical signal of an analyte of the present invention will be described in more detail with reference to the drawings. However, it is as described above that the interpretation is not limited only to the matters described in the drawings.

Referring to FIGS. 1 and 2 , the fourth substrate 40 constituting the lowermost layer of the patch-type biosensor may be attached to an analysis target, and is preferably attached to a point at which a sample is secreted. In one embodiment, the biosensor of the present invention is for measuring glucose contained in sweat, and may be attached to the upper arm.

A portion of the sample secreted by the pressure of the sample secreted from the analyte is provided in the first base unit 10 through the third sample inlet 41 provided on the lower surface of the fourth base unit 40 . It is guided to the first sample inlet (11).

The sample guided to the first sample inlet 11 is guided to the second sample inlet 21 formed in the second base unit 20 , and is guided by a channel 23 , to a chamber ) moves to (22).

The sample moved to the chamber 22 fills the chamber 22 and moves toward the second sample outlet 24 . At this time, the analyte included in the sample reacts with the receptor formed in the first electrode part 12 constituting the working electrode, thereby generating an electrical change.

A voltage is applied to an electrode unit including the first electrode unit 12 and the second electrode unit 13 to measure a response current emitted in response to the electrical change, and based on the response current value, An electrochemical signal of the analyte is calculated.

The applied voltage is not particularly limited, but in one or a plurality of embodiments, it may be -500 to +500 mV, preferably -200 to +200 mV, based on the silver-silver chloride electrode (Ag/AgCl electrode). .

In the method for measuring an electrochemical signal of a detection target substance of the present disclosure, in other embodiments, after contacting with the reagent and maintaining the non-applied state for a predetermined time, a voltage may be applied to the electrode, or A voltage may be applied to the electrode portion simultaneously with the contact.

Thereafter, the sample after the reaction with the first electrode unit 12 is guided to the second sample discharge unit 24 by a channel 23 , and the first sample discharge formed in the third base unit 30 . It is discharged through the section (31).

According to the biosensor of the present invention, the above series of processes does not occur singly, but continuously flows in and out of the sample due to the pressure of the sample secreted from the analyte. It is possible to measure the analyte.

<Electrochemical signal measurement system>

The present invention provides an electrochemical signal of an analyte in a sample, comprising the biosensor, a means for applying a voltage to an electrode part of the biosensor, and a means for measuring a current in the electrode part and an electrochemical signal measuring system for measuring. According to the electrochemical signal measuring method of the present invention, it is possible to obtain a sample even if the sample is not artificially collected from the analyte, and continuous measurement of the analyte included in the sample is possible due to the continuous inflow and discharge of the sample. It is possible.

The application means is not particularly limited as long as it conducts with the electrode portion of the biosensor and can apply a voltage, and a known application means can be used. The application means may include, in one or more embodiments, a contact capable of contacting the electrode portion of the biosensor, and a power source such as a DC power supply.

The measuring means is for measuring a plurality of currents in the electrode part generated at the time of voltage application, and in one or a plurality of embodiments, measures a response current value correlating with the amount of electrons emitted from the electrode part of the biosensor As long as it is possible, the one used as a conventional or later developed biosensor may be used.

Hereinafter, examples of the present invention will be specifically described. However, the present invention is not limited to the embodiments disclosed below, but may be implemented in various different forms, and only these embodiments allow the disclosure of the present invention to be complete, and common knowledge in the art to which the present invention pertains It is provided to fully inform those who have the scope of the invention, and the present invention is only defined by the scope of the claims. Like reference numerals refer to like elements throughout.

The terminology used herein is for the purpose of describing the embodiments, and is not intended to limit the present invention. In this specification, the singular also includes the plural unless specifically stated otherwise in the phrase.

As used herein, includes and/or comprising refers to the presence or addition of one or more other components, steps, operations and/or elements other than the recited elements, steps, operations and/or elements. It is used in the sense of not being excluded.

Hereinafter, preferred embodiments of the present invention will be described in detail.

<Examples and Comparative Examples>

With reference to Table 1, biosensors corresponding to Examples and Comparative Examples were prepared.

A first sample inlet for guiding the inflow of the sample was formed by using a laser cutter on the PET film constituting the first substrate.

In addition, using carbon paste and silver paste, the working electrode and the reference electrode were respectively printed by screen printing to correspond to the position of the chamber provided in the second base unit.

A second sample inlet, a chamber, and a second sample outlet were formed on the OCA film constituting the second substrate in the same manner as above.

The first sample discharging unit was formed on the PET film constituting the third base unit in the same manner as above.

A third sample inlet was formed on the OCA film constituting the fourth substrate in the same manner as above.

A biosensor was manufactured by attaching and stacking each of the sample inlet and the sample outlet formed in the first to fourth base parts to correspond to each other.

<Experimental example>

The following evaluation was performed with the biosensors prepared in Examples and Comparative Examples, and a fluid containing a dye was used so that the movement of the fluid introduced into the biosensor could be easily recognized by the naked eye.

The fluid containing the dye was injected into the third sample inlet part of the fourth base part to evaluate whether the fluid was injected, the injection speed of the fluid, and the bubble generation rate inside the chamber when the injection was completed, and the results are shown in Table 1 below .

In order to shorten the measurement time of the biosensor, it is preferable that the injection speed of the fluid is fast, and in order to obtain an accurate measurement result, it is preferable that the bubble generation rate inside the chamber is low.

It can be seen that the biosensors of Examples 1 to 5 have superior injection rates and lower bubble generation rates than those of Comparative Examples 1 and 2.

However, as in Comparative Example 1, when the width of the first sample inlet is less than 100 µm, the injection speed is lowered and the bubble generation rate is increased, and as in Comparative Example 2, the width of the first sample inlet is more than 1000 µm In this case, the bubble generation rate is very high, indicating that the measurement time is shortened and it is difficult to use as a biosensor for obtaining accurate measurement results.

10: first base unit
11: first sample inlet
12: working electrode
13: reference electrode
20: second base unit
21: second sample inlet
22: chamber
23: channel
24: second sample discharge unit
30: 3rd base department
31: first sample discharge unit
40: fourth base unit
41: third sample inlet

Claims (15)

a first base unit;
a second base part formed on the first base part;
a third base part formed on the second base part;
a chamber in which the reaction of the sample occurs;
A biosensor including a first sample inlet into which a sample is introduced,
The first sample inlet is provided on the lower surface of the first substrate,
The width of the first sample inlet is 100 to 1,000㎛, characterized in that the biosensor.
The biosensor according to claim 1, wherein the chamber is formed in the second base part.
The method according to claim 1, The height of the chamber (chamber) characterized in that formed to be 50 to 1,000㎛, the biosensor.
The method according to claim 2, wherein the second base unit further comprises a second sample inlet formed at a position corresponding to the first sample inlet, and a channel connecting the second sample inlet and a chamber. Characterized in that, the biosensor.
The biosensor of claim 4, wherein the channel has a width of 100 to 1,000 μm.
The biosensor of claim 2, wherein the chamber is directly connected to the first sample inlet.
The biosensor of claim 1, wherein the first sample inlet is at least one.
The biosensor of claim 1, further comprising a first electrode part and a second electrode part formed between the first base part and the second base part.
The method according to claim 1, wherein the first base part and the third base part are each independently glass, polyethersulfone (PES), polymethyl (meth)acrylate (PMMA), polycarbonate (PC), polyethylene (PE), polyethylene Naphthalate (PEN), polyphenylene sulfide (PPS), polypropylene (PP), triacetyl cellulose (TAC), cellulose acetate propionate (CAP), polyethylene terephthalate (PET), polyimide (PI), poly At least one selected from the group consisting of etherimide (PEI), polyamide (PA), cycloolefin polymer (COP), cycloolefin copolymer (COC), PMMA/PC copolymer, and PMMA/PC/PMMA copolymer A biosensor comprising:
The biosensor of claim 1, wherein the second base part is made from a pressure sensitive adhesive (PSA) composition or an optical clear adhesive (OCA) composition.
The biosensor of claim 1, further comprising a fourth base part on a lower surface of the first base part.
The biosensor of claim 11 , wherein the fourth base unit comprises a third sample inlet formed at a position corresponding to the first sample inlet formed on a lower surface of the first base unit.
The biosensor according to claim 1, further comprising a first sample outlet through which the introduced sample is discharged to the outside.
The biosensor of claim 13, wherein the first sample discharging unit is formed in the third base unit.
The biosensor of claim 13, wherein the width of the first sample outlet is 100 to 1,000 μm.

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