KR20150011179A - Bio-sensor - Google Patents

Abstract

The present invention aims to provide a biosensor which can reduce an error range of a detected value by filtering a portion of a solid substance from a sample containing the solid substance such as blood. The biosensor may include: a base substrate having a detection part; an upper plate which is stacked on the base plate and includes a sample inlet through which the sample enters into the detection part; and a filter member which is provided between the upper plate and the base substrate and filtrates the solid substance in a predefined size entering through the sample inlet.

Description

Biosensor {BIO-SENSOR}

The present disclosure relates to a biosensor.

In general, when testing fluid samples for clinical and environmental monitoring, one of the various devices used for sample analysis is a biosensor using electrochemical test sensors. In particular, users with insulin dependence are used to measure the level of glucose in the blood (sample) while carrying the biosensor periodically and self-checking. When a sample is provided with such a biosensor, a sufficient amount of sample must be accurately provided on the detection position so that a reaction can take place on the detection position of the electrode or sensor of the biosensor. A sample inlet portion having a narrow flow path is formed in front of the biosensor so as to introduce the sample into the biosensor and provide the sample to the detection position. As a conventional technique related to the construction of such a biosensor, there has been proposed a method of detecting a biosensor in accordance with the method disclosed in US Patent Publication No. US2008 / 0149480 (Pub. Date: 2008.6.26, entitled GEL FORMATION TO REDUCE HEMATOCRIT SENSITIVITY IN ELECTROCHEMICAL TEST), Korean Patent No. 10-0854389 Date: 2008.08.20, entitled "Electrochemical Biosensor").

As described above, various biosensors are provided for measuring various samples. Among them, a biosensor generally used is a blood glucose meter, which is used to measure a change in blood glucose using a user's blood as a sample. In the case of a biosensor, the biosensor includes a sample inlet portion for introducing the sample and a detection portion for analyzing the introduced sample. The sample inlet uses a capillary phenomenon to allow the sample to flow into the detector. That is, the sample inlet portion provided on the front surface of the biosensor is provided very narrowly to suck blood, and the sample inlet space formed from the sample inlet portion to the detection portion is provided very narrowly to suck the sample into the detection portion.

When a user pierces his or her fingertip with a needle or the like to measure blood sugar, and blood is drawn into the sample inlet of the biosensor, the blood collects in the detection part through the capillary phenomenon, and the blood glucose value of the user is measured will be. Such a detector may be referred to as a blood glucose sensor, and in the case of a blood glucose sensor, a portion for detecting glucose (D-Glucose) may be an enzyme or a non-enzyme type using a transition metal and an oxide. In the case of such a blood glucose sensor, the glucose is oxidized by gluconic acid or the like and the blood glucose value of the user can be known through the detection value of the electric signal obtained through the oxidation.

A sample used to measure blood sugar, blood, is divided into a solid component and a liquid component. The solid component is composed of blood cells, specifically, leukocytes, red blood cells and platelets. The liquid component is composed of plasma. The composition in which blood glucose is measured through the detection part is a liquid component.

Among the solid components of red blood cells, white blood cells and platelets, red blood cells have a largest size of 7 to 10 탆. These red blood cells are stacked on the sample inlet portion of the biosensor and the narrow sample inlet space from the sample inlet portion to the detection portion, or stacked on the detection portion. Particularly, when red blood cells are stacked on the detection part, the liquid component is prevented from contacting the surface of the detection part. That is, when the red blood cells are stacked on the sample inlet and the sample inlet space, the sample inlet and the sample inlet space are narrowed, and when compared with the influx of only the liquid component, the inflow rate is slowed and an error may occur in the blood glucose value .

In particular, when a solid component is laminated on the detection part, the detection area of the detection part is reduced, and the blood component value is measured by the detection area where the liquid component is reduced. In addition, since the content and the size of the solid component contained in the blood, particularly the size of the red blood cell, are different for each user using the biosensor, the error range of the blood glucose value detected even when the same biosensor is used also varies.

Various attempts have been made to reduce the error range of the blood glucose value. For example, it is possible to measure and correct the erythrocyte amount optically using the increase of scattering as the amount of red blood cells increases. In addition, a difference in viscosity or the like occurs depending on the content of the solid component in the blood, and the flow rate of the blood is changed, whereby the content of the solid component is measured by comparing the flow rate in the blood with that in the case of being provided as a pure liquid component . Specifically, it is possible to determine the error and measure the blood glucose level by measuring the flow velocity of the blood using the time difference between the blood flowing between the electrodes located at different places on the basis of the flow direction of the blood flowing into the sample inlet.

In addition, the ratio of the solid component in the blood can be measured by various methods, and the error of the blood glucose value can be determined therefrom. However, in the case of the above examples, specifically, in the case of optically measuring the amount of erythrocytes, various components and circuits are required for application to a biosensor for disposable use, and thus it is difficult to apply. In addition, it is not simple to measure the ratio of the solid component, and the sample varies greatly depending on the friction between the surface of the wall of the sample inlet space and the blood, the boundary condition, etc. in order to flow the sample from the sample inlet to the detection part. Therefore, in the case of the method as in the above example, as the distance between the electrodes for measuring the time difference is very narrow and the average flow rate obtained by the statistical value and the actual flow rate value are deviated, It is difficult to obtain an accurate blood glucose value.

Therefore, it is difficult to actually detect the ratio or size of the solid component, and the error range is widened thereby making it difficult to measure the blood glucose value close to the accuracy.

Therefore, the embodiment of the present disclosure intends to provide a biosensor capable of reducing a range of error of a detection value by filtering a part of a solid component in a sample, particularly a sample containing a solid component such as blood.

According to an aspect of the present invention, there is provided a biosensor comprising: A biosensor comprising: a base substrate having a detection unit; An upper plate laminated on the base substrate and provided with a sample inlet portion through which the sample is introduced into the detection portion; And a filter member provided between the upper plate and the base substrate and filtering a solid component of a predetermined size introduced into the sample inlet.

The biosensor constructed as described above is capable of filtering a solid component having a predetermined size or more through a simple structure to prevent the solid component from being stacked on the flow path between the sample inlet and the detection unit and to be stacked with the detection unit, The blood glucose value can be reduced and the error range of the blood glucose value can be reduced.

In addition, even if the size of the solid component included in the sample is different, the solid component of a predetermined size or more can be filtered, and individual errors of the biosensor can be reduced.

1 is a view illustrating a biosensor according to an embodiment of the present invention.
2 is a view showing that a mesh pattern of a filter member is formed in a plain shape in a biosensor according to an embodiment of the present disclosure shown in Fig.
Fig. 3 is a view showing that a mesh pattern of a filter member is formed in a twill shape in a biosensor according to an embodiment of the present disclosure shown in Fig. 1;
Fig. 4 is a view showing that a mesh pattern of a filter member is formed in a numeric shape in a biosensor according to an embodiment of the present disclosure shown in Fig. 1; Fig.
FIG. 5 is a view showing a state in which a solid component is filtered in a filter member in a biosensor according to an embodiment of the present disclosure shown in FIG. 1; FIG.

Hereinafter, a biosensor according to embodiments of the present disclosure will be described with reference to the accompanying drawings. In this process, the thicknesses of the lines and the sizes of the components shown in the drawings may be exaggerated for clarity and convenience of explanation. Further, the terms described below are defined in consideration of the functions in this disclosure, which may vary depending on the intentions or customs of the user, the operator. Therefore, definitions of these terms should be made based on the contents throughout this specification.

Further, in describing the embodiments of the present disclosure, ordinal numbers such as 1, 2, and so on are used, but they are for distinguishing objects of the same name from each other, and the order may be arbitrarily set, Of the present invention may be applied mutatis mutandis.

The biosensor 100 according to one embodiment of the present disclosure is a biosensor according to an embodiment of the present invention that includes a solid component such as blood to prevent a solid component from being stacked on the detection part 111, Lt; / RTI > To this end, the biosensor 100 of the present disclosure will be described with reference to FIGS. 1 to 6. FIG.

1 is a view illustrating a biosensor according to an embodiment of the present invention. 1, a biosensor 100 according to an embodiment of the present disclosure includes a base substrate 110, an insulating layer 120, a top plate 130, and a filter member 140 to be. The base substrate 110 is disposed on the lowermost side of the biosensor 100. An insulating layer 120 and an upper plate 130 are stacked in this order on the upper side of the base substrate 110 and on the upper side of the insulating layer 120. The upper plate 130 is connected to the sample inlet The filter member 140 is laminated on the side of the filter member 132a.

The base substrate 110 of the present disclosure may include a non-conductive material such as a ceramic, a glass plate, or a polymer resin, and may be formed of an organic polymer material such as polyester, polyvinyl chloride, and polycarbonate It can also be used. However, the material of the base substrate 110 is not limited to this, and can be changed or modified in consideration of the cost and the configuration of the detection unit 111 and the like provided on the base substrate 110.

The upper surface of the base substrate 110 is provided with a detection unit 111 for detecting information of the sample introduced through the sample inlet 132a of the upper plate 130. The detection unit 111 is formed on the base substrate 110 and may include a lead 111a and an electrode layer 111b. The lead 111a is provided on the front portion F of the base substrate 110 and forms a sample inlet 132a so that the sample introduced through the sample inlet 132a to be described later can be moved to the electrode layer 111b . The lead 111a is provided with an insulating layer 120 on top to prevent the sample from contacting. The electrode layer 111b is provided on the rear portion B of the base substrate 110 and is contacted with the sample to perform a test such as blood glucose analysis on the sample. The electrode layer 111b may include two electrodes, specifically, a first electrode 111ba, which is a working electrode, and a first electrode 111bb, which is an auxiliary electrode. The electrode layer 111b is brought into contact with the sample introduced through the sample inlet 132a to analyze the information of the sample. The first electrode 111ba and the first electrode 111bb are adjacent to each other in the longitudinal direction of the biosensor 100. [ The first electrode 111ba and the second electrode 111bb may be formed on the base substrate 110 by electrodeprinting, screen printing, deposition, etching, or the like.

The insulating layer 120 is provided on the upper surface of the base substrate 110 and is preferably provided on the front surface portion F of the base substrate 110. The insulating layer 120 prevents the sample from contacting the detecting portion 111, specifically, the lead 111a located on the front portion F of the base substrate 110. [ The insulating layer 120 has a hole 120a for connecting a vent hole 131a to be described later and a sample inlet space (hereinafter, referred to as a 'flow path'). When the sample flows into the sample inlet 132a, Allows you to escape the gas filled in the Euro.

The upper plate 130 is positioned at the uppermost position of the biosensor 100 and is overlaid on the upper side of the base substrate 110. In an embodiment of the present disclosure, the top plate 130 may include a lid portion 131 and a sample introduction plate 132. The lid part 131 is overlaid on the upper surface of the sample introduction plate 132 and covers the upper side of the sample inlet 132a formed on one side of the sample introduction plate 132, Thereby forming a space so as to be able to flow through the through holes. A vent hole 131a is formed in the lid part 131. The vent hole 131a is connected to the other end of the sample inlet 132a to discharge the air filled in the flow path so that the sample can be drawn through the capillary phenomenon when the sample flows through one side of the sample inlet 132a .

The sample introduction plate 132 is overlaid on the upper side of the base substrate 110 and a sample inlet 132a through which the sample can flow is formed on one side.

Although the upper plate 130 includes the lid part 131 and the sample introduction plate 132 in the embodiment of the present disclosure, the present invention is not limited thereto. For example, it may be formed of one upper plate 130, or two or more laminated layers may be provided if necessary.

The filter member 140 is provided between the upper plate 130 and the base substrate 110, specifically between the sample introduction plate 132 and the insulating layer 120, and is located above the sample inlet 132a. The filter member 140 is configured to filter solid components of a predetermined size (d) or more contained in the sample entering the sample inlet 132a. That is, when the sample is supplied to the sample inlet 132a, the sample passes through the filter member 140, not directly onto the flow path. Therefore, the solid component of the predetermined size (d) or more contained in the sample is filtered while passing through the filter member 140 before the sample flows into the flow path. In particular, the blood glucose value detected by the biosensor 100 through a sample such as blood is an output obtained by analyzing the liquid component, not by analyzing the solid component. Therefore, as the solid component decreases, accurate numerical values can be obtained. Particularly, the solid component is piled on a narrow flow path to block or slow down the flow of the liquid component, thereby lowering the accuracy of the detection value. The solid component is deposited on the detection part 111 and specifically on the electrode layer 111b as well as being laminated on the flow path so that the area of contact of the liquid component with the electrode layer 111b is reduced or the liquid component is contacted with the electrode layer 111b And the accuracy of the detection value is lowered. The filter member 140 can prevent the flow path from being clogged or accumulated on the electrode layer 111b by filtering all the solid components contained in the sample or solid components having a certain size (d) or more when the sample is introduced.

The filter member 140 includes at least one or more of polyester, nylon, polyethylene, and fluorine resin. In addition, a hydrophilic coating layer can be formed on the surface of the filter member 140, specifically, the warp yarn 141 described later and the surface of the weft 142. The hydrophilic coating layer is formed on the surface of the electrode layer 111b located on the rear portion B of the biosensor 100 so as to facilitate introduction of the liquid sample into the detection portion 111, And the surface of the weft 142 are coated with a hydrophilic material. The term " hydrophilic " means that the liquid can adhere well to the surface of the warp yarns 142 and the warp yarns 141. [ When the sample is supplied to the sample inlet 132a, the solid component is filtered by the filter member 140, and the liquid component does not flow through the capillary phenomenon due to the hydrophilic coating layer provided on the surface of the filter member 140, 142 and the surface of the warp yarn 141 to the detection unit 111 side.

The size d of the opening O formed in the filter member 140 according to the embodiment of the present disclosure may be formed with a size d for filtering a sample, particularly a solid component of a predetermined size d or more in the blood . Specifically, in consideration of the fact that the size d of the solid component contained in the blood, that is, the size of the erythrocyte ranges from 7 to 10 μm, the size of the opening O may be between 10 and 50 μm, So that the intersection of the weft yarns 142 can be formed.

The filter member 140 may be provided with a warp yarn 141 and a weft yarn 142 and may be provided in a mesh pattern in which the warp yarns 141 and the weft yarns 142 alternate with each other.

2 to 4 are views showing various shapes of a mesh pattern of a filter member in a biosensor according to an embodiment of the present disclosure shown in Fig. 1, Fig. 2 shows that a mesh pattern is formed in a plain shape Fig. 3 shows that the mesh pattern is formed into a twill shape, and Fig. 4 shows that the mesh pattern is formed into a water-like shape. Referring to FIGS. 2 to 4, as described above, the filter member 140 crosses the warp yarns 141 and the weft yarns 142 to form a three-dimensional mesh pattern. As shown in FIG. 2, the mesh pattern may be formed in a plain shape in which the warp yarns 141 and the weft yarns 142 are alternately crossed one by one and formed in three dimensions. That is, the warp yarns 141 and the weft yarns 142 are alternately formed one after another. An opening O having a predetermined size d is formed at a portion where the warp yarns 141 and the weft yarns 142 intersect. The sample provided on the sample inlet port 132a is provided as a passage through the filter member 140. The solid component contained in the sample can be passed through the opening O And is filtered by the filter member 140, and the remaining sample is introduced into the flow path through the opening O.

As shown in FIG. 3, the mesh pattern is formed in a twill shape. The warp yarns and the weft yarns alternate with each other to form a three-dimensional shape. The warp yarns 141 or the weft yarns 142 are formed to cross over two or more. Thus, like the plain mesh pattern, the predetermined opening O is formed at the intersection of the warp yarns 141 and the weft yarns 142. Therefore, the sample provided on the sample inlet 132a is provided as a passage through the filter member 140, and a solid component of the solid component contained on the sample exceeds the space size d of the mesh pattern, It is filtered by the filter member 140, and the remaining sample flows into the flow path.

As shown in FIG. 4, the mesh pattern is formed in a water-like shape, and the warp yarns 141 and the weft yarns 142 are alternately crossed to form a three-dimensional shape. One of the warp yarns 141 or the weft yarns 142 . As in the embodiment of the present disclosure, the weft 142 can be formed to cross the four warps 141 and cross. Thus, a predetermined opening O is formed at a portion where the warp yarns 141 and the weft yarns 142 intersect, like a plain weave or a twill weave mesh pattern. Thus, the sample provided on the sample inlet port 132a is provided as a passage through the filter member 140. The solid component of the solid component contained on the sample, which is larger than the size d of the opening O of the mesh pattern, O, it is filtered by the filter member 140, and the remaining sample flows into the flow path.

In the embodiment of the present disclosure, the mesh pattern is a plain weave shape, a twilled weave shape or a numerical shape, for example, but is not limited thereto. For example, it is possible to change the shape crossing according to the size (d) of the solid component to be filtered, and to form the opening O according to the size (d) of the solid component to be filtered. The shape and the structure of the mesh pattern can be changed at any time.

Although not shown, the filter member 140 according to one embodiment of the present disclosure may include two filter portions of the first filter portion and the second filter portion. The first filter portion forms a pattern only in the direction of the warp yarns 141 or the weft yarns 142. The second filter portion forms a pattern in a direction crossing the pattern direction of the first filter portion, that is, a direction different from that of the first filter portion among the warp yarns 141 or the weft yarn 142 direction. That is, when the pattern direction of the first filter unit is formed in the direction of the warp yarns 141, the pattern direction of the second filter unit is formed in the direction of the weft yarn 142 intersecting the first filter unit. If the pattern direction of the first filter part is formed in the direction of the weft 142, the pattern direction of the second filter part is formed in the direction of the warp yarn 141 which intersects with the first filter part. When the first filter unit and the second filter unit are formed in the warp yarns 141 or the weft yarns 142 and the first filter unit and the second filter unit are overlapped with each other, The patterns of the negative weft yarns or warp yarns cross each other. Thus, an opening O is formed at a portion where the warp yarns 141 and the weft yarns 142 intersect. When the sample is supplied to the sample inlet 132a in a state where the first filter unit and the second filter unit are laminated, the solid components of the solid O contained in the sample are larger than the size d of the opening O, . The sample filtered by the solid component having the size (d) or more of the opening (O) can be flowed into the detecting portion 111, that is, the electrode layer 111b through the flow path, and the solid component previously deposited on the flow path and the electrode layer 111b The reliability of detection of the electrode layer 111b is improved. In addition, the hydrophilic coating layer can be provided by the pattern surfaces of the warp yarns 141 and the weft yarns 142 of the first filter portion and the second filter portion of the present embodiment. After the sample is supplied to the sample inlet 132a to filter the solid component having a predetermined size d or more, the sample is supplied to the warp yarns 141 of the first filter unit and the second filter unit and the liquid component It can be attached to the surface easily and can be moved quickly by the capillary phenomenon.

FIG. 5 is a view showing a state where a solid component is filtered on a filter member in a biosensor according to an embodiment of the present disclosure shown in FIG. 1; FIG. Referring to FIG. 5, when a user drops a sample, specifically, blood on the sample inlet 132a side of the biosensor 100, the sample is sucked into the detection unit 111 through the capillary phenomenon. At this time, the sample provided in the sample inlet 132a must pass through the filter member 140 in order to flow into the channel. Therefore, a solid component larger than the opening O of the filter member 140 having the above-described shape among the solid components contained in the sample is stacked on the upper side of the filter member 140 and can not penetrate through the opening O, . Therefore, after the blood having a predetermined size (d) or more of the solid component is filtered into the channel, the channel moves to the electrode layer 111b through the channel through the capillary phenomenon and contacts the electrode layer 111b. The blood flowing into the flow path is limited in that the solid component having a predetermined size (d) or more is filtered so as to be stacked on the flow path or laminated on the electrode layer 111b as filtered. Since the solid component is not laminated on the flow path or the electrode layer 111b, the blood can be easily moved on the flow path, and the blood can easily contact the electrode layer 111b. The blood is brought into contact with the blood in the electrode layer 111b to detect information of the blood and thereby the error of the blood glucose value may be reduced and the error of the blood glucose value may be reduced even when the difference in the size d of the solid component occurs . In addition, accuracy and reliability of the detected blood glucose value can be improved.

Although the present disclosure has been described with reference to specific embodiments, various modifications may be made without departing from the scope of the present disclosure. Although the warp yarn and the weft yarn are described as an example of the filter member, the filter member may form a mesh pattern of various shapes such as a right angle or a diagonal line if the structure is such that the openings are formed while intersecting each other.

As described above, it is not necessary that the filter member is formed as a single layer. It is also possible to form the filter unit so that two or more filter units in which patterns are formed in one direction are formed so that the patterns cross each other. The scope of implementation.

Therefore, the scope of the present invention should not be limited by the described embodiments but should be determined by the equivalents of the claims and the claims.

100: Biosensor 110: Base substrate
111: detecting portion 120: insulating layer
130: upper plate 140: filter member

Claims (9)

In the biosensor,
A base substrate having a detection portion;
An upper plate laminated on the base substrate and provided with a sample inlet portion through which the sample is introduced into the detection portion; And
And a filter member provided between the upper plate and the base substrate and filtering a solid component of a predetermined size introduced into the sample inlet.
The method according to claim 1,
Wherein the filter member is provided in a mesh pattern in which a warp yarn and a weft yarn alternate with each other.
3. The method of claim 2,
Wherein the mesh pattern has at least one shape of a plain weave, a twill weave, or a water polished weave.
The filter according to claim 1,
At least one or more filter sections having a mesh pattern are stacked,
Wherein when the filter portion is stacked, the mesh pattern of each filter portion has a different direction.
5. The filter according to claim 4,
A first filter portion formed in at least one direction of a warp or weft direction; And
And a second filter portion stacked on the first filter portion and formed in a direction different from the first filter portion of the warp or weft direction.
The method according to claim 1,
Wherein the filter member comprises at least one or more materials selected from the group consisting of polyester, nylon, polyethylene, and fluorine resin.
The method according to claim 1,
And a hydrophilic coating layer is formed on the surface of the filter member so that a liquid sample flows into the detection unit.
The method according to claim 1,
And the size of the opening formed in the filter member is 10 to 50 占 퐉.
The method according to claim 1,
Wherein a solid component larger than an opening size of the filter member among the solid components in the sample is filtered by the filter member when the sample is dropped on the inlet.

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