JP5821430B2 - Liquid absorbing member and biological reaction detection system - Google Patents

Description

  The present invention relates to an immunochromatographic test strip and a detection system using the same.

Conventionally, simple and rapid diagnosis of influenza and the like has been performed by an immunochromatographic method using a membrane filter (hereinafter referred to as a liquid absorption carrier). Here, the immunochromatography method is a stationary phase in which an antibody (or antigen) against an antigen (or antibody) as a substance to be detected is immobilized on a liquid absorption carrier and a reaction site is prepared on the liquid absorption carrier. The mobile phase is a chromatograph of the mobile phase on the above-mentioned stationary phase using, as a mobile phase, a dispersion liquid in which particles for detection sensitized by an antibody (or antigen) capable of binding to the above-mentioned target substance as a detection reagent The sample is brought into contact with the reaction site, whereby an antigen (or antibody) present in the sample is bound to the immobilized antibody (or immobilized antigen) at the reaction site. In addition, when the sensitizing antibody (or sensitizing antigen) on the detection particle is bound to the antigen (or antibody), the detection particle is specifically bound and captured (for example, Patent reference 1).
In addition, an analysis method has been proposed that can increase the sensitivity of chromatographic analysis such as immunochromatographic analysis without using a special membrane or absorbent on the chromatographic strip (see, for example, Patent Document 2).

Japanese Patent No. 3385377 JP 2010-164535 A

  In the conventional liquid absorption carrier used in the immunochromatography method, a porous liquid absorption carrier is produced with micropores formed by dissolving nitrocellulose with an organic solvent and volatilizing the organic solvent. The shape of the hole was controlled by physical parameters such as temperature and humidity. However, this method makes it difficult to control the pores, and since the material is a nitrocellulose liquid-absorbing carrier, the hydrophilic / hydrophobic properties change over time and greatly change depending on the surrounding atmosphere, especially humidity. It was difficult to control the flow rate. As a result, this resulted in variations in measurement results. Further, the carrier for absorbing nitrocellulose liquid is opaque because of its irregular porous shape, so that all of the labeling substances gathered in the form of antibody lines could not contribute to visibility. As a result, this resulted in a detection sensitivity of less than half.

  Accordingly, an object of the present invention is to solve the above-mentioned problems of the prior art, and to provide a liquid absorbing member for immunochromatography capable of improving the detection sensitivity capable of controlling the flow rate.

  SUMMARY An advantage of some aspects of the invention is to solve at least a part of the problems described above, and the invention can be implemented as the following forms or application examples. That is, the gist of the present invention is to provide an immunochromatographic liquid absorbing member capable of controlling the liquid absorption carrier flow rate and improving the detection sensitivity.

  Application Example 1 A liquid absorbing member according to this application example includes a carrier having a groove along a first direction, an antibody fixed on the surface of the groove, and an absorber disposed on the groove. And the liquid passes through the groove.

  According to this application example, by providing the carrier with a groove along the first direction, the flow rate of the liquid flowing in the groove can be controlled by capillary action, and this carrier can be used for detection diagnosis such as immunochromatography. When used in a tool, the detection accuracy can be improved.

  Application Example 2 In the liquid absorbing member according to the application example, the grooves are arranged in a second direction intersecting the first direction.

  According to this application example, by providing a plurality of groove shapes, many capillary phenomena can be generated. By controlling the groove shape, the liquid can be controlled to move through the carrier at an assumed speed.

  Application Example 3 In the liquid absorbing member according to the application example described above, the carrier is disposed so as to overlap along a third direction intersecting the first direction and the second direction. To do.

  According to this application example, the detection sensitivity can be improved by stacking a plurality of sheets along the third direction.

  Application Example 4 In the liquid absorbing member according to the application example described above, the carrier further has a pillar structure, and the liquid passes through the pillar structure.

  According to this application example, when this liquid absorbing member is used in a detection diagnostic tool such as immunochromatography, it is necessary to immobilize an antibody or the like which is a biomaterial. Although it is possible to apply and immobilize an antibody on a part of one liquid absorbing member having a groove structure from above, it becomes difficult when a plurality of the liquid absorbing members are stacked. Therefore, if a part of the groove structure has a pillar structure, the antibody can be injected from the side surface in the thickness direction of the liquid absorbing member, and the antibody can be immobilized at the pillar structure.

  Application Example 5 In the liquid absorbing member according to the application example described above, the carrier includes polydimethylsiloxane.

According to this application example, by using polydimethylsiloxane (hereinafter referred to as PDMS) as a resin molded from a mold, it is possible to manufacture a liquid absorbing member that ensures transparency and accuracy from the characteristics of this material. PDMS can be transferred to a sub-micron structure by molding and has a very high mold release characteristic with respect to a silicon substrate used as a microfabricated material, so that a fine structure can be easily formed. Since it is self-adsorbing, it is easy to bond PDMS to each other or glass, so it is easy to assemble a workpiece into a layer structure. It is colorless and transparent and hardly absorbs in the visible light region. It has the feature of being a biocompatible material.
In addition, since a transparent material is used, when this material is used as a diagnostic tool, an optical signal of a labeling substance for detection can be detected more easily than an opaque material.
Furthermore, since the material is transparent, detection sensitivity can be improved by stacking a plurality of the same materials in the thickness direction.

  Application Example 6 In the liquid absorbing member according to the application example described above, the surface of the groove is surface-treated.

  According to this application example, when this liquid absorbing member is used in a detection diagnostic tool such as immunochromatography, it is necessary to immobilize an antibody or the like which is a biomaterial. When immobilizing this antibody, if the surface of the material is extremely hydrophilic, there is a possibility that when the solution containing the antibody is dropped, it spreads over the entire carrier. On the other hand, in the case of extremely hydrophobicity, there is a possibility that the liquid does not flow in the carrier. For this reason, it is necessary to control the hydrophilicity or hydrophobicity of the carrier surface. In addition, liquid feeding in the carrier is caused by a capillary phenomenon. As a physical parameter for controlling the capillary phenomenon, there is a contact angle θ in addition to the capillary radius described above. By subjecting the material to a hydrophilic treatment in advance, this contact angle can be controlled, and the liquid feeding speed by capillary action can be controlled.

  Application Example 7 In the liquid absorbing member according to the application example described above, the carrier is formed by pouring a resin into a matrix, solidifying the resin, and releasing the solidified resin and the matrix. It is characterized by that.

  According to this application example, it is possible to form a carrier having an elongated groove with a minute pattern by pouring a resin into a mother die, solidifying the resin, and releasing the solidified resin and the mother die.

  Application Example 8 A biological reaction detection system according to this application example includes a detector that detects whether or not a substance to be detected has reacted with the antibody in the liquid absorbing member according to the application example. .

  According to this application example, by detecting from the side surface, the signal is compressed by the width of the liquid absorbing carrier, and the apparent signal is increased. As a result, the detection sensitivity can be finally improved.

  The above-described configurations can be combined with each other without departing from the spirit of the present invention.

Explanatory drawing which shows the biological reaction detection system which concerns on this embodiment. The figure which showed the liquid absorption support | carrier which concerns on this embodiment. The SEM image of the conventional carrier for nitrocellulose liquid absorption. The figure which showed the preparation methods of the liquid absorption support | carrier which concerns on this embodiment. The figure which showed the preparation methods of the immunochromato strip which concerns on this embodiment. The figure which showed the usage method of the immunochromatography strip which concerns on this embodiment. The figure which showed the method to detect the label | marker substance which concerns on this embodiment.

Hereinafter, embodiments of the present invention will be described with reference to the drawings.
A. Overall configuration of the biological reaction detection system:
FIG. 1 is an explanatory diagram showing a biological reaction detection system according to this embodiment. The biological reaction detection system 100 according to the present embodiment performs simple rapid diagnosis such as influenza, and the antibody 4 (or antigen) against the antigen (or antibody) that is the substance to be detected is liquid-absorbing carrier (carrier). An immunochromatographic strip 0 as a liquid absorbing member fixed to 1 and a detector 15 for detecting whether or not a substance to be detected has reacted with the antibody 4 in the immunochromatographic strip 0.

B. Composition of immunochromatographic strip:
The immunochromatographic strip 0 according to the present embodiment includes a liquid absorbing carrier 1 that allows a solution (liquid) to permeate and an absorption pad (absorber) 2 that sucks up the solution. The immunochromatographic strip 0 is coated with an antibody 4 that is a biomaterial in the middle of the liquid absorbing carrier 1. The immunochromatographic strip 0 captures an antigen by utilizing a non-specific reaction of the antibody 4. The liquid absorbing carrier 1 includes a laminated body 3 of structures 5 having elongated grooves 10 when enlarged. The solution passes through the groove 10. The solution here is a solution in which an antigen or labeled antibody described below is dissolved, or a washing solution.

  The liquid absorbing carrier 1 has a groove 10 along the first direction (x direction in FIG. 1). The grooves 10 are arranged in a second direction (y direction in FIG. 1) that intersects the first direction. The liquid absorbing carrier 1 is disposed so as to overlap along a third direction (z direction in FIG. 1) intersecting the first direction and the second direction. The liquid absorbing carrier 1 is a thin film-like object having a width of about 5 mm, a length of 5 cm, and a thickness of about 2 mm, for example. The liquid absorbing carrier 1 can be produced using a polymer material. In that case, it is suitable to produce with transparent resin. As the transparent resin, for example, a thermosetting transparent resin such as polystyrene, acrylic resin, polypropylene, cycloolefin polymer resin, polyethylene terephthalate resin, polyacetal, or polydimethylsiloxane (PDMS) which is a kind of silicone resin can be used. By making such a transparent resin, an optical signal of the labeling substance 16 for detection described later can be easily detected.

  The laminated body 3 is a structure 5 having a plurality of grooves 10 whose cross section is controlled to a square shape of about 10 μm × 10 μm. The cross-sectional shape is not particularly limited to a square as long as it is easy to mold. The laminate 3 of the structure 5 having the elongated grooves 10 is desirably a material that can be easily processed and molded to about 10 μm. Examples of such materials include polystyrene, acrylic resin, polypropylene, cycloolefin polymer resin, polyethylene terephthalate resin, thermosetting transparent resin such as polyacetal, polydimethylsiloxane (PDMS) which is a kind of silicone resin, polycarbonate, polyvinyl chloride, Polyethylene terephthalate or the like can be used. PDMS is a material that satisfies the above-described conditions of transparency and workability. PDMS can be transferred to a sub-micron structure by molding and has a very high release property with respect to a silicon substrate used as a microfabricated material, so that a fine structure can be easily formed.

  The surface of the flow path of the laminate 3 is controlled to be hydrophilic or hydrophobic. Here, the control of hydrophilicity or hydrophobicity is to impart hydrophilic or hydrophobic characteristics to the material surface. When the hydrophilic or hydrophobic treatment is not performed, the hydrophilic or hydrophobic characteristics of the material surface easily change over time. For example, in the case of cellulose, a surfactant is added dropwise to control the hydrophilic or hydrophobic characteristics of the material, but since the surfactant is only added dropwise, if the amount of the solution to be absorbed increases, The hydrophobic property changes, and the set property cannot be maintained.

  Here, a method for controlling hydrophilicity or hydrophobicity is to specifically perform a treatment such as oxygen plasma, corona discharge, or UV treatment. For example, when a polystyrene material is subjected to oxygen plasma, hydroxyl groups are precipitated on the surface of the material, so that the hydrophobic surface of polystyrene can be transformed into a hydrophilic surface. As described above, since the shape and the hydrophilic or hydrophobic characteristics of the flow path surface are controlled, the speed of the solution flowing through the liquid absorbing carrier 1 can be kept constant.

  The antibody 4 is fixed to the surface of the groove 10. The antibody 4 is a biomaterial for capturing an antigen using a non-specific reaction of the biomaterial. Specifically, it is a material such as IgG (immunoglobulin). The method for immobilizing the antibody 4 is generally physical adsorption.

  The absorbent pad 2 is disposed on the groove 10. The absorbent pad 2 sucks up the solution that has passed through the liquid absorbent carrier 1 and uses, for example, a nonwoven fabric. The absorbent pad 2 may be composed of a structure having an elongated groove as in the liquid absorbing carrier 1 or a laminate of structures having pillars to be described later. Thereby, solution control becomes possible.

  FIG. 2 is a view showing the liquid absorbing carrier 1 according to the present embodiment. Specifically, in an enlarged view of the laminate 3, as shown in FIG. 2 (A), a microstructure for constituting the laminate 3 of the structure 5 having the elongated grooves 10 is shown. Further, as shown in FIG. 2B, the liquid absorbing carrier 1 may constitute a laminate 7 of a structure 6 having pillars. The solution passes through the structure 6 with pillars. Further, the structure 5 having the elongated grooves 10 and the structure 6 having the pillars are superposed on each other to superimpose the stacked body 3 including the structures 5 having the elongated grooves 10 and the structure having the pillars. A micro flow path may be constructed like the laminated body 7 constituted by six. In addition, the both sides of a pillar structure are equipped with the wall surface of the same height as a pillar, and this is for assisting the liquid feeding effect which may be insufficient only with a pillar.

  When the structure 5 having the elongated groove 10 is compared with the structure 6 having the pillar, the structure 5 having the elongated groove 10 that is a simple flow path structure is better for controlling the flow velocity, and the sensitivity is improved. For this purpose, a structure 6 having pillars for applying as much antibody 4 as possible to the reaction and reacting the antigen and the solid-phased material as uniformly as possible on the liquid absorbing carrier 1 is preferable. For this reason, the structure 6 having pillars only where the antibody 4 reacts and the structure 5 having elongated grooves 10 other than that can realize the carrier having both the above-described characteristics. it can. For example, it is a structure like the composite structure 8 shown in FIG. Further, it is possible to apply and immobilize the antibody 4 on a part of a single liquid absorption carrier having a groove structure from above, but it becomes difficult when a plurality of the antibodies are stacked. Therefore, if a part of the groove structure has a pillar, the antibody 4 is injected from the side surface in the thickness direction of the liquid absorbing carrier 1 and the antibody 4 is immobilized at the structure having the pillar. can do.

  FIG. 3 is an SEM image of a conventional nitrocellulose liquid absorbing carrier. From the SEM image, irregular micropores 19 of 2 μm to 14 μm are confirmed. Generally, the capillary phenomenon in a structure such as a nitrocellulose liquid absorbing carrier can be expressed by the following formula.

However, l: penetration depth, r: capillary radius, γ: surface tension of liquid, θ: contact angle, η: viscosity, t: time.
Represented by Lucas Washburn's formula. For this reason, if the same solution is flowed, the liquid feeding speed is determined by the capillary radius r that forms the micropores 19, the surface tension γ of the liquid determined by the hydrophilic or hydrophobic characteristics of the surface, and the contact angle θ. .

  From the Lucas Washburn equation, it is conceivable that the nitrocellulose liquid absorbing carrier is difficult to control the flow rate as compared with the liquid absorbing carrier 1 of the present embodiment. More specifically, when the micropores 19 are 2 μm to 14 μm, the maximum and minimum diameters are different by 7 times. When the difference is seven times, the penetration depth l that determines the velocity is 2.65 times and the flow rate difference is also 2.65 times from the capillary phenomenon equation. As described above, the variation of the micro holes 19 becomes the variation of the flow velocity.

  The liquid absorbing carrier 1 in the present embodiment is manufactured using a photofabrication technique and a molding technique. Thereby, micropores can be produced with submicron accuracy, and the flow rate in the produced micropores does not vary as in the case of nitrocellulose. Photofabrication technology can be processed at a level of several tens of nanometers, and molding technology using a PDMS material enables processing at a submicron level. For this reason, since there is no error of several micrometers as in the case of the nitrocellulose liquid absorbing carrier, it is possible to send liquid at a substantially constant flow rate if the control of hydrophilicity or hydrophobicity is sufficient. The rate of liquid delivery can be checked by measuring the time required to draw a certain amount of solution.

  FIG. 4 is a view showing a method for producing the liquid absorbing carrier 1 according to this embodiment. The laminated body 3 may be directly produced by a microfabrication technique such as photofabrication, but it is better to use a mold in order to improve the productivity of the liquid absorbing carrier 1. Here, photofabrication is a precision processing method in which the surface of a material is chemically or electrochemically dissolved, or a precise processing shape for depositing metal on the surface of the material is performed using a photographic technique. is there.

  As a pre-stage, a silicon mold (matrix) is produced by a normal fine processing technique. Specifically, a resist pattern is formed on the substrate surface using a mask pattern, and an Si mold 9 shown in FIG. 4A is formed by anisotropic wet etching.

  Next, as shown in FIG. 4A, fluidized resin (PDMS) 18 is poured into the Si mold 9. At that time, it is necessary to sufficiently degas the PDMS 18 by a technique such as vacuum degassing. When the PDMS 18 is poured, if the PDMS 18 is not sufficiently defoamed, many bubbles will enter the PDMS 18 when solidified. When bubbles are introduced, the transparency is lowered, so that it is difficult to improve detection sensitivity and perform detection at various angles as assumed in the present embodiment.

  Next, as shown in FIG. 4B, the PDMS 18 fluidized in the Si mold 9 is solidified. At that time, when solidifying, it is necessary to perform sufficient leveling using a level. If the leveling is not performed, structures having different thicknesses depending on the part are formed. In a structure having a different thickness, the structure 5 having the elongated groove 10 cannot be formed into a three-dimensional structure like the stacked body 3 (see FIG. 2A). Even if it can be made, a gap is generated in the layer portion of the laminate 3 of the structure 5 having the long and narrow grooves 10, so that the expected flow rate cannot be controlled and the solution leaks. Solidification is preferably performed, for example, with a hot air circulating dryer for about 80 degrees 20 minutes.

  After that, as shown in FIG. 4C, the structure 5 having the fine groove 10 is formed by releasing the mold. When releasing, it is necessary to remove it slowly. If it is not peeled off slowly, the minute structure 5 remains in the matrix of FIG. 4A by the PDMS 18 and the desired microstructure cannot be transferred to the PDMS 18.

  In addition, the structure 5 having the long and narrow groove 10 shown in FIG. 4C may be manufactured using a hot embossing technique in which the structure 5 is pressed against a heated resin substrate.

  FIG. 5 is a diagram showing a method for producing the immunochromatographic strip 0 according to the present embodiment. Specifically, a method for applying the antibody 4 to the structure 5 having the elongated groove 10 and a method for producing the laminate 3 of the structure 5 having the elongated groove 10 are shown. First, as shown in FIG. 5A, the antibody 4 is applied to a part of the upper surface of the structure 5 having the elongated grooves 10. At that time, it is desirable that the surface of the structure 5 on the groove 10 side is activated. “Activated” means to activate a stable plastic surface by subjecting the plastic material to oxygen plasma treatment or UV treatment. Thereby, the antibody 4 becomes easy to be physically adsorbed.

  Next, as shown in FIG. 5 (B), the substrate for immobilizing the antibody 4 is made into a multi-layer to produce the liquid absorbing carrier 1. Multi-layering with a PDMS material can be manufactured as shown in FIG. 5B by superposing the adhesion surfaces of the respective substrates on oxygen plasma. In addition, if there are through holes on the substrate with a fine pattern, the antibody 4 can be immobilized even after being stacked in multiple layers. If necessary, blocking is performed using a blocking material such as MPC (2-methacryroyloxyethylphosphorylcholine) polymer, casein, bovine serum albumin (BSA), and the like.

  Here, the blocking is performed in order to prevent the detection target substance from being adsorbed to the base material in a non-specific manner rather than being captured by the immobilized antibody 4 and localized on the substrate. If non-specific adsorption occurs, the target cannot be measured. That is, the blocking material is adsorbed on the liquid absorption carrier 1 other than where the antibody 4 is immobilized, and the detection target substance is prevented from adsorbing on the liquid absorption carrier 1. Furthermore, by applying a blocking material, the hydrophilicity or hydrophobicity of the surface of the liquid absorbing carrier 1 can be controlled.

C. Operation of the embodiment:
FIG. 6 is a view showing a method of using the immunochromatographic strip 0 according to the present embodiment. First, an antibody 4 is fixed in the middle of the liquid absorbing carrier 1 and blocked with BSA. As the immobilized antibody 4, an antibody 4 that specifically reacts with the antigen 12 to be measured was used.

  Next, as shown in FIG. 6A, the immunochromatographic strip 0 is immersed in a solution 11 containing the antigen 12. The solution flows in the order of the liquid absorption carrier 1 and the absorption pad 2 (see FIG. 1) by capillary action. The antigen 12 contained in the solution reacts with the antibody 4 immobilized on the liquid absorbing carrier 1 and is trapped by the antibody 4.

  Next, as shown in FIG. 6 (B), a gold colloid-labeled antibody 14, which is labeled with a gold colloid having a diameter of about 40 nm, which binds to a site different from the antibody 4 immobilized on the liquid absorbing carrier 1. The colloidal gold labeled antibody solution 13 is sucked. The antigen 12 trapped in the antibody 4 reacts with the gold colloid-labeled antibody 14 to finally collect the labeling substance 16 in a line according to the antigen concentration. Since the gold colloid is used for the labeling substance 16, when there is a sufficient amount of the antigen 12, a red line of the labeling substance 16 is displayed on the liquid absorbing carrier 1.

  Finally, as shown in FIG. 6C, the color density of the red line of the labeling substance 16 is examined by the detector 15 or the like. The density of the red line corresponds to the amount of the antigen 12, and the antigen amount can be examined by confirming this relationship.

  As described in FIG. 3, the micropores of the conventional liquid absorption carrier have a width of 2 μm to 14 μm, and the average value of the micropores 19 in the liquid absorption carrier is the same. The size will be different. First, due to the difference in the size of each micropore 19, the result on the liquid absorbing carrier is expanded, and the result is blurred and the result is expanded. In addition, the difference in the average value results in a difference in the reaction time of the antigen-antibody because the liquid feeding speed in the liquid absorbing carrier varies, resulting in variations in measurement results. With this mechanism, the conventional immunochromatography can only detect a quantitative amount.

  Originally, immunochromatography is a detection method expected to be applied to various inspections because a target can be detected simply by dropping a sample. However, the application range is limited because only the qualitative detection can be performed at the present time due to the problem described above.

  Therefore, as in the immunochromatographic strip 0 of this embodiment, by controlling the microchannel (groove 10), a stable measurement result is obtained, the reaction result is detected by the detector 15, and the result is digitized. By doing so, quantitative measurement can be realized.

  Regarding the variation of the flow path system, the smaller the error, the better. However, it is technically difficult to make the flow path diameter accuracy less than 1% because of the possibility of variation. Conversely, if the flow path diameter error exceeds 50%, only qualitative detection can be performed. That is, by setting the variation in flow path diameter to 1% or more and 50% or less, the flow rate can be controlled by the configuration of the present embodiment, and as a result, the detection sensitivity can be improved.

  FIG. 7 is a diagram showing a method for detecting the labeling substance 16 according to this embodiment. In FIG. 7A, a signal derived from the labeling substance 16 constituting the line is visually confirmed from above the liquid absorbing carrier 1. In FIG. 7B, a signal derived from the labeling substance 16 constituting the line is confirmed by the detector 15 from the upper part of the liquid absorbing carrier 1. In FIG. 7C, the liquid absorbing carrier 1 is illuminated by the irradiator 17 from above and detected by the detector 15 from below. In FIG. 7D, a signal derived from the labeling substance 16 constituting the line is detected by the detector 15 from the side surface of the liquid absorbing carrier 1. In FIG. 7E, irradiation with the irradiator 17 is performed from the side surface of the liquid absorbing carrier 1, and a signal derived from the labeling substance 16 constituting the line is detected from the side surface.

  In the case of a conventional nitrocellulose liquid-absorbing carrier, since the liquid-absorbing carrier itself is opaque, there is only a method of observing from the upper part of the surface on which the antibody 4 is applied. However, in the present embodiment, since the carrier instead of the liquid absorbing carrier is a transparent material, it can be detected from the side surface in the thickness direction of the liquid absorbing carrier 1. Thereby, signal intensity can be improved by detecting in the state where the signal was overlapped by the width of the liquid absorbing carrier 1.

  Further, if the signal derived from the labeling substance 16 constituting the line is due to light absorption, the wavelength of the irradiator 17 may be white light having a broad wavelength, but the irradiation wavelength is set to the absorption wavelength. As a result, the signal intensity against noise is increased, and the detection sensitivity can be further increased.

  The present invention is not limited to the description of the embodiment described above, and can be widely applied without departing from the gist of the present invention.

  DESCRIPTION OF SYMBOLS 0 ... Immunochromato strip (liquid absorption member) 1 ... Carrier for liquid absorption (carrier | carrier) 2 ... Absorption pad (absorber) 3 ... Laminated body 4 ... Antibody 5 ... Structure with long and narrow groove 6 ... Structure with pillar (Pillar structure) 7 ... Laminated body composed of structures having pillars 8 ... Composite structure 9 ... Si mold 10 ... Groove 11 ... Solution containing antigen 12 ... Antigen 13 ... Gold colloid labeled antibody solution 14 ... Gold colloid labeled Antibody (labeled antibody) 15 ... Detector 16 ... Labeled substance 17 ... Irradiator 18 ... Resin (PDMS) 19 ... Micropore 100 ... Biological reaction detection system.

Claims (6)

A carrier having grooves along a first direction;
An antibody immobilized on the surface of the groove;
An absorber disposed on the groove;
Including
The grooves are arranged in a second direction intersecting the first direction;
The carrier is disposed so as to overlap along a third direction intersecting the first direction and the second direction,
A liquid absorbing member, wherein a liquid passes through the groove. The liquid absorbing member according to claim 1 ,
The carrier further has a pillar structure,
The liquid absorbing member, wherein the liquid passes through the pillar structure. In the liquid absorption member according to claim 1 or 2 ,
The liquid absorbent member, wherein the carrier contains polydimethylsiloxane. In the liquid absorption member according to any one of claims 1 to 3 ,
The liquid absorbing member, wherein the surface of the groove is surface-treated. In the liquid absorption member according to any one of claims 1 to 4 ,
The liquid absorbent member, wherein the carrier is formed by pouring a resin into a mother mold, solidifying the resin, and releasing the solidified resin and the mother mold. A biological reaction detection system comprising a detector for detecting whether or not a substance to be detected has reacted with the antibody in the liquid absorbing member according to claim 1 .