JP5316530B2 - Microchip and its channel structure - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a microchip capable of interleaving a sample liquid laminar flow by a sheath liquid laminar flow along the vertical direction (depth direction) of a channel, and providing a high-precision analysis. <P>SOLUTION: The microchip 1 includes a channel 11 permitting a sheath liquid to flow therethrough, and a microtube 14 for introducing a sample liquid into the sheath liquid laminar flow flowing through the channel 11. In the microchip 1, liquid is fed under the condition where the sample liquid laminar flow is surrounded by the sheath liquid laminar flow because the sample liquid is introduced through the microtube 14 into the sheath liquid laminar flow. <P>COPYRIGHT: (C)2010,JPO&amp;INPIT

Description

  The present invention relates to a microchip and its flow channel structure. More specifically, the microchip is provided with a channel for performing chemical and biological analysis, and the sample liquid laminar flow is surrounded by the sheath liquid laminar flow in the channel and is sent. It relates to microchips.

  2. Description of the Related Art In recent years, microchips that are provided with regions and flow paths for performing chemical and biological analysis on a silicon or glass substrate have been developed by applying microfabrication technology in the semiconductor industry. These microchips are beginning to be used in, for example, electrochemical detectors for liquid chromatography and small electrochemical sensors in the medical field.

  Such an analysis system using a microchip is called μ-TAS (micro-Total-Analysis System), lab-on-chip, biochip, etc., and speeding up and high efficiency of chemical and biological analysis. As a technology that enables downsizing, integration, or downsizing of analyzers, it is attracting attention.

  Since μ-TAS can be analyzed with a small amount of sample and can be used as a disposable microchip, it is expected to be applied to biological analysis, especially for handling precious trace samples and many specimens. Has been.

  As an application example of μ-TAS, there is a microparticle analysis technique for optically, electrically, or magnetically analyzing the characteristics of microparticles such as cells and microbeads in a channel disposed on a microchip. In this microparticle analysis technique, as a result of the analysis, a population (group) that satisfies a predetermined condition is also collected separately from the microparticles.

  For example, Patent Document 1 discloses “a fine particle sorting microchip having a fine particle-containing solution introduction flow channel and a sheath flow forming flow channel disposed on at least one side of the flow channel”. The microparticle sorting microchip further includes a “particulate measurement site for measuring the introduced microparticles, two or more microparticle sorting channels for separating and collecting the microparticles installed downstream of the microparticle measurement site, and a microparticle It has two or more electrodes for controlling the moving direction of the fine particles installed in the vicinity of the flow path opening from the measurement site to the fine particle sorting flow path ”.

  The microparticle sorting microchip disclosed in Patent Document 1 typically forms a fluid laminar flow by a “three-pronged channel” composed of a microparticle-containing solution introduction channel and two sheath flow forming channels. (Refer to the document “FIG. 1”).

  FIG. 13 shows a general three-pronged channel structure (A) and a sample liquid laminar flow and a sheath liquid laminar flow (B) formed thereby. In this three-pronged channel, the sample liquid laminar flow that flows through the channel 101 in the direction of the solid arrow in FIG. 13A is sandwiched from the left and right by the sheath liquid laminar flow introduced into the channels 102 and 102 from the direction of the dotted arrow. Can do. Thus, as shown in FIG. 13B, the sample liquid laminar flow can be sent to the center of the flow path. In FIG. 13B, the sample liquid laminar flow is indicated by a solid line, and the flow path structure is indicated by a dotted line.

  In the microparticle sorting microchip of Patent Document 1, a microparticle-containing solution is sandwiched between sheath liquids from the left and right by the three-pronged channel, and the microparticles are sent to the center of the channel of the microparticle measurement site. Thereby, for example, when measuring fine particles optically, it is possible to accurately irradiate the fine particles with measurement light.

JP 2003-107099 A

  According to the three-pronged channel shown in FIG. 13, the sample liquid laminar flow is sandwiched by the sheath liquid laminar flow from the left and right, and the sandwiching direction (Y-axis positive / negative direction in FIG. 13) is at an arbitrary position in the channel. The sample liquid laminar flow can be deflected and sent. However, with respect to other directions, for example, the vertical direction of the flow path (Z-axis positive / negative direction in FIG. 13), it was not possible to control the position of the sample liquid feeding. That is, in the three-pronged channel shown in FIG. 13, only a vertically long sample liquid laminar flow could be formed in the Z-axis direction.

  Therefore, in a conventional microchip having a three-pronged channel, for example, when optical analysis is performed by passing a solution containing microparticles as a sample solution into the channel, the microchip in the vertical direction (depth direction) of the channel is small. There was a variation in the particle flow position. For this reason, there was a problem that it was impossible to irradiate fine particles with measurement light with high accuracy.

  In particular, when analyzing cells such as blood cells as microparticles, the cells are sent while rolling on the bottom of the channel, and the cell delivery position and measurement light in the vertical direction (depth direction) of the channel There was a large shift in the focal position of the lens, which caused the analysis accuracy to decrease.

  Therefore, the present invention provides a microchip that can sandwich a sample liquid laminar flow by a sheath liquid laminar flow in the vertical direction (depth direction) of the flow path and can obtain high analysis accuracy. Main purpose.

In order to solve the above problems, the present invention includes a flow path through which the sheath liquid and the sample liquid can flow, and the sample liquid laminar flow introduced into the flow path is surrounded by the sheath liquid laminar flow. Provided is a microchip that is fed in a liquid state. In this microchip, the flow path bottom surface and / or the top surface is formed as an inclined surface so that the area of the cross section perpendicular to the liquid feed direction gradually decreases in accordance with the liquid feed direction, and the flow path side walls It has a constricted portion that is gradually constricted according to the liquid feeding direction, and the sheath liquid laminar flow and the sample liquid laminar flow are isotropically reduced while being deflected toward the upper or lower surface of the microchip, and then fed. .
In this microchip, the inclination angle of the channel bottom surface and / or the top surface of the narrowing portion and the narrowing angle of the channel side wall may be formed equal.
A branch channel that branches downstream of the narrowing part of the channel is provided, and the liquid feeding direction in the branch part of the sample liquid to which the charge is applied is controlled by an electrode arranged in the branch part of the branch channel. You can also
You may provide the fluid introducing | transducing part which joins from the at least one side upstream of the said branch part of the said flow path, and introduce | transduces any fluid of gas or an insulating liquid into a flow path. In this case, the sheath liquid laminar flow and the sample liquid laminar flow that flow through the flow path can be divided by the fluid introduced from the fluid introduction unit, and the liquid can be sent as droplets.
In addition, the fine particles can be separated by controlling the liquid feeding direction in the branching portion of the sample liquid containing the fine particles that have been made droplets and given a charge.
The present invention also provides a fluid analysis device and a fine particle sorting device on which the above-described microchip can be mounted.

In addition, the present invention is a flow channel structure formed inside a microchip, comprising a flow channel through which a sheath liquid and a sample liquid can flow, and a sample liquid laminar flow introduced into the flow path However, it provides a flow channel structure in which the liquid is fed in a state surrounded by a sheath liquid laminar flow. In this flow channel structure, the flow channel is formed such that the flow channel bottom surface and / or the top surface is an inclined surface so that the area of the vertical cross section with respect to the liquid flow direction becomes gradually smaller according to the liquid flow direction, and the flow channel side wall Has a constricted portion that is gradually constricted in accordance with the liquid feeding direction, and the sheath liquid laminar flow and the sample liquid laminar flow are isotropically contracted while being deflected toward the upper or lower surface of the microchip, and then fed. The
Furthermore, the present invention introduces a sample liquid into a sheath liquid laminar flow that flows through the flow path, and sends the sample liquid in a state in which the periphery of the sample liquid laminar flow is surrounded by the sheath liquid laminar flow. A liquid feeding method is also provided in which liquid laminar flow is isotropically reduced and sent while narrowing down.

  According to the present invention, a microchip capable of obtaining a high analysis accuracy can be provided in which the sample liquid laminar flow can be sandwiched by the sheath liquid laminar flow also in the vertical direction (depth direction) of the flow path.

1 is a simplified top view showing a configuration of a microchip 1 according to the present invention. 2 is a schematic cross-sectional view showing a sheath liquid laminar flow and a sample liquid laminar flow formed in a flow path 11 of the microchip 1. FIG. (A) shows a PP cross section in the enlarged view of FIG. 1, and (B) shows a Q-Q cross section in the enlarged view of FIG. FIG. 4 is a schematic cross-sectional view of a microtubule 14 in which a plurality is bundled. The figure corresponds to the Q-Q section in the enlarged view of FIG. 2 is a schematic cross-sectional view showing a sheath liquid laminar flow and a sample liquid laminar flow upstream (A) and downstream (B) of a narrowing portion 115 of the microchip 1. FIG. (A) shows the R ₁ -R ₁ cross section in FIG. 2, and (B) shows the R ₂ -R ₂ cross section in FIG. FIG. 5 is a schematic cross-sectional view showing a configuration of a narrowing unit 115 in which an area of a vertical cross section with respect to a liquid feeding direction is gradually reduced in accordance with a liquid feeding direction. 2 is a conceptual diagram illustrating an example of a manufacturing method of a microchip 1. FIG. FIG. 3 is a conceptual diagram for explaining a method for sorting microparticles contained in a sample liquid using the microchip 2 according to the present invention in which microtubes 14 are formed of a metal to which a voltage can be applied. 3 is a schematic cross-sectional view for explaining the arrangement position of a piezoelectric element for forming a sample liquid into droplets in the microchip 2. FIG. 2 is a simplified perspective view showing the configuration of a microchip 2 in which the surface of a detection unit D is recessed. FIG. 3 is a simplified top view showing the configuration of a microchip 3 according to the present invention. FIG. 4 is an enlarged schematic view showing a junction part 117 of the microchip 3. FIG. (A) is a top view, and (B) is a ZX plane cross-sectional view including microtubules 14. It is a mimetic diagram explaining composition of a fluid analysis device (fine particle sorting device) concerning the present invention. It is a simplified perspective view showing a general three-way channel structure (A) and a fluid laminar flow state (B) formed thereby.

  DESCRIPTION OF EXEMPLARY EMBODIMENTS Hereinafter, preferred embodiments for carrying out the invention will be described with reference to the drawings. In addition, embodiment described below shows an example of typical embodiment of this invention, and, thereby, the range of this invention is not interpreted narrowly.

1. Microchip FIG. 1 is a simplified top view showing a configuration of a microchip according to the present invention.

  In FIG. 1, a microchip denoted by reference numeral 1 is provided with a flow path 11 having bent portions 111, 112, 113, 114 that bend approximately 90 degrees. In FIG. 1, reference numeral 12 denotes a sheath liquid inlet for introducing the sheath liquid into the flow path 11, and reference numeral 13 denotes an outlet for discharging the sheath liquid and the like out of the flow path 11. The sheath liquid introduced into the flow path 11 from the sheath liquid inlet 12 is bent by approximately 90 degrees at the bent portions 111, 112, 113, and 114, and is discharged from the outlet 13.

(1-1) Microtubule In the bent portion 112 of the flow channel 11, a microtube 14 for introducing a sample liquid into the sheath liquid laminar flow flowing through the flow channel 11 is disposed. In FIG. 1, reference numeral 15 denotes a sample liquid inlet for introducing the sample liquid into the microtube 14, reference numeral 141 denotes an opening at the end of the microtube 14 on the flow path 11 side, and reference numeral 142 denotes an end of the sample liquid inlet side. Indicates an opening. The sample liquid supplied from the sample liquid inlet 15 to the opening 142 flows through the microtube 14 and is introduced into the sheath liquid laminar flow that flows through the flow path 11 from the opening 141.

  In the microchip 1, the sample liquid is introduced into the sheath liquid laminar flow that flows through the flow path 11 by the microtubule 14 in this manner, so that the sample liquid laminar flow is surrounded by the sheath liquid laminar flow. It is possible to send liquid.

(1-2) Narrowing part In FIG. 1, reference numeral 115 denotes a narrowing part provided in the flow path 11. The narrowing portion 115 is formed so that the area of the vertical cross section with respect to the liquid feeding direction gradually decreases from the upstream side to the downstream side of the flow path. That is, the flow passage side wall of the narrowing portion 115 is formed so as to narrow in the Y-axis direction in the drawing according to the liquid feeding direction, and the narrowing portion 115 can be seen as a weight shape that becomes gradually narrower in top view. With this shape, the narrowing part 115 can narrow the laminar flow width of the sheath liquid laminar flow and the sample liquid laminar flow in the Y-axis direction in the drawing and send the liquid. Further, the narrowing portion 115 is formed so that the bottom surface of the flow path becomes an inclined surface that increases in the depth direction (Z-axis direction in the figure) from upstream to downstream, and the laminar flow width also in the same direction. Can be narrowed down (detailed below).

2. FIG. 2 is a schematic diagram showing a sheath liquid laminar flow and a sample liquid laminar flow formed in the flow path 11. FIG. 2A is a schematic cross-sectional view corresponding to the PP cross section in the enlarged view of FIG. 1, and shows the opening 141 of the microtubule 14 and the narrowed portion 115 of the flow path 11 in an enlarged manner. FIG. 2B is a schematic cross-sectional view corresponding to the QQ cross section in the enlarged view of FIG. 1 and shows an enlarged view of the opening 141 as viewed from the downstream side of the flow path.

  As shown in FIG. 2 (A), the sample liquid is introduced into the sheath liquid laminar flow (refer to symbol T in the figure) flowing through the flow path 11 by the microtubule 14, and the sample liquid laminar flow (in the figure). The liquid can be fed in a state surrounded by the sheath liquid laminar flow T.

  FIG. 2 shows a case where the microtubule 14 is disposed so that the center thereof is located coaxially with the center of the flow path 11. In this case, the sample liquid laminar flow S is introduced into the center of the sheath liquid laminar flow T flowing through the flow path 11. The formation position of the sample liquid laminar flow S in the sheath liquid laminar flow T can be arbitrarily set by adjusting the arrangement position of the microtubules 14 in the flow path 11.

  FIG. 2 shows the case where the microtubules 14 are arranged as one tube. The microtubules 14 are not limited to this. For example, as shown in FIG. 3, a plurality of tubes (four in the drawing) may be bundled to form a bundle. By making the microtubules into a bundle, for example, a sample liquid can be introduced from any one of the microtubules 14a, 14b, 14c, and 14d, and a solvent other than the sample liquid and the sheath liquid can be introduced from the other. FIG. 3 shows a case where four microtubes 14a, 14b, 14c, and 14d are integrally formed to form a bundle.

  More specifically, for example, a sample liquid containing microparticles is introduced from the microtubule 14a, and a solution containing a substance that can react with the microparticles is introduced from the microtubules 14b, 14c, and 14d, respectively, into the flow path 11. It is conceivable to carry out the reaction between the fine particles and the substance in the laminar flow that is formed. Examples of the substance capable of reacting with the microparticle include an antibody that binds to the surface of the microparticle, a compound that chemically reacts with the microparticle, and the like.

  As will be described later, when a solution containing microparticles as a sample liquid is passed through the flow path to perform optical analysis and fractionation of the microparticles, the sample liquid is also formed on the surface of the microparticles during the formation of the sample liquid laminar flow. By introducing a binding antibody, it is possible to analyze and sort the microparticles based on the fluorescent label labeled on the antibody bound to the microparticles. In addition, if a compound that chemically reacts with the microparticles is introduced, the reaction between the microparticles and the compound can be detected in the flow path 11, and analysis and fractionation of the microparticles can be performed based on the presence or absence of the reaction. .

  The number of microtubules to be bundled can be two or more, and may be arbitrarily set according to the number of sample liquids and solvents to be introduced. In addition, a configuration for supplying each sample solution and solvent like the sample solution inlet 15 is provided in the opening on the opposite side to the flow channel 11 side end of each microtubule.

3. Narrowing of the laminar flow width by the narrowing portion The narrowing portion 115 is formed such that the area of the vertical cross section with respect to the liquid feeding direction gradually decreases from the upstream side to the downstream side of the flow path. That is, as shown in FIG. 2A, the narrowing portion 115 is formed such that the bottom surface of the flow path becomes an inclined surface that increases in the Z-axis direction in the drawing from upstream to downstream. With this shape, the laminar flow width and the sample liquid laminar flow sent to the narrowing portion 115 are narrowed in the Z-axis direction in the figure while being deflected to the upper surface side of the microchip 1.

FIG. 4 is a schematic diagram showing the sheath liquid laminar flow and the sample liquid laminar flow upstream (A) and downstream (B) of the narrowing part 11. 4A is a schematic cross-sectional view corresponding to the R ₁ -R ₁ cross section in FIG. 2, and FIG. 4B is a schematic cross-sectional view corresponding to the R ₂ -R ₂ cross section in FIG.

  As described with reference to FIG. 1, the narrowing portion 115 is formed in a spindle shape that gradually decreases in the Y-axis direction from upstream to downstream. In addition, as described with reference to FIG. 2, the flow path bottom surface of the narrowing portion 115 is formed as an inclined surface that increases in the Z-axis direction from upstream to downstream. In this way, by forming the narrowing portion 115 so that the area of the vertical cross section perpendicular to the liquid feeding direction gradually decreases from the upstream side to the downstream side of the flow path, the sheath liquid laminar flow T and the sample liquid laminar flow S are While narrowing down the laminar flow width in the Z-axis direction, the liquid can be sent while being deflected to the upper surface side of the microchip 1 (Z-axis positive direction in FIG. 4). That is, the sheath liquid laminar flow T and the sample liquid laminar flow S shown in FIG. 4 (A) are sent in the narrowing part 115 with the laminar flow width narrowed as shown in FIG. 4 (B).

  In this way, by narrowing the laminar flow width of the sheath liquid laminar flow and the sample liquid laminar flow, for example, a solution containing microparticles as the sample liquid is allowed to flow through the flow path, and the microparticle optical When performing analysis, it becomes possible to irradiate the measurement light to the fine particles in the narrowed sample liquid laminar flow with high accuracy. In particular, the narrowing unit 115 narrows the laminar flow width of the sample liquid laminar flow not only in the horizontal direction (Y-axis direction in FIG. 1) of the microchip 1 but also in the vertical direction (Z-axis direction in FIG. 2). Therefore, the focus position of the measurement light in the depth direction of the flow path 11 can be precisely matched with the flow position of the fine particles. For this reason, it is possible to obtain high measurement sensitivity by irradiating fine particles with measurement light with high accuracy.

  Such narrowing of the laminar flow width of the sheath liquid laminar flow and the sample liquid laminar flow can also be performed by forming both the channel bottom surface and the top surface of the narrowing portion 115 as inclined surfaces. Further, as shown in FIG. 5A, the narrowing portion 115 may form the upper surface (and / or the bottom surface) of the flow channel in a stepped shape from upstream to downstream. In this case, the narrowing portion 115 is formed in a stepped shape that gradually decreases in the Y-axis direction even when viewed from above. As described above, if the laminar flow width is narrowed by forming the area of the vertical cross section of the narrowing portion 115 so as to gradually decrease from the upstream side to the downstream side of the flow path, The benefits of

  As will be described later, the narrowed portion 115 and the like disposed on the microchip 1 is formed by wet etching or dry etching of a glass substrate layer, or by nanoimprinting, injection molding, or cutting of a plastic substrate layer. . At this time, if the shape of the narrowed portion 115 is a stepped shape rather than an inclined surface, the narrowed portion 115 can be easily molded, and in particular, molding by machining or stereolithography can be easily performed.

  For example, in the case of machining, in order to form the narrowed portion 115 as an inclined surface, it is necessary to reciprocate the drill many times in units of several μm, and this is very laborious. Also, wear of the drill is likely to proceed, and burrs may occur at the cutting site. On the other hand, if the narrowing portion 115 is formed in a stepped shape having only a few steps, cutting is easy, wear of the drill is small, and burrs are hardly generated. Also, in the case of stereolithography, if the narrowing part 115 is formed in a stepped shape with only a few steps, the number of iterations of the CAD process and stereolithography process can be greatly reduced, and the production time and cost can be reduced. .

  When narrowing down by narrowing the area of the vertical section with respect to the liquid feeding direction of the narrowing portion 115 from the upstream to the downstream of the flow path, the vertical cross-sectional area is reduced after narrowing as shown in FIG. Even an area corresponding to the laminar flow width can be reduced in one step. Also in this case, it has been confirmed that the sheath liquid laminar flow T and the sample liquid laminar flow S can be narrowed down in the Y-axis and Z-axis directions without causing turbulent flow.

  Here, if the flow path 11 is formed as a sufficiently thin flow path and the sample liquid is introduced into the sheath liquid laminar flow that flows through the flow path 11 using the microtubule 14 having a small diameter, the laminar flow is It is considered possible to form a sheath liquid laminar flow and a sample liquid laminar flow with narrowed widths. However, in this case, by reducing the diameter of the microtubule 14, there may be a problem that the microparticles contained in the sample liquid are clogged in the microtubule 14.

  In the microchip 1, the narrowed portion 115 is provided, so that the sample liquid laminar flow and the sheath liquid laminar flow are formed using the microtubule 14 having a diameter sufficiently larger than the diameter of the microparticles contained in the sample liquid. After performing, the laminar flow width can be narrowed down. Therefore, it is possible to solve the problem of the clogging of the microtubule 14 as described above.

  In the present invention, “microparticles” widely include living body-related microparticles such as cells, microorganisms, and liposomes, or synthetic particles such as latex particles, gel particles, and industrial particles.

  Biologically relevant microparticles include chromosomes, liposomes, mitochondria, organelles (organelles) that constitute various cells. The cells of interest include animal cells (such as blood cells) and plant cells. Microorganisms include bacteria such as Escherichia coli, viruses such as tobacco mosaic virus, and fungi such as yeast. Furthermore, biologically relevant microparticles may include biologically relevant polymers such as nucleic acids, proteins, and complexes thereof. The industrial particles may be, for example, an organic or inorganic polymer material, a metal, or the like. Organic polymer materials include polystyrene, styrene / divinylbenzene, polymethyl methacrylate, and the like. Inorganic polymer materials include glass, silica, magnetic materials, and the like. Metals include gold colloid, aluminum and the like. The shape of these fine particles is generally spherical, but may be non-spherical, and the size and mass are not particularly limited.

  The inner diameter of the microtube 14 can be appropriately set according to the diameter of the microparticles contained in the sample liquid to be analyzed. For example, when blood is used as a sample solution and blood cell analysis is performed, a suitable inner diameter of the microtubule 14 is about 10 to 500 μm. Further, the width and depth of the flow path 11 may be appropriately set according to the outer diameter of the microtube 14 reflecting the diameter of the microparticles to be analyzed. For example, when the inner diameter of the microtubule 14 is about 10 to 500 μm, the width and depth of the flow path 11 are each preferably about 100 to 2000 μm. In addition, the cross-sectional shape of the microtubule can be an arbitrary shape such as an ellipse, a quadrangle, or a triangle other than a circle.

The laminar flow width of the sheath liquid laminar flow and the sample liquid laminar flow before narrowing in the narrowing portion 115 can vary depending on the width and depth of the channel 11 and the diameter of the microtube 14, but the narrowing portion It is possible to narrow down to an arbitrary laminar flow width by appropriately adjusting the area of the vertical section of 115 with respect to the liquid feeding direction. For example, in FIG. 2, the flow path length of the narrow-down section 115 L, if the inclination angle of the channel bottom was theta _Z, the laminar flow widths of the sheath liquid laminar flow T and the sample liquid laminar flow S in the narrow-down section 115 The narrowing width is L · tanθ _Z. Therefore, it is possible to set any narrowing width by suitably adjusting the channel length L and the inclination angle theta _Z. Further, in FIG. 1, the narrowing angles in the Y-axis direction of the narrowed portion 115 flow path side wall are set as θ _Y1 and θ _Y2 respectively, and these are formed to be equal to the above θ _Z , thereby allowing FIGS. 4 (A) and (B). As shown in FIG. 5, the sheath liquid laminar flow T and the sample liquid laminar flow S can be narrowed down by isotropic reduction.

4). Manufacturing Method of Microchip 1 The material of the microchip 1 can be glass or various plastics (PP, PC, COP, PDMS). When the analysis using the microchip 1 is performed optically, a material having optical transparency, low autofluorescence, and low wavelength dispersion is selected because of low auto-fluorescence.

  In order to maintain the light transmittance of the microchip 1, it is desirable to stack a so-called hard coat layer used for an optical disc on the surface thereof. If dirt such as fingerprints adheres to the surface of the microchip 1, particularly the surface of the light detection unit (see “detection unit D” in FIG. 7 to be described later), the amount of transmitted light may decrease and the optical analysis accuracy may decrease. By laminating a hard coat layer excellent in transparency and antifouling property on the surface of the microchip 1, it is possible to prevent this deterioration in analysis accuracy.

  The hard coat layer can be formed using a commonly used hard coat agent, for example, using a UV curable hard coat agent to which a fingerprint adhesion preventing agent such as a fluorine-based or silicon-based antifouling additive is added. Film can be formed. JP-A-2003-157579 discloses a polyfunctional compound (A) having two or more polymerizable functional groups that can be polymerized by active energy rays, an organic group having a mercapto group, and a hydrolyzable group as a hard coding agent. Alternatively, active energy ray curability containing modified colloidal silica (B) having an average particle diameter of 1 to 200 nm and surface-modified with a mercaptosilane compound having a hydroxyl group bonded to a silicon atom, and a photopolymerization initiator (C) Composition (P) is disclosed.

  Molding of the flow path 11 and the like disposed on the microchip 1 can be performed by wet etching or dry etching of a glass substrate layer, or by nanoimprinting, injection molding, or cutting of a plastic substrate layer. Then, the microchip 1 can be formed by covering and sealing the substrate layer formed with the flow path 11 and the like with a substrate layer of the same material or a different material.

  FIG. 6 is a conceptual diagram illustrating an example of a manufacturing method of the microchip 1. The microchip 1 can be easily manufactured simply by forming a single substrate layer by injection molding using a mold or the like. 6 is a schematic cross-sectional view corresponding to the P-P cross section in the enlarged view of FIG.

  First, with respect to the substrate layer 1a, a mold having the shape of the flow path 11 having the bent portions 111 to 114 and the narrowing portion 115 and the shape of the sample inlet 15 or the like is set in an injection molding machine, and the substrate layer 1a Perform shape transfer. On the injection-molded substrate layer 1a, the shape of the flow path 11 having the bent portions 111 to 114 and the narrowed portion 115, the shape of the sample inlet 15, and the like are formed (see FIG. 6A).

  Next, as shown in FIG. 6B, the microtubules 14 are arranged. The microtubule 14 is disposed so as to be fitted in a groove formed so as to communicate between the sample inlet 15 and the channel 11, and the sample liquid introduced into the sample inlet 15 is channeled by the microtubule 14. Arranged to be fed into the inside.

  After the arrangement of the microtubules 14, as shown in FIG. 6C, the substrate layer 1b is bonded to the substrate layer 1a. For bonding the substrate layer 1b to the substrate layer 1a, a conventionally known method can be appropriately used. For example, heat fusion, adhesive, anodic bonding, bonding using an adhesive sheet, plasma activated bonding, ultrasonic bonding, or the like can be used as appropriate. In FIG. 6C, the symbol c indicates an adhesive for fixing the microtubule 14 to the substrate layers 1a and 1b. This adhesive c also serves to seal the groove in which the microtube 14 is fitted and to separate the sample inlet 15 and the flow path 11. As a result, the sample inlet 15 and the channel 11 are brought into communication only through the inside of the microtubule 14, and the sample liquid introduced into the sample inlet 15 is fed into the channel 11 by the microtube 14. It becomes like this.

  The microchip 1 obtained by the above method can be used regardless of the front and back. Therefore, the microchip 1 shown in FIG. 6C can be used with the substrate layer 1a on the upper surface and the substrate layer 1b on the lower surface. In the state of FIG. 6C, the narrowing portion 115 is formed as an inclined surface whose bottom surface of the flow path gradually increases from upstream to downstream. However, if the microchip 1 is turned upside down, the narrowing portion 115 is narrowed down. The portion 115 can be viewed as an inclined surface whose upper surface of the flow path becomes lower in the flow path depth direction from upstream to downstream. In this case, the laminar flow width is narrowed down while the sheath liquid laminar flow and the sample liquid laminar flow sent to the narrowing part 115 are deflected to the lower surface side of the microchip 1. The same applies to the case where the upper surface (and / or the bottom surface) of the narrowing portion 115 is formed in a staircase shape as described with reference to FIG.

  The microtube 14 may be a tube made of metal, glass, ceramics, or various plastics (PP, PC, COP, PDMS), and the material is not particularly limited. As an example, a silica tube can be employed as the microtubule 14. A silica tube having an inner diameter of several tens to several hundreds of μm is commercially available, and a tube having a suitable diameter can be used as appropriate. Since the silica tube has high heat resistance, it is possible to form a stable microchip when the substrate layer is thermocompression bonded.

  When a metal tube is employed as the microtube 14, an electric charge can be imparted to the sample solution flowing through the microtube 14 through the inside. Thereby, for example, the “particulate measurement site for measuring the introduced particulates” and the two or more particulate separations for separating and collecting the particulates installed downstream of the particulate measurement site described in Patent Document 1 above The microchip 1 is provided with a flow path and two or more electrodes for controlling the moving direction of the fine particles installed in the vicinity of the flow path opening from the fine particle measurement site to the fine particle separation flow path, and the fine particles are separated. It becomes possible.

  Further, like the microchip 3 to be described later, the microchip according to the present invention joins the flow path 11 from at least one side, and introduces either a gas or an insulating liquid into the flow path 11. A fluid inlet can be provided. This fluid introduction part is also formed by wet etching, dry etching, nanoimprinting, injection molding, and equipment processing, like the flow path 11 and the like.

5. Microchip separation method using microchip (5-1) Microchip 2
FIG. 7 is a conceptual diagram for explaining a method of sorting the microparticles contained in the sample liquid using the microchip 2 in which the microtubes 14 are formed of a metal to which a voltage can be applied. The microchip 2 has the same configuration as that of the microchip 1 except for the configuration specifically described below.

  The flow path 11 of the microchip 2 includes branch flow paths 11a and 11b that branch at the branch section 116 downstream of the narrowing section 115, and the microparticles contained in the sample liquid introduced into the flow path 11 from the microtube 14 Can be selectively sent to one of the branch channels 11a and 11b.

  In FIG. 7, reference numeral 143 denotes a charging unit that applies a voltage to the microtube 14. The charging unit 143 imparts a positive or negative charge to the sample liquid containing microparticles flowing through the inside. Control of the flow direction of the microparticles in the branching section 116 can be performed based on the charge applied to the sample liquid containing microparticles by the charging section 143.

  More specifically, for example, by introducing a slight pressure difference to the microtube 14 at the time of introducing the sample liquid into the flow path 11, as shown in FIG. Each of the droplets P is sent into a sheath liquid laminar flow that flows through the flow path 11. At the same time, by switching between positive and negative of the voltage applied to the charging unit 143, a positive or negative charge is imparted to the droplet P sent out in the sheath liquid laminar flow. At this time, in order to electrically insulate the droplets P from each other, it is desirable to use an electrically insulating sheath liquid.

  The method for applying a pressure difference to the microtube 14 is, for example, a method in which a piezoelectric element (microvibration element) that can be microvibrated by being brought into contact with the microtube 14, or facing the inside of the sample liquid inlet 15. A method of disposing a piezoelectric element can be employed.

  FIG. 8 is a view for explaining the arrangement position of the piezoelectric element for making the sample liquid into droplets. The figure is a schematic cross-sectional view corresponding to FIG. Here, the case where the piezoelectric element is disposed on the bottom surface of the sample liquid inlet 15 is shown.

  In the figure, a piezoelectric element denoted by reference numeral 151 is disposed on the bottom surface of the sample liquid inlet 15 so as to face the sample liquid inlet 15. The piezoelectric element 151 is deformed when a voltage is applied, and applies pressure to the sample liquid flowing through the sample liquid inlet 15. This pressure also applies pressure to the sample liquid in the microtubule 14 communicating with the sample liquid inlet 15. At this time, if the piezoelectric element 151 is vibrated using the voltage applied to the piezoelectric element 151 as a pulse voltage and the pressure to the sample liquid in the microtube 14 is periodically changed, the sample liquid becomes droplets and becomes a microtubule. 14 is discharged into the flow path 11.

  Such droplet formation using the piezoelectric element 151 can be performed, for example, in the same manner as ink droplet discharge using a piezoelectric vibration element employed in an ink jet printer. Here, the case where the piezoelectric element 151 is disposed facing the inside of the sample liquid inlet 15 has been described. However, the piezoelectric element 151 is disposed so as to contact the outer wall of the microtube 14, for example, and is deformed. The pressure of the element 151 may be directly applied to the microtube 14 to form a droplet of the sample liquid. The applied signal to the piezoelectric element for applying the pressure difference and the applied signal for applying the voltage to the microtubule 14 are synchronized to form a droplet at an arbitrary timing and charge the droplet. Is possible.

  A pair of electrodes 1161 and 1162 are arranged at the branching portion 116 so as to face both sides of the flow path 11 (see FIG. 7). The electrodes 1161 and 1162 can be positively or negatively charged, and the droplet P is separated from the branch channels 11a and 11b by an electric repulsive force (or suction force) with the electric charge applied to the droplet P. Guide to either. The electrodes 1161 and 1162 may be arranged on the microchip 2 in advance, and are arranged in the microparticle sorting apparatus on which the microchip 2 is mounted so as to be positioned at the branch portion 116 of the mounted microchip 2. It may be provided. In addition, the electrodes 1161 and 1162 can be formed by using a metal tube in the vicinity of the branch portion 116 of the branch flow paths 11a and 11b as in the microchip 3 described later, and function as an electrode.

  The classification of the microparticles is performed based on the result of determining the characteristics of the microparticles in the detection unit indicated by the symbol D in FIG. Here, a case will be described as an example in which the detection unit D is configured as an optical detection system, and the optical characteristics of the microparticles are determined by detecting light generated by laser light irradiation on the microparticles in the introduction path 11. The optical detection system and the microparticle sorting apparatus can be configured in the same manner as a conventional microparticle analysis system using a microchip. Specifically, a laser light source, a condensing lens, a dichroic mirror, a band-pass filter, etc. for condensing and irradiating laser light to fine particles, and light generated from the fine particles by laser light detection are detected. And a detector. As the detector, for example, a PMT (photo multiplier tube), an area imaging device such as a CCD or a CMOS device, or the like is used.

  When the detection unit D is configured as an optical detection system, the surface of the detection unit D is placed on another surface of the microchip 2 as shown in FIG. It is desirable that the surface of the detection part D is recessed to prevent contact with the fingertip or dirt on the surface of the part. 9A shows a case where a depression is formed in the detection portion D portion on the surface of the microchip 2, and FIG. 9B shows a case where a groove including the surface of the detection portion D portion is formed on the surface of the microchip 2. Indicates.

  The parameters for determining the optical properties of the microparticles include forward scattered light that measures the size of the microparticles, side scattered light that measures the structure, Rayleigh scattering, It can be scattered light such as Mie scattering or fluorescence. The detection unit D analyzes light detected by these parameters and determines whether or not the microparticles have predetermined optical characteristics.

  For example, when the charge imparted by the charging unit 143 to the droplet P of the sample liquid containing microparticles is positive, if it is determined that the microparticles have predetermined optical characteristics, the electrode 1161 is Negatively, the electrode 1162 is positively charged, and the droplet P is guided to the branch channel 11a by an electric repulsive force. Conversely, when it is determined that the microparticles do not have the predetermined optical characteristics, the electrode 1161 is positively charged and the electrode 1162 is negatively charged, and the droplet is separated by the electric repulsive force 11b. Lead to. As a result, only fine particles having predetermined optical characteristics can be guided to the branch channel 11a and separated.

  In this way, in the microchip 2, the microtube 14 is made of metal, so that the sample liquid droplet P containing microparticles is sent to the center of the sheath liquid laminar flow T flowing through the flow path 11 at the same time. A charge can be imparted, and fine particles can be separated based on this charge.

  In the microchip 2, the narrowing portion 115 narrows the laminar flow width of the sheath liquid laminar flow and the sample liquid droplet P in the horizontal direction and the vertical direction of the microchip 2, and sends the liquid to the detection unit D. The focus position of the measurement light can be precisely matched with the flow position of the fine particles. For this reason, it is possible to accurately irradiate the microparticles with the measurement light, and to detect the optical characteristics of the microparticles with high sensitivity.

  Furthermore, in the microchip 2, the micropipe 14 and the narrowing unit 115 can arrange the droplets P of the sample liquid containing the microparticles in a substantially single line in the narrowed laminar flow. By arranging the droplets P in approximately one row, it is easy to apply an electrical repulsive force from the electrodes 1161 and 1162 to the droplets P including minute particles having predetermined characteristics in the branching portion 116. In addition, since the laminar flow width in the branch portion 116 is sufficiently narrowed, the droplet P can be guided to the branch flow channel 11a or 11b only by applying a small repulsive force by the electrodes 1161 and 1162.

  Although the case where the detection unit D is configured as an optical detection system and the characteristics of the microparticles are optically measured has been described here, the characteristics of the microparticles can be measured electrically or magnetically. That is, when measuring the electrical properties and magnetic properties of the microparticles, the microelectrodes are arranged in the detection unit D, for example, the resistance value, the capacitance value (capacitance value), the inductance value, the impedance, and the electric field between the electrodes. A change value or the like, for example, a magnetization, a magnetic field change, a magnetic field change, or the like related to a fine particle is measured. Two or more of these characteristics can be measured simultaneously. For example, when measuring a magnetic bead labeled as a fine particle with a fluorescent dye, optical characteristics and magnetic characteristics are measured simultaneously.

  According to the microchip 2, even when measuring the electrical or magnetic properties of the microparticles, the measurement position of the microelectrode disposed in the detection unit D and the microparticle flow position are precisely matched, It is possible to detect the characteristics of fine particles with high sensitivity.

(5-2) Microchip 3
Next, the microchip 3 provided with a fluid introduction part that joins the flow path 11 from at least one side and introduces either a gas or an insulating liquid into the flow path 11 is used in the sample liquid. A method for separating the contained fine particles will be described.

  FIG. 10 is a simplified top view showing the configuration of the microchip 3 according to the present invention. The microchip 3 has the same configuration as the microchip 1 and the microchip 2 except for the configuration specifically described below.

  In FIG. 10, reference numerals 91 and 92 denote fluid introduction portions for introducing either a gas or an insulating liquid into the flow path 11. The fluid introducing portions 91 and 92 are provided with fluid inlets 911 and 912 that communicate with the flow path 11 at one end and are supplied with fluid at the other end. Gas or insulating liquid (hereinafter referred to as “gas” or the like) supplied from the fluid inlets 911 and 912 to the fluid inlets 91 and 92 by a pressurizing pump (not shown) enters the flow path 11 at the junction indicated by reference numeral 117. be introduced.

  In the microchip 3, the liquid flowing through the flow channel 11 is divided by the fluid introduced from the fluid introducing portions 91 and 92 into the confluence portion 117, and is formed into droplets, and the branch portions 116 of the branch flow channels 11a and 11b are separated. Can be sent to.

  FIG. 11 is an enlarged schematic diagram showing the junction part 117. 11A is a top view, and FIG. 11B is a ZX plane cross-sectional view including the microtubule 14. The figure shows a case where the sheath liquid laminar flow T and the sample liquid laminar flow S sent to the confluence part 117 via the microtube 14 and the narrowing part 115 are divided into droplets.

  That is, when a gas or the like is introduced at a predetermined timing from the fluid introduction portions 91 and 92 to the sheath liquid laminar flow T and the sample liquid laminar flow S that are fed in the confluence portion 117, the introduced gas or the like The sheath liquid laminar flow T and sample liquid laminar flow S are divided into droplets as shown in the figure. As a result, the sheath liquid laminar flow T and the sample liquid laminar flow S can be formed into droplets in the flow path 11 and sent to the branching portion 116 (see droplet P in FIG. 11). Then, if a liquid containing microparticles is allowed to flow as a sample liquid and a gas or the like is introduced at a predetermined timing, droplets P containing one or a predetermined number of microparticles can be formed.

  Here, FIG. 10 and FIG. 11 show the case where one fluid introduction part is provided on each side of the flow path 11, but one gas introduction part is provided on at least one side of the flow path 11. It only has to be. Furthermore, two or more fluid introduction parts can be joined at the joining part 117. 10 and 11, the fluid introduction part is joined at a right angle to the flow path 11, but the joining angle of the fluid introduction part can be arbitrarily set.

  In the microchip 2, a pair of electrodes 1161 and 1162 are arranged at the branching portion 116 so as to face both sides of the flow path 11. On the other hand, the microchip 3 employs a configuration in which the vicinity of the branch portion 116 of the branch flow paths 11a and 11b is formed as metal tubes 1163 and 1164 and functions as electrodes. The metal tubes 1163 and 1164 can be positively or negatively charged, and the droplets P are separated from the branch flow paths 11a, 11a by the electric repulsive force (or suction force) with the electric charge applied to the droplets P. Guide to one of 11b.

  That is, as described in the microchip 2, when the charge imparted by the charging unit 143 (see FIG. 7) to the droplet P of the sample liquid containing microparticles is positive, the microparticles have predetermined optical characteristics. If it is determined that the metal tube 1163 is negative, the metal tube 1163 is negatively charged and the metal tube 1164 is positively charged, and the droplet P is guided to the branch channel 11a by an electric repulsive force. Conversely, when it is determined that the microparticles do not have the predetermined optical characteristics, the metal tube 1163 is charged positively and the metal tube 1164 is charged negatively, and the droplet is discharged by an electric repulsive force. Guide to the branch channel 11b. In the figure, reference numerals 131 and 132 denote outlets for taking out the microparticles sorted into the branch channels 11a and 11b, respectively, from the chip.

  As described above, in the microchip 3, by providing the fluid introduction portions 91 and 92, the sample liquid containing the microparticles can be formed into droplets and at the same time, the microtubule 14 can be charged, and based on this charge It is possible to perform fractionation of fine particles.

  In order to maintain the electric charge of the sample liquid formed into droplets in the liquid passage 11, it is preferable to use a gas for the fluid introduced from the fluid introduction portions 91 and 92. At this time, when the sheath liquid laminar flow and the sample liquid laminar flow in the liquid channel 11 are not completely separated and the adjacent liquid droplets are partially communicated, the charge of the liquid droplets disappears. In this case, there is a possibility that control of the flow direction in the branching portion 116 becomes impossible or inaccurate. Therefore, in order to completely divide the sheath liquid laminar flow and the sample liquid laminar flow by the introduced gas and maintain the insulation between the divided liquid droplets, the surface of the flow path 11 (especially downstream of the confluence portion 117). It is desirable to provide water repellency. It is also effective to impart electric insulation to the surface of the flow path 11 to prevent the movement of charges between the divided droplets. The electrical insulation can be imparted, for example, by applying or forming a film having an insulation property on the channel surface. In addition, by flowing a liquid having an insulating property such as ultrapure water on the surface of the flow path, it is possible to prevent energization between the droplets.

  Further, in order to maintain the electric charge of the sample that has been formed into droplets in the liquid passage 11, an electrically insulating liquid (“insulating liquid”) may be used as the fluid. For example, the above-described ultrapure water is used as the insulating liquid. Thereby, the movement of the electric charge between the divided droplets can be prevented.

6). Fluid analyzer (fine particle sorting device)
FIG. 12 is a schematic diagram illustrating the configuration of the fluid analyzer according to the present invention. This fluid analysis device is suitably used as a microparticle sorting device that analyzes the characteristics of microparticles and sorts the microparticles based on the analysis results. Hereinafter, each configuration of the fluid analysis device (microparticle sorting device) will be described by taking as an example the case where the microchip 3 is mounted.

  The microparticle analyzer shown in FIG. 12 includes an optical detection system (irradiation unit 102, detection unit 103) for detecting microparticles flowing inside the flow channel 11 upstream of the confluence unit 117 of the microchip 3, and a confluence. An optical detection system (irradiation unit 104, detection unit 105) for determining the optical characteristics of the microparticles downstream of the unit 117, a pressure pump 106 for supplying gas or the like to the fluid inlets 911, 921 of the microchip 3, Is provided. In the figure, reference numeral 101 denotes an overall control unit for controlling the voltages applied to the optical detection system and the pressure pump, and the microtube 14 and the metal tubes 1163 and 1164.

  Further, the microparticle sorting apparatus includes a liquid supply unit (not shown), and supplies a sheath liquid laminar flow from the sheath liquid inlet 12 of the microchip 3 and a sample liquid laminar flow from the sample liquid inlet 15. The sheath liquid and the sample liquid supplied to the microchip 3 are joined together with the sample liquid laminar flow surrounded by the sheath liquid laminar flow and the laminar flow width narrowed by the microtubule 14 and the constriction unit 115. The solution is fed to the unit 117 (see FIG. 2).

(6-1) Detection of microparticles The microparticle sorting apparatus includes an optical detection system for optically detecting microparticles contained in the sample liquid laminar flow upstream of the confluence unit 117. This optical detection system can be configured in the same manner as a conventional microparticle analysis system using a microchip. Specifically, an irradiation unit 102 composed of a laser light source, a condensing lens for condensing and irradiating laser light to fine particles, and the light generated from the fine particles by irradiating the laser light with a dichroic mirror, a band And a detection unit 103 that detects using a pass filter or the like. The detection unit includes, for example, a PMT (photo multiplier tube), an area imaging device such as a CCD or a CMOS device, or the like.

  In the microchip 3, the laminar flow width of the sheath liquid laminar flow and the sample liquid laminar flow can be narrowed by the narrowing unit 115, and the liquid can be fed to the laser light irradiation site of the irradiation unit 102. For this reason, the focal position of the laser beam from the irradiation unit 102 and the flow position of the microparticles in the flow channel 11 can be precisely matched. Thereby, it is possible to detect the fine particles with high sensitivity by irradiating the fine particles with laser light with high accuracy.

  Light generated from the microparticles detected by the detection unit 103 is converted into an electric signal and output to the overall control unit 101. The light detected by the detection unit 103 may be forward scattered light or side scattered light of fine particles, scattered light such as Rayleigh scattering or Mie scattering, or fluorescence.

  The overall control unit 101 detects microparticles in the sample liquid laminar flow sent through the flow path 11 based on the electric signal. Then, by controlling the pressurizing pump 106 at a predetermined timing, gas or the like is introduced from the fluid inlets 911, 912 and the fluid introducing portions 91, 92 to the joining portion 117, and the sheath liquid laminar flow and the sample liquid laminar flow are divided. It is formed into droplets (see FIG. 11).

  As for the timing of introducing the fluid into the merging portion 117, for example, every time one minute particle is detected based on the electric signal from the detecting portion 103, gas or the like is introduced after a certain time. The time from the detection of the microparticles to the introduction of the fluid is defined by the distance between the laser beam irradiation site of the irradiation unit 102 and the confluence unit 117 and the liquid feeding speed of the sample liquid in the flow path 11. After appropriately adjusting this time, a sheath liquid laminar flow and a sample liquid laminar flow are divided for each microparticle by introducing gas or the like into the confluence portion 117 each time one microparticle is detected, It can be made into droplets.

  In this case, each droplet contains one microparticle, but the number of microparticles contained in each droplet can be arbitrarily set by appropriately adjusting the timing of introducing the fluid into the junction 117. Can be set. That is, if a gas or the like is introduced every time a predetermined number of fine particles are detected, the fine particles can be made into droplets for each number.

  Here, the case where the detection for detecting the microparticles contained in the sample liquid laminar flow is performed by the optical detection system has been described. Detection of microparticles is not limited to optical means, and can also be performed by electrical or magnetic means. In the case of detecting fine particles electrically or magnetically, a microelectrode is arranged upstream of the junction part 117, for example, a resistance value, a capacitance value (capacitance value), an inductance value, an impedance, and a change value of an electric field between the electrodes. Or, for example, magnetization, change in magnetic field, change in magnetic field, etc. relating to fine particles are measured. Then, by outputting the measurement result as an electrical signal, the overall control unit 101 detects fine particles based on this signal.

  In the microchip 3, even when detecting microparticles electrically or magnetically, the measurement position of the arranged microelectrode and the flow position of the microparticle are precisely matched to detect the microparticle with high sensitivity. Is possible.

  Here, in the case where the microparticles are magnetic, the microparticles in the branching portion 116 based on magnetic force can be obtained by configuring the metal tubes 1163 and 1164 of the microchip 3 as magnetic poles. It is also conceivable to control the direction of flow.

(6-2) Determination of optical characteristics of microparticles The microparticle sorting apparatus includes an optical detection system including the irradiation unit 104 and the detection unit 105 even downstream of the merging unit 117. This optical detection system is for determining the characteristics of the microparticles, but the configuration itself of the irradiation unit 104 and the detection unit 105 can be the same as that of the irradiation unit 102 and the detection unit 104 described above.

  The irradiation unit 104 irradiates the fine particles contained in the droplets formed in the merging unit 117 with laser light. Thereby, the light generated from the fine particles is detected by the detection unit 105. The light detected by the detection unit 103 may be forward scattered light or side scattered light of fine particles, scattered light such as Rayleigh scattering or Mie scattering, or fluorescence, and these are converted into an electrical signal to be controlled by the overall control unit 101. Is output.

  Based on the input electrical signal, the overall control unit 101 determines the optical characteristics of the microparticles using the microparticles as parameters, such as forward scattered light, side scattered light, scattered light such as Rayleigh scattering and Mie scattering, and fluorescence. The parameters for determining the optical properties are forward scattered light when determining the size of the microparticles and side scattered light when determining the structure according to the target microparticles and the purpose of sorting. Fluorescence is employed when determining the presence or absence of a fluorescent substance labeled on the microparticles.

  The overall control unit 101 analyzes the light detected by these parameters and determines whether or not the microparticles have predetermined optical characteristics.

  Although the case where the characteristics of the microparticles contained in the droplet are optically determined has been described here, the characteristics of the microparticles can also be determined electrically or magnetically. When measuring the electrical properties and magnetic properties of the microparticles, a microelectrode is arranged downstream of the confluence portion 117. For example, a resistance value, a capacitance value (capacitance value), an inductance value, an impedance, and an electric field between the electrodes. A change value or the like, for example, a magnetization, a magnetic field change, a magnetic field change, or the like related to a fine particle is measured. Two or more of these characteristics can be measured simultaneously. For example, when measuring a magnetic bead labeled as a fine particle with a fluorescent dye, optical characteristics and magnetic characteristics are measured simultaneously.

(6-3) Sorting of microparticles The overall control unit 101 controls the voltage applied to the microtube 14 and the metal tubes 1163 and 1164 based on the determination result of the characteristics of the microparticles, thereby obtaining predetermined characteristics. The droplets containing the provided microparticles are guided to one of the branch flow paths 11a and 11b, thereby sorting and sorting the microparticles.

  For example, when it is determined that the microparticles contained in the droplet have predetermined characteristics, if a microcharge is applied to the droplet including the microparticle by the microtube 14, the metal The tube 1163 is negatively charged and the metal tube 1164 is positively charged. As a result, the moving direction of the droplet in the branching portion 116 is guided to the branching channel 11a, and the microparticles having a predetermined characteristic are collected from the outlet 131.

  Conversely, when it is determined that the microparticles contained in the droplet do not have a predetermined characteristic, the droplet is obtained by charging the metal tube 1163 positively and the metal tube 1164 negatively. To the branch channel 11b, and the microparticles are discharged from the outlet 132.

  As described above, in the microparticle sorting apparatus according to the present invention, the charge applied to the droplet containing the microparticle and the voltage applied to the electrode are appropriately switched between positive and negative according to the determination result of the characteristics of the microparticle. By controlling, it is possible to guide and sort microparticles into one arbitrarily selected branch channel.

  Here, an optical detection system (irradiation unit 102, detection unit 103) for detecting microparticles in the sample liquid laminar flow flowing through the flow path 11 to form droplets, and microparticles contained in the droplets Although the optical detection system (irradiation unit 104, detection unit 105) for determining the optical characteristics of these is separately provided upstream and downstream of the merging unit 15, these can also be configured integrally.

1, 2, 3 Microchip
1a, 1b, 2a, 2b substrate layer
11 Flow path
11a, 11b Branch channel
111, 112, 113, 114 Turned part
115 Refinement part
116 Branch
1161, 1162 electrodes
1163, 1164 Metal tube
117 Junction
12 Sheath fluid inlet
13, 131, 132 outlet
14, 14a, 14b, 14c, 14d microtubule
141 opening (channel side)
142 Opening (sample liquid inlet side)
143 Charged part
15 Sample solution inlet
151 Piezoelectric element
91, 92 Fluid introduction part
911, 921 Fluid inlet
102, 104 Irradiation part
103, 105 detector
101 Overall control unit
106 Pressure pump
c Adhesive
D detector
P Sample liquid droplet
S Sample liquid laminar flow
T sheath liquid laminar flow

Claims (8)

A flow path through which the sheath liquid and the sample liquid can flow;
The sample liquid laminar flow introduced into the flow path is sent in a state surrounded by a sheath liquid laminar flow,
The flow path is formed such that the flow path bottom surface and / or the top surface is an inclined surface so that the area of the vertical cross-section with respect to the liquid feed direction gradually decreases according to the liquid feed direction, and the flow path side walls gradually increase according to the liquid feed direction. Having a narrowed constriction,
The sheath liquid laminar flow and the sample liquid laminar flow are isotropically reduced while being deflected to the upper surface or the lower surface side of the microchip by the constriction part, and are sent after being narrowed .
A microchip in which an inclination angle of a channel bottom surface and / or an upper surface of the narrowing portion and a narrowing angle of a channel side wall are formed equally . A branch channel that branches downstream of the narrowed portion of the channel,
The electrode disposed in the branch portion of the branched flow paths, conductive claim 1, wherein microchip load can control the feeding direction of the branch portion of the applied sample solution. A fluid introduction part that merges from at least one side upstream of the branch part of the flow path and introduces either a gas or an insulating liquid into the flow path;
The microchip according to claim 2, wherein the sheath liquid laminar flow and the sample liquid laminar flow flowing in the flow path are divided by the fluid introduced from the fluid introducing portion, and the liquid is formed into droplets and sent. The microchip according to claim 3 , wherein the microparticles can be separated by controlling a liquid feeding direction in the branch portion of the sample liquid containing the microparticles that are formed into droplets and are charged. A channel structure formed inside the microchip,
A flow path through which the sheath liquid and the sample liquid can flow;
The sample liquid laminar flow introduced into the flow path is sent in a state surrounded by a sheath liquid laminar flow,
The flow path is formed such that the flow path bottom surface and / or the top surface is an inclined surface so that the area of the vertical cross-section with respect to the liquid feed direction gradually decreases according to the liquid feed direction, and the flow path side walls gradually increase according to the liquid feed direction. Having a narrowed constriction,
The sheath liquid laminar flow and the sample liquid laminar flow are isotropically reduced while being deflected to the upper surface or the lower surface side of the microchip by the constriction part, and are sent after being narrowed .
A flow channel structure in which the inclination angle of the flow channel bottom surface and / or top surface of the narrowing portion and the narrowing angle of the flow channel side wall are formed equally .   A fluid analyzer equipped with the microchip according to claim 1. A microparticle sorting apparatus on which the microchip according to claim 4 is mounted. Sample liquid is introduced into the sheath liquid laminar flow that flows through the flow path inside the microchip, and the sample liquid laminar flow is surrounded by the sheath liquid laminar flow, and is sent.
The sheath liquid laminar flow and the sample liquid laminar flow are sent while being narrowed and narrowed isotropically while deflecting to the upper or lower surface side of the microchip by the narrowing part of the flow path ,
The narrowing portion is formed such that the flow path bottom surface and / or the top surface is an inclined surface so that the area of the vertical cross section with respect to the liquid feeding direction gradually decreases according to the liquid feeding direction, and the flow path side wall gradually increases according to the liquid feeding direction. is confined, the flow channel bottom surface and / or the inclination angle of the upper surface, der Ru liquid transfer method which the constriction angles of the channel side walls are formed equally.

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