Microfluidic device and sample analysis method

Abstract

To provide a microfluidic device which is capable of reducing the generation of air bubbles and improving detection efficiency when forming and heating microdroplets for optical detection.SOLUTION: There is provided a microfluidic device 1 including a flow path 35, and one or more droplet holders 11 connected to the flow path 35. The flow path 35 has a height of more than 0 μm and 30 μm or less.SELECTED DRAWING: Figure 2

Description

[Technical field]

[0001] The present invention relates to a microfluidic device and a sample analysis method using the microfluidic device. This application claims priority to Japanese Patent Application No. 2019-034228, filed on February 27, 2019, the contents of which are incorporated herein by reference. [Background technology]

[0002] In recent years, microwell arrays with various types of fine flow channel structures formed by etching and photolithography techniques used in semiconductor circuit manufacturing, or by fine plastic molding methods, have been studied. The wells of these microwell arrays are used as chemical reaction vessels for carrying out various biochemical or chemical reactions in a minute volume of fluid.

[0003] Materials used for manufacturing microfluidic systems include hard substances such as silicon and glass, various polymer resins such as PDMS (polydimethylsiloxane), and soft substances such as silicone rubber. For example, Patent Documents 1 to 3 and Non-Patent Document 1 describe the use of such microfluidic systems as various microchips or biochips.

[0004] There are known techniques for detecting biomolecules in flow channel devices. For example, in DNA microarray technology, biomolecules are introduced into micropores and reacted with heat to detect the biomolecules. There are also known techniques capable of detecting single biomolecules. Examples of the techniques capable of detecting single molecules include digital measurement techniques such as digital ELISA (Digital Enzyme-Linked ImmunoSorbent Assay), digital PCR (Digital Polymerase Reaction), and digital Invasive Cleavaged Assay (Digital ICA). Digital PCR technology involves dividing a mixture of reagents and nucleic acids into countless tiny droplets for PCR amplification, allowing signals such as fluorescence to be detected from the droplets containing the nucleic acid, and quantifying the amount by counting the droplets in which a signal is detected.

[0005] Methods under consideration for forming microdroplets include a method in which a mixture of reagent and nucleic acid is fragmented using a sealing liquid to form microdroplets, and a method in which a mixture of reagent and nucleic acid is poured into a hole formed on a substrate, and then a sealing liquid is poured in to form microdroplets. [Prior art documents] [Patent documents]

[0006] [Patent Document 1] Patent No. 6183471 [Patent Document 2] Special Publication No. 2014-503831 [Patent Document 3] International Publication No. 2013-151135 [Non-patent literature]

[0007] [Non-Patent Document 1] Kim SH, et al., Large-scale femtoliter droplet array for digital counting of single biomolecules., Lab on a Chip, 12 (23), 4986-4991, 2012. Summary of the Invention [Problem to be solved by the invention]

[0008] However, when minute droplets are formed and heated, and optical detection is performed using fluorescence or the like, air bubbles may be generated inside the flow path, which may impede detection.

[0009] Therefore, an object of the present invention is to provide a microfluidic device that can suppress the generation of bubbles and improve detection efficiency when forming and heating microdroplets and performing optical detection. Another object of the present invention is to provide a sample analysis method that can suppress the generation of air bubbles when forming and heating microdroplets to optically detect a sample, thereby improving the efficiency of sample detection. [Means for solving the problem]

[0010] In order to achieve the above object, the present invention employs the following configuration. [1] A microfluidic device comprising a flow channel and a droplet holder formed in the flow channel, the height of the flow channel being greater than 0 μm and equal to or less than 30 μm. [2] The microfluidic device according to [1], wherein the flow channel has a planar substrate, and the droplet holder is a hole present in the substrate. [3] The microfluidic device according to [1] or [2], wherein a plurality of the droplet holders are present. [4] The microfluidic device according to any one of [1] to [3], further comprising a cover member, wherein the flow channel is a space sandwiched between the cover member and the substrate. [5] The microfluidic device according to any one of [1] to [4], wherein the capacity of each of the droplet holders is from 10 fL to 100 pL. [6] The microfluidic device according to any one of [1] to [5], wherein the total volume of the droplet holder is 0.2 μL or more and 2.0 μL or less. [7] The microfluidic device according to any one of [1] to [6], wherein a ratio of a total volume of the droplet holder to a volume of the flow channel is 5% or more and 40% or less. [8] The microfluidic device according to any one of [2] to [7], wherein the ratio of the depth of the droplet holder to the height of the channel is 3% or more and 150% or less. [9] A microfluidic device described in any one of [2] to [8], wherein the ratio of the total area of ​​the openings of the droplet holder to the unit area of ​​the region in which the droplet holder is formed on the substrate is 23% or more and 90% or less.

[10] A sample analysis method using the microfluidic device described in any one of [1] to [9], comprising: a sample supplying step of supplying an aqueous liquid containing a sample to the flow path and causing the droplet holder to hold the aqueous liquid; a sealing step of introducing a sealing liquid into the flow path to replace the aqueous liquid present in the flow path and enclosing the aqueous liquid in the droplet holder; a reaction step of causing a reaction in the droplet holder to generate a signal for detection; and a detection step of detecting the signal.

[11] The sample analysis method described in

[10] , wherein the sample is a biological molecule.

[12] The sample analysis method according to

[10] or

[11] , wherein in the reaction step, the microfluidic device is heated to cause the reaction, and the heating temperature is 60°C or higher.

[13] The sample analysis method according to any one of

[10] to

[12] , wherein the signal is detected by imaging.

[14] The sample analysis method according to any one of

[10] to

[13] , wherein the signal is fluorescence.

[15] The sample analysis method according to any one of

[10] to

[14] , wherein the reaction is an isothermal reaction.

[0011] Another aspect of the present invention includes the following embodiments.

[16] A microfluidic device comprising a flow channel and one or more droplet holders connected to the flow channel, wherein the height of the flow channel is greater than 0 μm and less than or equal to 30 μm.

[17] The microfluidic device according to

[16] , further comprising a flat substrate, the flow path being located on the flat substrate, and the droplet holder being a hole on the substrate.

[18] The microfluidic device according to

[17] , further comprising a cover member, wherein the flow channel is a space sandwiched between the cover member and the substrate.

[19] A microfluidic device according to

[17] or

[18] , wherein the ratio of the total area of ​​the openings of the droplet holder per unit area of ​​the region in which the droplet holder is formed on the substrate is 23% or more and 90% or less.

[20] The microfluidic device according to any one of

[16] to

[19] , wherein the droplet holder comprises a plurality of droplet holders.

[21] The microfluidic device according to any one of

[16] to

[20] , wherein the volume of each of the droplet holders is from 10 fL to 100 pL.

[22] The microfluidic device according to any one of

[16] to

[21] , wherein the total volume of the droplet holder is 0.2 μL or more and 2.0 μL or less.

[23] The microfluidic device according to any one of

[16] to

[22] , wherein a ratio of a total volume of the droplet holder to a volume of the flow channel is 5% or more and 40% or less.

[24] The microfluidic device according to any one of

[16] to

[23] , wherein a ratio of the depth of the droplet holder to the height of the flow channel is 3% or more and 150% or less.

[25] A method for sample analysis using the microfluidic device described in any one of

[16] to

[24] , comprising the steps of: introducing an aqueous liquid containing a sample into the flow path and retaining the aqueous liquid in the droplet holder; introducing a sealing liquid into the flow path to replace the aqueous liquid present in the flow path and seal the aqueous liquid in the droplet holder; causing a reaction in the droplet holder to generate a signal for detection; and detecting the signal.

[26] The sample analysis method described in

[25] , wherein the sample is a biological molecule.

[27] The sample analysis method described in

[25] or

[26] , wherein generating a signal for detection includes heating the microfluidic device to cause the reaction, and the temperature at which the microfluidic device is heated is 60°C or higher.

[28] The sample analysis method according to any one of

[25] to

[27] , wherein the signal is detected by imaging the microfluidic device.

[29] The sample analysis method according to any one of

[25] to

[28] , wherein the signal is fluorescence.

[30] The sample analysis method according to any one of

[26] to

[29] , wherein the reaction is an isothermal reaction. Effect of the Invention

[0012] According to the microfluidic device of the present invention, it is possible to form minute droplets and suppress the generation of air bubbles when the minute droplets are heated. Furthermore, according to the sample analysis method of the present invention, when microdroplets are formed, the microdroplets are heated, and the sample is optically detected, it is possible to suppress the generation of air bubbles when the microdroplets are heated, thereby improving the efficiency of sample detection. [Brief description of the drawings]

[0013] [Figure 1] FIG. 1 is a perspective view showing a microfluidic device according to an embodiment of the present invention. [Diagram 2] FIG. 2 is a cross-sectional view taken along line bb in FIG. [Diagram 3] FIG. 2 is a cross-sectional view taken along line bb in FIG. [Figure 4] FIG. 2 is a top view of a microchannel device according to an embodiment of the present invention, in which a region in which a droplet holder is formed exists only in a part of a substrate. [Diagram 5] FIG. 1 is a cross-sectional view showing a microfluidic device according to one embodiment of the present invention. [Figure 6] FIG. 2 is a diagram showing a state in which a microfluidic device according to one embodiment of the present invention is in use. [Figure 7] FIG. 2 is a diagram showing a state in which a microfluidic device according to one embodiment of the present invention is in use. [Figure 8] FIG. 13 is a diagram showing a state in which a microfluidic device according to a comparative example is in use. [Figure 9A] FIG. 2 shows a fluorescent image observed using a microfluidic device according to one embodiment of the present invention. [Figure 9B]FIG. 13 is a diagram showing a fluorescent image observed using a microfluidic device according to a comparative example. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0014] An embodiment of the present invention will be described with reference to Figures 1 to 5. In this specification, the dimensional ratios in each drawing are exaggerated for the purpose of explanation and do not necessarily correspond to the actual dimensional ratios.

[0015] FIG. 1 is a perspective view showing a microfluidic device 1 according to this embodiment. FIGS. 2 and 3 are cross-sectional views taken along the line bb in FIG. 1. As shown in FIGS. 2 and 3, the microfluidic device 1 includes a flow channel 35 and a droplet holder 11. The flow channel 35 may be formed by arranging a cover member 20 and a substrate 10 facing each other at a fixed distance. In this case, the flow channel 35 is a space sandwiched between the cover member 20 and the substrate 10. A peripheral member 34 is positioned between the substrate 10 and the cover member 20. The region sandwiched between the substrate 10 and the cover member 20 and surrounded by the peripheral member 34 is the flow channel 35. The peripheral member 34 may be formed integrally with the cover member 20.

[0016] When the substrate 10 on which the flow path 35 is formed is planar, that is, a flat plate, the droplet holder 11 is preferably a hole present in the substrate 10, that is, a well. 3, the droplet holder 11 is preferably a microwell 33 having a plurality of holes (wells) on the substrate 10. In other words, the substrate 10 preferably has a plurality of microwells 33. Hereinafter, the microfluidic device 1 according to this embodiment will be described taking as an example a microfluidic device 1 in which the droplet holder 11 is a microwell 33 having a plurality of holes (wells) on a substrate 10.

[0017] The microwell array 30 may have a bottom layer 31, a wall layer 32 (which may be referred to as partitions 32), and a plurality of microwells 33. The bottom layer 31 is provided on the substrate 10. The wall layer 32 is formed on the bottom layer 31. The plurality of microwells 33 are composed of the bottom layer 31 and a plurality of through holes 32a formed in the thickness direction of the wall layer 32. The plurality of microwells 33 are formed in an array in the wall layer 32. In the internal space S between the substrate 10 and the cover member 20, there is a gap between the microwell array 30 and the cover member 20, in other words, between the upper surface of the wall layer 32 and the cover member 20. This gap functions as a flow path 35 that communicates with the plurality of microwells 33, as well as the first hole 21 and the second hole 22.

[0018] The substrate 10 may be capable of transmitting electromagnetic waves. Here, examples of electromagnetic waves include X-rays, ultraviolet rays, visible light, and infrared rays. By allowing the substrate 10 to transmit electromagnetic waves, it is possible to observe, from the substrate 10 side, fluorescence or phosphorescence or the like that occurs due to a reaction between a sample and a reagent sealed in the microfluidic device 1. Substrate 10 may be capable of transmitting only electromagnetic waves in a predetermined wavelength range. For example, when the presence of a sample in a microwell is determined by detecting fluorescence having a peak in the visible light range of 350 to 700 nm, a substrate capable of transmitting at least visible light in the above wavelength range may be used as substrate 10.

[0019] Examples of materials for forming the substrate 10 include glass and resin. Examples of materials for the resin substrate include ABS resin, polycarbonate resin, COC (cycloolefin copolymer), COP (cycloolefin polymer), acrylic resin, polyvinyl chloride, polystyrene resin, polyethylene resin, polypropylene resin, polyvinyl acetate, PET (polyethylene terephthalate), and PEN (polyethylene naphthalate). These resins may contain various additives. Examples of additives include antioxidants, additives that impart water repellency, and additives that impart hydrophilicity. The resin substrate may contain only one of the above resins, or may be a mixture of multiple resins.

[0020] Since the sample analysis method described below may utilize fluorescence or phosphorescence, it is preferable to use a material that has substantially no autofluorescence for the substrate 10. Here, "substantially no autofluorescence" means that the substrate has no autofluorescence at the wavelength used to detect the experimental results, or that even if it has autofluorescence, it is so weak that it does not affect the detection of the experimental results. For example, if the autofluorescence is 1 / 2 or less, preferably 1 / 10 or less, of the fluorescence to be detected, it can be said to be so weak that it does not affect the detection of the experimental results.

[0021] The thickness of the substrate 10 can be determined as appropriate, but is preferably 5 millimeters (mm) or less, more preferably 2 mm or less, and even more preferably 1.6 mm or less, for example, in order to facilitate transmission of fluorescence or phosphorescence emitted in sample analysis. The lower limit of the thickness of the substrate 10 can be determined as appropriate, but it is preferable that the thickness is such that no distortion occurs even if the pressure inside the microfluidic device 1 increases. For example, it is preferably 0.1 mm or more, more preferably 0.2 mm or more, and even more preferably 0.4 mm or more. The upper and lower limits of the thickness of the substrate 10 can be arbitrarily combined. For example, the thickness of the substrate 10 is preferably 0.1 mm or more and 5 mm or less, more preferably 0.2 mm or more and 2 mm or less, and even more preferably 0.4 mm or more and 1.6 mm or less.

[0022] The bottom layer 31 constitutes the bottom surface of the microwell 33. Therefore, if it is desired to impart hydrophilicity to the bottom surface, the bottom layer 31 may be formed of a hydrophilic material. The bottom layer 31 is preferably formed so that the bottom layer 31 is capable of transmitting electromagnetic waves and does not interfere with the observation of the sample in the microwell 33 from the substrate 10 side. If it is desired to impart hydrophobicity to the bottom surface, the bottom layer 31 may be formed of a hydrophobic material. The bottom layer 31 is preferably formed so that it does not interfere with the observation of the sample in the microwell 33 from the substrate 10 side. It is also preferable to use a material that has substantially no autofluorescence for the bottom layer 31. Here, the substrate 10 and the bottom layer 31 integrated together may be simply referred to as a substrate.

[0023] In addition, if there is no problem with the characteristics of the bottom surface of the microwell 33 being the same as the characteristics of the substrate 10, the wall layer 32 may be formed directly on the substrate 10 without providing the bottom layer 31. In that case, therefore, the microwell 33 is formed by the surface of the substrate 10 and the through-hole 32a of the wall layer 32.

[0024] The wall layer 32 has a plurality of through-holes 32a arranged in an array when viewed in the thickness direction. The inner surface of each of the through-holes 32a constitutes the inner wall surface of each of the microwells 33.

[0025] The material for forming the wall layer 32 may be the same resin as that for forming the substrate 10, but it may also be a material in which a colored component that absorbs electromagnetic waves of a predetermined wavelength is mixed into the resin. As the resin material, either a hydrophilic resin in which the molecules of the resin components have hydrophilic groups, or a hydrophobic resin in which the molecules of the resin components have hydrophobic groups can be used, taking into consideration the characteristics desired for the microwells 33.

[0026] Examples of hydrophilic groups include hydroxyl groups, carboxyl groups, sulfone groups, sulfonyl groups, amino groups, amide groups, ether groups, and ester groups. Examples of hydrophilic resins include siloxane polymers, epoxy resins, polyethylene resins, polyester resins, polyurethane resins, polyacrylamide resins, polyvinylpyrrolidone resins, acrylic resins such as polyacrylic acid copolymers, polyvinyl alcohol resins such as cationized polyvinyl alcohol, silanolized polyvinyl alcohol, and sulfonated polyvinyl alcohol, polyvinyl acetal resins, polyvinyl butyral resins, polyethylene polyamide resins, polyamide polyamine resins, cellulose derivatives such as hydroxymethyl cellulose and methyl cellulose, polyalkylene oxide derivatives such as polyethylene oxide and polyethylene oxide-polypropylene oxide copolymers, maleic anhydride copolymers, ethylene-vinyl acetate copolymers, styrene-butadiene copolymers, and combinations of the above resins. Examples of hydrophobic resins include novolac resins, acrylic resins, methacrylic resins, styrene resins, vinyl chloride resins, vinylidene chloride resins, polyolefin resins, polyamide resins, polyimide resins, polyacetal resins, polycarbonate resins, polyphenylene sulfide resins, polysulfone resins, fluororesins, silicone resins, urea resins, melamine resins, guanamine resins, phenolic resins, cellulose resins, and combinations of the above resins. Materials having a contact angle of 70 degrees or more measured according to the sessile drop method specified in JIS R3257-1999 can be appropriately selected and used. That is, hydrophobicity in this specification means that the contact angle measured according to the sessile drop method specified in JIS R3257-1999 is 70 degrees or more. Note that the contact angle can also be measured according to a method conforming to ASTM D5725-1997 instead of the sessile drop method specified in JIS R3257-1999.

[0027] Both the hydrophilic resin and the hydrophobic resin may be a thermoplastic resin or a thermosetting resin, and may further be a resin that is cured by active energy rays such as electron beams or UV light, or may be an elastomer. When photoresist is used as the resin material, a large number of minute through holes 32a can be formed in the wall layer 32 with high precision by photolithography. When photolithography is used, known means can be appropriately selected for the selection of the type of photoresist to be used, the application, exposure (exposure) and removal of unnecessary photoresist. If no resist is used, the wall layer 32 can be formed by, for example, injection molding.

[0028] Examples of colored components include organic or inorganic pigments. Specifically, black pigments include carbon black, acetylene black, and iron black. Yellow pigments include chrome yellow, zinc yellow, ocher, Hansa yellow, permanent yellow, and benzine yellow. Orange pigments include orange lake, molybdenum orange, and benzine orange. Red pigments include red iron oxide, cadmium red, antimony vermilion, permanent red, lithol red, lake red, brilliant scarlet, and thioindigo red. Blue pigments include ultramarine blue, cobalt blue, phthalocyanine blue, ferrocyanine blue, and indigo. Green pigments include chrome green, viridian naphthol green, and phthalocyanine green.

[0029] Furthermore, when the wall layer 32 is formed by injection molding or the like, not only pigments dispersed in the resin but also various dyes dissolved in the resin can be used as colored components. The dyes can be exemplified by various dyeing methods. Specific examples include direct dyes, basic dyes, cationic dyes, acid dyes, mordant dyes, acid mordant dyes, sulfur dyes, vat dyes, naphthol dyes, disperse dyes, and reactive dyes. In particular, disperse dyes are often selected when dyeing resin.

[0030] The lid member 20 (which may simply be referred to as the lid 20) is a member formed in a plate or sheet shape. The lid member 20 faces the substrate 10 while being spaced apart from it. In other words, the lid member 20 covers the multiple microwells 33. The flow path 35 is a region surrounded by the lid member 20, the microwell array 30, and the peripheral member 34. The flow path 35 is connected to the openings of the multiple microwells 33, and is located above the multiple microwells 33.

[0031] The cover member 20 has a first hole 21 and a second hole 22 penetrating in the thickness direction. In a plan view of the cover member 20, the first hole 21 and the second hole 22 are positioned so as to sandwich one or more of the liquid retaining portions. In the completed microfluidic device 1, the first hole 21 and the second hole 22 communicate with the internal space S including the microwell array 30 and the flow channel 35. The first hole 21 and the second hole 22 function as an inlet for supplying a fluid to the internal space S and an outlet for discharging the fluid, respectively. The material and thickness of the lid member 20 may be the same as those of the substrate 10 . When the lid member 20 has electromagnetic wave transparency, the electromagnetic wave transparency can be appropriately set. For example, when the electromagnetic wave irradiation step described later is not performed from the lid member 20 side, the lid member 20 does not need to be able to transmit electromagnetic waves.

[0032] 2, the height h of the flow channel 35 is the height from the top surface of the substrate 10 on the flow channel 35 side (the surface of the substrate 10 on the flow channel 35 side where no holes are formed) to the surface of the cover member 20 on the flow channel 35 side. In the case where the microfluidic device 1 includes the wall layer 32, the height h is the height from the surface 32b of the wall layer 32 on the flow channel 35 side to the surface 20a of the cover member 20 on the flow channel side, as shown in FIG.

[0033] The height h of the flow channel 35 is more than 0 μm and less than 50 μm, preferably more than 0 μm and less than 30 μm, preferably 2 μm to 30 μm, preferably 3 μm to 25 μm, more preferably 5 μm to 20 μm, and particularly preferably 8 μm to 18 μm. By having the height of the flow channel be more than 0 μm and less than 50 μm, the generation of bubbles is suppressed when the droplets formed in the droplet holder 11 (microwell 33) are heated. Therefore, the detection of the fluorescence, etc. is not hindered by the bubbles, and the sample can be detected by the fluorescence, etc.

[0034] From the viewpoint of suppressing the generation of bubbles, the height h of the flow channel is preferably smaller than 50 μm, but if the height h of the flow channel is smaller than 2 μm, it may not be easy to fill the flow channel with the sample. If the height h of the flow channel is 2 μm or more, the pressure when filling the flow channel with the aqueous liquid containing the sample does not increase too much, and the aqueous liquid can be easily filled. If the height h of the flow channel is 50 μm or more, bubbles are likely to be generated when the droplet formed in the droplet holder 11 (microwell 33) is heated, and the generation of the bubbles makes it difficult to detect the sample by fluorescence or the like. In other words, if the height h of the flow channel is less than 50 μm, bubbles are unlikely to be generated even if the droplet formed in the droplet holder 11 (microwell 33) is heated, and the sample can be accurately detected by fluorescence or the like. As a result, if the height h of the flow channel is less than 50 μm, the yield rate of the microfluidic device is improved. In addition, if the height h of the flow channel is less than 50 μm, the efficiency of detecting the sample is improved, and the success rate of the detection operation is improved.

[0035] The height of the flow channel 35 may be an average value of heights at a plurality of points on the uppermost surface of the substrate 10 on the flow channel 35 side (the surface of the substrate 10 on the flow channel 35 side in the portion where no holes are formed), or may be a height at a representative point. The representative point can be selected from any position on the substrate 10. For example, it may be the center of the substrate 10 on which the flow channel 35 is formed, or a position 10% to 50% from the tip side of a line connecting the tip and center of the substrate 10 on which the flow channel 35 is formed. Considering ease of measurement, it is preferable to select the position at the point where a virtual orthogonal line at the center of a virtual line connecting the center of the first hole 21 and the center of the second hole 22 intersects with the peripheral member 34 when the cover member 20 is viewed from above as the representative point. Furthermore, when the microfluidic device 1 includes the wall layer 32, the height may be an average value of heights at a plurality of points on the surface 32a of the wall layer 32 facing the flow channel 35, or may be a height at a representative point. The representative point can be selected from any position of the wall layer 32. For example, the representative point may be the center of the wall layer 32. The representative point may be a position that is 10% to 50% from the tip of a line connecting the tip of the side of the wall layer 32 facing the flow channel 35 and the center. In consideration of ease of measurement, it is preferable to select the position at the point where a virtual orthogonal line at the center of a virtual line connecting the first hole 21 and the second hole 22 intersects with the peripheral member 34 as the representative point. Here, the term "forefront" refers to the end in a direction (referred to as the longitudinal direction) parallel to an imaginary line connecting the first hole 21 and the second hole 22 of the microfluidic device 1. The term "end" refers to the portion that comes into contact with a peripheral member 34, which will be described later.

[0036] Furthermore, the surface of the cover member 20 on the flow path side that forms the flow path 35 is preferably smooth. By making the surface of the cover member 20 on the flow path 35 side smooth, it is possible to further suppress the generation of bubbles when the droplets in the droplet holder 11 (microwell 33) are heated. In this specification, "smooth" means that the unevenness when observed with an optical microscope is small, that is, the microscopic unevenness is small. In this specification, "smooth" does not mean that the cover member 20 is not curved on the inside of the peripheral member 34. In this embodiment, the cover member 20 may be curved on the inside of the peripheral member 34. For example, the cover member 20 may be curved so as to protrude toward the substrate 10 near the center of the main surface of the cover member 20. In other words, the flow path 35 in the part that contacts the peripheral member 34 may be higher than the flow path 35 near the center of the main surface of the cover member 20. Here, the center of the main surface of the cover member 20 is the geometric center of the main surface of the cover member 20.

[0037] In this specification, a microwell means a well with a volume of 10 nanoliters (nL) or less. By making the volume of the droplet holder 11 the volume of a microwell, reactions such as digital PCR and digital ICA reactions can be suitably carried out in a small space. For example, gene mutation detection can be performed by the above-mentioned method. The volume of the droplet holder 11 (microwell 33) is not particularly limited, but is preferably 10 femtoliters (fL) to 100 picoliters (pL), more preferably 10 fL to 5 pL, and most preferably 10 fL to 2 pL. Setting the volume within such a range is suitable for storing one to several biomolecules or carriers in one droplet holder 11 (microwell 33) during sample analysis, which will be described later.

[0038] The shape of the microwell 33 is not particularly limited as long as the volume is within the above-mentioned range, and may be, for example, a cylinder, a polyhedron composed of multiple faces (e.g., a rectangular parallelepiped, a hexagonal prism, an octagonal prism, etc.), an inverted cone, an inverted pyramid (an inverted triangular pyramid, an inverted square pyramid, an inverted pentagonal pyramid, an inverted hexagonal pyramid, and an inverted polygonal pyramid with seven or more sides), etc. Furthermore, the shape of the multiple macrowells 33 may be a shape that combines two or more of the above shapes. For example, some of the multiple macrowells 33 may be cylindrical, and the rest may be inverted cone-shaped. When the microwells 33 are inverted cone-shaped or inverted pyramid-shaped, the bottom of the cone or pyramid becomes an opening that connects the flow path 35 to the microwells 33. In this case, the bottom of the microwells 33 may be flattened by using a shape in which a part is cut off from the top of the inverted cone or inverted pyramid. As another example, the bottom of the microwells 33 may be a curved shape that protrudes toward the opening, or the bottom of the macrowells 33 may be a curved shape that is recessed.

[0039] The unit area of ​​the region of the substrate 10 where the droplet holder is formed (usually 1 mm 2 The ratio of the total area of ​​the openings of the droplet holder 11 (microwell 33) per unit area of ​​the substrate 10 is preferably 23% or more and 90% or less, more preferably 25% or more and 90% or less, more preferably 30% or more and 90% or less, more preferably 35% or more and 80% or less, more preferably 39% or more and 76% or less, and more preferably 39% or more and 64% or less. When the ratio of the total area of ​​the openings of the droplet holder 11 (microwell 33) per unit area of ​​the substrate 10 in which the droplet holder is formed is within the above-mentioned preferred range, the generation of bubbles in the flow path can be effectively suppressed. This is considered to be because, when the aqueous liquid in the droplet holder 11 (microwell 33) is heated, the pressure applied to the sealing liquid in the flow path 35 can be suppressed to some extent because the total area of ​​the openings is not too large.

[0040] Hereinafter, the ratio of the total area of ​​the openings of the droplet holders 11 (microwells 33) per unit area of ​​the region of the substrate 10 in which the droplet holders are formed is also referred to as the "opening area ratio."

[0041] When the region in which the droplet holder 11 (microwell 33) is formed exists over the entire surface of the substrate 10, the total area of ​​the openings of the droplet holder 11 (microwell 33) of the substrate 10 may be approximated to be the same as the area of ​​the region of the substrate 10 partitioned by the peripheral member. The region in which the droplet holder 11 (microwell 33) is formed may exist only in a part of the substrate 10, as shown in FIG. 4. Here, the region in which the droplet holder 11 (microwell 33) is formed refers to a region in which the droplet holders 11 (microwells 33) are spaced apart at a constant interval when the substrate 10 is viewed from the vertical direction, as shown in FIG. 4. In this case, the total area of ​​the openings of the droplet holder 11 (microwell 33) of the substrate 10 may be approximated to the area of ​​a region surrounded by an imaginary line passing through the centers of the openings of the droplet holders 11 (microwells 33) located at the outermost part of the region in which the droplet holder 11 (microwell 33) is formed. The term "constant intervals" does not necessarily mean that the intervals are strictly constant, and naturally, manufacturing errors are allowed.

[0042] The greater the area of ​​the region in which droplet holder 11 is formed relative to the area of ​​the region partitioned by the peripheral member of substrate 10, the more easily the aqueous liquid evaporates and the more easily air bubbles are generated. However, when height h of flow path 35 is set to less than 50 μm as in this embodiment, the generation of air bubbles in flow path 35 can be effectively suppressed.

[0043] When the wall layer 32 is present, the thickness of the wall layer 32 defines the depth of the droplet holder 11 (microwell 33). When the microwell is cylindrical, for the purpose of enclosing an aqueous liquid (sample) containing biomolecules, the thickness of the wall layer 32 can be, for example, in the range of 10 nm to 100 μm, preferably 100 nm to 50 μm, more preferably 1 μm to 30 μm, even more preferably 2 μm to 15 μm, and even more preferably 3 μm to 10 μm. The dimensions of each part of the microwell 33 can be appropriately determined so that one or several biomolecules can be accommodated in one microwell, taking into consideration the amount of aqueous liquid to be accommodated and the size of the carrier such as beads to which the biomolecules are attached.

[0044] The ratio of the depth of the droplet holder 11 (microwell 33) to the height h of the flow channel 35 is preferably 3% to 150%, more preferably 10% to 100%, even more preferably 12% to 75%, even more preferably 15% to 75%, even more preferably 33% to 75%, and even more preferably 33% to 50%. By being in this range, it is possible to both suppress the generation of bubbles and facilitate the introduction of the detection target into the droplet holder 11 (microwell 33).

[0045] The number and density of microwells 33 provided in microwell array 30 can be set as appropriate, but it is preferable to set the number and density of microwells 33 so that the total volume of microwells 33 is, for example, from 0.2 μL to 2.0 μL, and preferably from 0.5 μL to 1.5 μL. Furthermore, the total volume of the microwells 33 is preferably 5% to 40%, more preferably 8% to 30%, and particularly preferably 10% to 20%, of the volume of the flow channel 35. When the ratio of the total volume of the microwells 33 to the volume of the flow channel 35 is within a preferred range, the generation of bubbles when the droplets in the microwells 33 are heated can be further suppressed.

[0046] 1cm 2 The number of microwells 33 per cm is, for example, from 10,000 to 10 million, preferably from 100,000 to 5 million, and more preferably from 100,000 to 1 million. 2The number of microwells 33 per well is sometimes referred to as the density of the microwells. When the density of the microwells is within this range, the operation of sealing the aqueous liquid as the sample in a predetermined number of wells is easy. Furthermore, when the density of the microwells is within this range, the wells are also easy to observe in order to analyze the experimental results. For example, when detecting a mutation in cell-free DNA, if the ratio of the mutant DNA to be detected to the wild-type DNA is about 0.01%, it is preferable to use, for example, about 1 to 2 million microwells. 1 shows an example of a one-dimensional array in which a plurality of microwells 33 are arranged in a line. However, when a large number of microwells are provided as described above, a two-dimensional array in which a plurality of microwells are arranged two-dimensionally may be used.

[0047] A peripheral member 34 having a frame shape in a plan view is disposed around the microwell array. The dimension of peripheral member 34 in the thickness direction of microfluidic device 1 is larger than that of wall layer 32. Peripheral member 34 supports cover member 20, thereby ensuring a gap between cover member 20 and the microwell array, and maintaining flow path 35. In other words, flow path 35 is a region sandwiched between microwell array 30 and cover member 20, and surrounded by peripheral member 34. There are no particular limitations on the material of the peripheral member 34, but examples include a double-sided adhesive tape in which an acrylic adhesive is laminated on both sides of a core film made of silicone rubber or acrylic foam. It should be noted that peripheral member 34 may be integrally formed with cover member 20. In that case, peripheral member 34 becomes a step portion of cover member 20, and the step portion secures a gap between cover member 20 and the microwell array, thereby maintaining flow path 35.

[0048] The microfluidic device 1 configured as above can be manufactured, for example, by the following procedure. First, the substrate 10 is prepared, and a wall resin layer that will become the wall layer 32 is formed on the surface of the substrate 10. When the bottom layer 31 is provided, the bottom layer 31 is formed before the formation of the wall resin layer. Even when the bottom layer 31 is not provided, an anchor layer or the like that enhances adhesion between the substrate 10 and the wall resin layer may be provided on the surface of the substrate 10 as necessary.

[0049] The wall resin layer may be formed of a material obtained by mixing a colored component with a resin material. When the resin material is a resist, the content of the colored component with respect to the total mass of the resin material and the colored component can be, for example, 0.5 mass% or more and 60 mass% or less. The content is preferably 5 mass% or more and 55 mass% or less, and more preferably 20 mass% or more and 50 mass% or less. The content of the colored component with respect to the total mass of the resin material and the colored component can be appropriately set so that a desired pattern can be constructed in consideration of the ratio of the photosensitive component contained in the resist. In addition, when the colored component is a pigment, the particle diameter of the pigment is set and prepared so as to satisfy the above-mentioned predetermined conditions for the microwell to be formed. A dispersant may be appropriately added to the resin material together with the pigment. When the wall resin layer is formed from a material in which a colored component is mixed into a resin material, the wall resin layer has a color based on the colored component contained in the wall resin layer.

[0050] Next, the through holes 32a are formed in the formed wall resin layer. As described above, the through holes 32a can be formed easily and accurately by using photolithography. When the wall resin layer is formed by injection molding or the like, the formation of the wall resin layer and the formation of the through holes can be performed in the same process. Alternatively, the through holes 32a can be formed by etching using a pattern mask or the like. When the through-holes 32a are formed, the wall resin layer becomes the wall layer 32, and the microwell array 30 is completed.

[0051] Thereafter, a peripheral member 34 is placed around the microwell array 30, and then the cover member 20 is placed on the peripheral member 34. The microfluidic device 1 is completed when the substrate 10, the peripheral member 34, and the cover member 20 are joined together. The flow path 35 is formed between the cover member 20 and the substrate 10 by the peripheral member 34. The joining method is not particularly limited, and examples thereof include joining with an adhesive, joining with double-sided tape, joining by laser welding, and joining by thermal welding. When the sample analysis method using the microfluidic device 1 includes a heating reaction, joining with an adhesive, joining with double-sided tape, and joining by laser welding are preferable because they can sufficiently withstand the pressure increase in the internal space S caused by heating.

[0052] In addition, the microfluidic device 1 may be formed such that the substrate 10 and the wall layer 32 are integrally molded, and the peripheral member 34 and the cover member 20 are integrally molded. FIG. 5 shows a microfluidic device 2 in which the substrate 10 and the wall layer 32 are integrally molded, and the peripheral member 34 and the cover member 20 are integrally molded. The microfluidic device 2 can be manufactured by disposing the substrate 10 integrally molded with the wall layer 32 on the cover member 20 integrally molded with the peripheral member 34, and bonding the step portion formed by integrally molding the peripheral member 34 and the cover member 20 to the substrate 10 integrally molded with the wall layer 32. The flow path 35 is formed between the cover member 20 and the substrate 10 by the step portion formed in the cover member 20. The configuration of the microfluidic device 2 is the same as that of the microfluidic device 1 described above, except that the substrate 10 and the wall layer 32 are integrally formed, and the peripheral member 34 and the cover member 20 are integrally formed.

[0053] In another embodiment, the microfluidic device may have the substrate 10 and the wall layer 32 as separate elements, and the peripheral member 34 and the cover member 20 are integrally formed. In this case, the configuration of the microfluidic device is the same as that of the microfluidic device 1 described above, except that the peripheral member 34 and the cover member 20 are integrally formed.

[0054] Next, a sample analysis method according to this embodiment using the microfluidic device 1 according to this embodiment will be described with reference to FIGS. The sample analysis method of the present embodiment is a method for analyzing a sample using the microfluidic device 1 according to the present embodiment, Introducing an aqueous liquid containing a sample into the flow channel 35 and causing the droplet holder 11 to hold the aqueous liquid; introducing a sealing liquid into the flow channel 35 to replace the aqueous liquid present in the flow channel 35, and sealing the aqueous liquid in the droplet holder 11; causing a reaction in the droplet holder 11 to generate a signal for detection; and detecting the signal.

[0055] Here, the aqueous liquid may contain water, a buffer solution, a detection reaction reagent, and the like in addition to the sample. The aqueous liquid may also contain an enzyme. For example, when the sample is a nucleic acid, the PCR method, the ICA method, the LAMP method (registered trademark, Loop-Mediated Isothermal Amplification), the TaqMan method (registered trademark), or a fluorescent probe method may be used. For example, when the sample is a protein, the ELISA method (registered trademark) may be used. Furthermore, the aqueous liquid may contain additives such as a surfactant.

[0056] Examples of the buffer solution include Tris-HCl buffer solution, acetate buffer solution, and phosphate buffer solution. Examples of the enzyme include DNA polymerase, RNA polymerase, reverse transcriptase, and flap endonuclease. Examples of surfactants include Tween 20 (also known as polyoxyethylene sorbitan monolaurate), Triton-X100 (also known as polyethylene glycol mono-4-octylphenyl ether (n=about 10)), glycerol, octylphenol ethoxylate, and alkyl glycoside.

[0057] The microfluidic device of this embodiment can suitably hold the aqueous liquid in the well even when the temperature of the enclosed aqueous liquid is changed, for example, in detecting gene mutations, etc. The range of the temperature to be changed, i.e., the range from the lower limit to the upper limit of the temperature change, is, for example, 0° C. to 100° C., preferably 20° C. to 100° C., more preferably 20° C. to 90° C., more preferably 20° C. to 80° C., and even more preferably 20° C. to 70° C. When the aqueous solution enclosed in the well is within this range, reactions carried out in a microspace, such as PCR reactions and ICA reactions, can be carried out suitably. In the microfluidic device of this embodiment, the height h of the flow channel is less than 50 μm, so that even when the droplet holder 11 (microwell 33) is heated within the above temperature range, the generation of air bubbles can be suppressed.

[0058] Examples of samples to be analyzed using the microfluidic device 1 according to this embodiment include samples collected from a living body, such as blood. Furthermore, the detection target detected by sample analysis may be a PCR product using DNA contained in the sample as a template, or an artificially synthesized compound (e.g., an artificially synthesized nucleic acid that mimics the DNA of the sample). For example, when DNA, which is a biological molecule, is the detection target, the well may have a shape and size that allows one DNA molecule to be placed therein.

[0059] The sample may include biomolecules such as DNA, RNA, miRNA, mRNA, proteins, or lipids. The lipids may include lipid bilayer structures. The biomolecules may include cells collected from humans for non-therapeutic purposes, cells collected from animals, microorganisms, or bacteria. When the detection target is a biomolecule, the sample analysis method in one aspect of the present invention can be said to be a biomolecule detection method, and the microfluidic device in one aspect of the present invention used in the biomolecule detection method can be said to be a biomolecule detection device.

[0060] The details of the sample analysis method will be described below. As a preparation step, an aqueous liquid containing a sample to be sealed in a microwell is prepared. The aqueous liquid containing the sample is a liquid containing the target to be detected and is mainly composed of water. For example, a PCR reaction solution containing a biological sample as a template and SYBR Green as a detection reagent, or an ICA reaction solution containing an allele probe, an ICA oligo, FEN-1, and a fluorescent substrate, etc. may be mentioned. In the preparation, a surfactant may be added to make the sample easier to enter the microwell. In addition, beads that specifically recognize the target to be detected may be added to capture the target to be detected. The target to be detected may be suspended in the aqueous liquid without being directly or indirectly bound to a carrier such as beads.

[0061] Next, the prepared aqueous liquid 100 containing the sample is introduced into the flow channel 35 from the first hole 21 using a syringe or the like, and the aqueous liquid containing the sample is held in the droplet holder 11 (also referred to as a sample supplying step). The supplied aqueous liquid 100 containing the sample is filled into each microwell 33 and the flow channel 35, as shown in FIG. 6. Gas in the flow channel 35 is removed in advance by a degassing operation prior to the sample supplying step. This degassing operation may be performed by filling the flow channel 35 with a buffer. Examples of the buffer include water, water containing a buffer solution, water containing a surfactant, and water containing a buffer solution and a surfactant.

[0062] Next, an encapsulation step is performed in which the aqueous liquid 100 containing the sample is encapsulated in the droplet holder 11 (microwell 33). Prior to the encapsulation step, the detection target in the sample contained in the aqueous liquid may be labeled with a fluorescent label or the like. The fluorescent labeling process may be performed prior to the sample supply step, for example, during sample preparation, or may be performed by introducing a fluorescent label into the flow channel 35 after the sample supply step. In the sealing step, a syringe or the like is used to supply sealing liquid 110 from first hole 21 to flow channel 35. The supplied sealing liquid 110 flows through flow channel 35 and, as shown in FIG. 7, pushes aqueous liquid 100 containing the sample present in flow channel 35 toward second hole 22. Then, sealing liquid 110 replaces aqueous medium 100 filling flow channel 35, and flow channel 35 is filled with sealing liquid 110. As a result, aqueous liquid 100 containing the sample is disposed only in each microwell 33 in a mutually independent state, completing the sealing of the sample.

[0063] In this specification, sealing liquid 110 refers to a liquid used to isolate the aqueous liquids introduced into each microwell 33 of microwell array 30 so that they do not mix with each other, and examples of such liquid include oils. Examples of oils that can be used include Sigma's product name "FC40," 3M's product name "HFE-7500," and mineral oils used in PCR reactions and the like. The contact angle of the sealing liquid 110 with respect to the material of the wall layer 32 is preferably 5 degrees or more and 30 degrees or less. When the contact angle of the sealing liquid 110 is in this range, the sample can be suitably sealed in each microwell 33. The contact angle of the sealing liquid 110 may be measured, for example, according to the sessile drop method defined in JIS R3257-1999, using the sealing liquid 110 instead of water. Note that the contact angle may be measured by a method in accordance with ASTM D5725-1997 instead of the sessile drop method defined in JIS R3257-1999.

[0064] Next, a reaction step is carried out in which a reaction occurs in the droplet holder 11 (microwell 33) of the microfluidic device 1 and a signal for detection is generated. Examples of signals for detection include fluorescence, chemiluminescence, color development, potential change, and pH change, with fluorescence being preferred. Prior to the reaction step, the microfluidic device 1 may be subjected to a thermal cycler to carry out an enzyme reaction such as a PCR reaction or an ICA reaction, if necessary. The reaction may be, for example, a biochemical reaction, more specifically, an enzyme reaction. The reaction may be caused by heating the microfluidic device 1. The temperature at which the reaction is heated is appropriately determined depending on the reaction, and is, for example, 60°C or higher and 100°C or lower. The temperature at which the reaction is heated is preferably 60°C or higher and 90°C or lower, more preferably 60°C or higher and 80°C or lower, and even more preferably 60°C or higher and 70°C or lower. The temperature at which the reaction is heated is not the actual temperature of the reagent liquid in the droplet holder 11 (microwell 33), but the heating temperature of the microfluidic device set by a thermal cycler or an incubator. The temperature at which the reaction is heated is, for example, 60°C or higher and 100°C or lower, and means that the maximum temperature of the temperature reaches 60°C or higher and 100°C or lower, and does not necessarily have to be always 60°C or higher and 100°C or lower. That is, the temperature of the microfluidic device 1 may change within the range of the temperature to be changed as described above. One example of the reaction is a signal amplification reaction. The signal amplification reaction is an isothermal reaction in which a reagent solution containing an enzyme for signal amplification is contained in the droplet holding portion 11 (microwell 33) and the microfluidic device 1 is maintained under constant temperature conditions at which the desired enzyme activity is obtained, for example, at least 60°C and no more than 100°C, for a predetermined period of time, for example, at least 10 minutes, and preferably about 15 minutes.

[0065] Next, a signal generated from the droplet holder 11 (microwell 33) by the above reaction is detected (also referred to as a detection step). For example, when the signal is fluorescence, the microfluidic device 1 is set on a fluorescence microscope and is irradiated with excitation light (electromagnetic waves). The wavelength of the excitation light is appropriately set depending on the fluorescent label used. The electromagnetic waves may be applied from the substrate 10 side of the microfluidic device 1, or from the cover member 20 side, i.e., from above the microwells 33, or from any other direction. The fluorescence or phosphorescence generated as a result of the application of the electromagnetic waves may be detected from the substrate side of the microwell array, from the well side, or from any other direction, but when detecting the fluorescence or phosphorescence using a fluorescence microscope, for example, it is convenient to detect it from the substrate 10 side of the microfluidic device 1.

[0066] Next, it is measured how many of the microwells 33 emitting fluorescence or phosphorescence are present among the multiple microwells 33 constituting the microwell array 30. The measurement may be performed by taking a fluorescent image of the microwell array 30 and using the fluorescent image. For example, a PCR reaction is performed in the microwell array 30, and the fluorescence of SYBR Green is detected in the microwells 33 where PCR amplification is observed, thereby making it possible to calculate the ratio of the microwells 33 where amplification is observed to the total number of microwells 33. When the detection target is, for example, a single nucleotide polymorphism (SNP), the expression frequency of the SNP can be analyzed by counting the number of microwells 33 that emit fluorescence.

[0067] Another aspect of the present invention includes the following embodiments.

[31] A microfluidic device comprising: a substrate; a cover member located on the substrate; a peripheral member connecting the substrate and the cover member; a flow path located between the substrate and the cover member and partitioned by the peripheral member; and one or more droplet holders located on the substrate and connected to the flow path, wherein the height of the flow path is greater than 0 μm and less than or equal to 30 μm.

[32] The microfluidic device according to

[31] , wherein the droplet holder is a hole provided on the surface of the substrate.

[33] The microfluidic device described in

[31] , having at least one first hole for introducing liquid into the flow path and at least one second hole for discharging liquid from the flow path, the first hole and the second hole being positioned so as to sandwich one or more of the liquid retaining portions.

[34] The microfluidic device according to any one of

[31] to

[33] , wherein the bottom of the droplet holder is on the substrate side, the droplet holder has an opening on the lid member side, and the flow channel is located above the opening.

[35] The microfluidic device according to any one of

[31] to

[34] , wherein the volume of each of the droplet holders is from 10 fL to 100 pL.

[36] The microfluidic device according to any one of

[31] to

[35] , wherein the total volume of the droplet holder is 0.2 μL or more and 2.0 μL or less.

[37] The microfluidic device according to any one of

[31] to

[36] , wherein a ratio of a total volume of the droplet holder to a volume of the flow channel is 5% or more and 40% or less.

[38] The microfluidic device according to any one of

[31] to

[37] , wherein the ratio of the depth of the droplet holder to the height of the flow channel is 3% or more and 150% or less.

[39] A microfluidic device described in any one of

[31] to

[38] , wherein the ratio of the total area of ​​the openings of the droplet holder per unit area of ​​the region in which the droplet holder is formed on the substrate is 23% or more and 90% or less.

[40] The microfluidic device according to any one of

[31] to

[39] , wherein the peripheral member is a stepped portion formed integrally with the cover member.

[41] A sample analysis method using the microfluidic device described in any one of

[31] to

[40] , comprising: introducing an aqueous liquid containing a sample into the flow path and causing the aqueous liquid to be held in the droplet holder; introducing a sealing liquid into the flow path to replace the aqueous liquid present in the flow path with the sealing liquid and seal the aqueous liquid in the droplet holder; causing a reaction in the droplet holder to generate a signal for detection; and detecting the signal.

[42] The sample analysis method described in

[41] , wherein the sample is a biological molecule.

[43] The sample analysis method described in

[41] or

[42] , wherein generating a signal for detection includes heating the microfluidic device to cause the reaction, and the temperature at which the microfluidic device is heated is 60°C or higher.

[44] The sample analysis method according to any one of

[41] to

[43] , wherein the signal is detected by imaging the microfluidic device.

[45] The sample analysis method according to any one of

[41] to

[44] , wherein the signal is fluorescence.

[46] The sample analysis method according to any one of

[41] to

[45] , wherein the reaction is an isothermal reaction. EXAMPLES

[0068] The present invention will now be described in more detail with reference to examples, but the present invention is not limited to the following examples.

[0069] Example 1 Two resin components were prepared: a substrate made of COP (ZEONOR1010R, Zeon Corporation) formed by injection molding, and a cover member made of COP (ZEONOR1010R, Zeon Corporation). The total volume of the micropores (i.e., microwells) was adjusted by changing the number of micropores molded in the COP substrate. The cover member and the step were integrally formed, and the height of the step was adjusted to 30 μm, making the height of the flow channel 30 μm. The micropores were 10 μm in diameter and 15 μm in depth and were placed in an area of ​​9000 mm × 30000 mm within the flow channel surface. The opening area ratio was defined as the ratio of the total area of ​​the openings of the micropores per 6.5 mm×9.0 mm region in which the micropores were formed. The substrate used was a 0.6 mm thick substrate with micro holes arranged all over the substrate, molded by injection molding. A contact type measuring device (TALYSURF PGI1240, manufactured by Taylor Hobson) was used to measure the height of the flow channel. The substrate and the step portion of the lid member were bonded by laser welding to prepare a microfluidic device. A fluorescent reagent (Fluorescein, manufactured by Tokyo Chemical Industry Co., Ltd.) having the composition shown in Table 1 was injected into the flow path formed between the substrate and the lid member. Furthermore, the multiple microwells were individually sealed with fluorocarbon oil (FC40, manufactured by Sigma). Note that, although no fluorescent reaction was performed in this example, an enzyme was added to the fluorescent reagent to create a state similar to that in which a fluorescent reaction was performed.

[0070] [Table 1]

[0071] The microfluidic device was heated at 66°C for 30 minutes. After leaving it at room temperature, the presence or absence of air bubbles was confirmed from the top, i.e., from the lid member side, and photographed using a digital camera (CX-4, Ricoh Co., Ltd.). In addition, micropore fluorescent images were observed using a 4x objective lens with a fluorescent microscope (BZ-710, KEYENCE Co., Ltd.). The exposure time was 3000 msec with a bright field of 20 msec and a GFP (Green Fluorescent Protein) fluorescent filter.

[0072] Table 2 shows the bubble generation rate of the microfluidic device. The bubble generation rate was calculated by preparing multiple microfluidic devices of the same design and dividing the number of microfluidic devices with bubbles in one microfluidic device by the number of all microfluidic devices analyzed. The presence or absence of bubbles was determined to be present when bubbles of a size visible to the naked eye were present in the microfluidic device, and determined to be absent when no bubbles were present under the same conditions. The maximum size of bubbles visible under the above conditions was approximately 500 μm or more. Even if small bubbles were present, it was determined that there were no bubbles when the size of the bubbles was smaller than the distance between the ends of the nearest micropores (i.e., microwells) when observing the microfluidic device under a microscope with a 4x objective lens. The reason for this determination is that when bubbles of the above size or smaller are present, they do not substantially impede detection and it is considered that the generation of bubbles is suppressed. As a result, as shown in Table 2, the microfluidic device produced in Example 1 had a low rate of air bubble generation. Fig. 8 shows typical bubble observation results (channel height: 100 µm) in the microfluidic device of the comparative example. In Fig. 8, the part indicated by the arrow indicates a typical bubble generation part. Fig. 8 shows that in addition to the presence of bubbles of several mm, multiple small bubbles of about 500 µm were also observed. In the microfluidic device of Example 1, in which the channel height was set to 30 µm, the generation rate of such bubbles was reduced.

[0073] Next, the results of fluorescence observation are shown in Fig. 9A. In the microfluidic device of Example 1 in which the channel height was 30 µm, droplets did not collapse, and it was possible to observe the micropores (that is, microwells).

[0074] Example 2 A microfluidic device was manufactured in the same manner as in Example 1, except that the height of the flow channel was set to 20 μm, and the bubble generation rate was measured. The results are shown in Table 2. As shown in Table 2, the microfluidic device manufactured in Example 2 had a low bubble generation rate.

[0075] Comparative Example 1 A microfluidic device was manufactured in the same manner as in Example 1, except that the height of the flow channel was set to 100 μm, and the bubble generation rate was measured. The results are shown in Table 2. As shown in Table 2, the microfluidic device manufactured in Comparative Example 1 had a high bubble generation rate. The results of the fluorescence observation are shown in Figure 9B. In the microfluidic device with a channel height of 100 μm, multiple air bubbles were generated, making it difficult to observe the micropores. In Figure 9B, the area indicated by the arrow indicates a typical area where air bubbles were generated.

[0076] Comparative Example 2 A microfluidic device was manufactured in the same manner as in Example 1, except that the well depth was set to 3.5 μm and the channel height was set to 100 μm, and the bubble generation rate was measured. The results are shown in Table 2. As shown in Table 2, the microfluidic device manufactured in Comparative Example 2 had a high bubble generation rate.

[0077] [Table 2]

[0078] Example 3 The substrate used was made of COP (ZEONOR1010R, Zeon Corporation) formed by injection molding. The micropores were 5 μm in diameter and 3.5 μm deep, and were arranged in an area of ​​6.5 mm × 9.0 mm on the flow channel surface. The cover member was made of COP (ZEONOR1010R, Zeon Corporation) formed by injection molding (with liquid supply and waste ports), and the peripheral member was made of 30 μm thick double-sided tape (No. 5603 BN, Nitto Denko Corporation) with a PET (polyethylene terephthalate) base material.

[0079] Other than these, a microfluidic device was manufactured in the same manner as in Example 1, and the bubble generation rate was measured. The results are shown in Table 3. Four microfluidic devices of Example 3 were connected to form a device group, and three such device groups were produced, totaling 12 microfluidic devices. The "ratio of the area where wells are formed" was defined as the ratio of the area where micropores are formed to the area surrounded by the peripheral member, that is, the area where the flow paths are formed.

[0080] Comparative Example 3 A microfluidic device was manufactured in the same manner as in Example 1, except that a 50 μm thick PET (polyethylene terephthalate) double-sided tape (product number: No. 5603 BN, manufactured by Nitto Denko Corporation) was used as the peripheral member, and the bubble generation rate was measured. The results are shown in Table 3.

[0081] Comparative Example 4 A microfluidic device was manufactured in the same manner as in Example 1, except that a 100 μm thick PET (polyethylene terephthalate) double-sided tape (product number: No. 5603 BN, manufactured by Nitto Denko Corporation) was used as the peripheral member, and the bubble generation rate was measured. The results are shown in Table 3.

[0082] [Table 3]

[0083] The height of the flow channel of the microfluidic device of Example 4 corresponds to the thickness of the peripheral member, and can therefore be said to be 30 μm. In the microfluidic device of Example 4, no air bubbles were generated.

[0084] On the other hand, in the microfluidic devices of Comparative Example 3 in which the channel height was 50 μm and Comparative Example 4 in which the channel height was 100 μm, the bubble generation rates were high at 50% and 100%, respectively. From the above, it was confirmed that when the height of the channel of the microfluidic device is 50 μm or more, the rate of bubble generation increases, but when the height of the channel is 30 μm, the rate of bubble generation is reduced. [Industrial Applicability]

[0085] According to the present invention, it is possible to provide a microfluidic device capable of suppressing the generation of bubbles when microdroplets are formed and heated. In addition, it is possible to provide a sample analysis method capable of suppressing the generation of bubbles when microdroplets are formed and heated and optically detecting a sample, thereby improving the detection efficiency of the sample. When using biomolecules as a sample, it is necessary to heat the sample to a high temperature for a certain period of time or more. According to the present invention, it is possible to effectively suppress the generation of bubbles even in such a case. [Explanation of symbols]

[0086] 1, 2 Microfluidic device 10 Substrate 11 Droplet holding part 20 Cover member 30 Microwell Array 32 Wall layer 33 Microwell 35 Flow Path 100 aqueous liquid 110 Sealing liquid

Claims

1. A liquid droplet ejection device having a liquid droplet ejection passage and a plurality of droplet holders connected to the liquid droplet ejection passage, the liquid droplet ejection passage having a height of more than 0 μm and not more than 30 μm, A microfluidic device, wherein the number of the droplet holders per cm 2 is equal to or greater than 10,000 and equal to or less than 10,000,000.

2. The microfluidic device according to claim 1 , further comprising a flat substrate, the flow channel being located on the flat substrate, and the droplet holder being a hole present on the substrate.

3. The microfluidic device according to claim 2 , further comprising a cover member, wherein the flow channel is a space sandwiched between the cover member and the substrate.

4. 4. The microfluidic device according to claim 2, wherein a ratio of a total area of ​​the openings of the droplet holder per unit area of ​​a region of the substrate in which the droplet holder is formed is 23% or more and 90% or less.

5. The microfluidic device according to any one of claims 1 to 4, wherein the total volume of the droplet holder is 0.2 µL or more and 2.0 µL or less.

6. 6. The microfluidic device according to claim 1, wherein a ratio of a total volume of the droplet holder to a volume of the flow channel is 5% or more and 40% or less.

7. 7. The microfluidic device according to claim 1, wherein a ratio of a depth of the droplet holder to a height of the flow channel is 3% or more and 150% or less.

8. A sample analysis method using the microfluidic device according to any one of claims 1 to 7, comprising: introducing an aqueous liquid containing a sample into the flow channel and allowing the droplet holder to hold the aqueous liquid; introducing a sealing liquid into the flow channel to replace the aqueous liquid present in the flow channel, and sealing the aqueous liquid in the droplet holder; causing a reaction in the droplet holder to generate a signal for detection; detecting said signal; A sample analysis method comprising:

9. The sample analysis method according to claim 8 , wherein the sample is a biomolecule.

10. The sample analysis method according to claim 8 or 9, wherein generating a signal for detection includes heating the microfluidic device to cause the reaction, and the temperature at which the microfluidic device is heated is 60°C or higher.

11. The sample analysis method according to any one of claims 8 to 10, wherein the signal is detected by imaging the microfluidic device.

12. The sample analysis method according to any one of claims 8 to 11, wherein the signal is fluorescence.

13. The sample analysis method according to any one of claims 8 to 12, wherein the reaction is an isothermal reaction.

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