JP2009145256A - Microchip and microchip analyzing system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To realize a microchip capable of bringing a plurality of kinds of liquids to flow into each other and then branching them at a prescribed mixture ratio, even if the length of its mixing channel is short. <P>SOLUTION: The microchip includes: a first inflow channel 101 for bringing first liquid to flow into a confluence section JC; a second inflow channel 102 and a third inflow channel 103 for bringing second liquid different from the first liquid to flow into the confluence section from an area being in the same plane as and on both the sides of the first inflow channel; an intermediate channel 110 for feeding the first liquid and the second liquid from the confluence section JC to a branch section SP, in the state of a laminar flow; a first outflow channel 111 for branching the confluent liquid of the first liquid and the second liquid fed from the second inflow channel 102 from the branch section SP, while keeping the laminar flow state from the confluence section JC; and a second outflow channel 112 for branching the confluent liquid of the first liquid and the second liquid fed from the third inflow channel 103 from the branch section SP, while keeping the laminar flow state. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to a microchip and a microchip analysis system.

  In recent years, a micro total analysis system (μTAS) has been attracting attention, in which a plurality of liquids are mixed and reacted in a microchip in which microchannels are integrated and processed, and the state of the reaction is detected and analyzed. Has been.

  μTAS has advantages such as a small amount of sample, a short reaction time, and a small amount of waste. When used in the medical field, the burden on the patient can be reduced by reducing the amount of specimen (blood, urine, wiping liquid, etc.), and the cost of the test can be reduced by reducing the amount of reagent. In addition, since the amount of sample and reagent is small, the reaction time is greatly shortened, and the efficiency of the test can be improved. Furthermore, since the device is small, it can be installed in a small medical institution, and a test can be performed quickly regardless of location.

  In a test using a microchip, for example, as shown in Patent Document 1, a microchip is connected to a micropump, and a driving liquid is supplied from the micropump so that a specimen or reagent contained in a flow path in the microchip is removed. The liquid is being delivered. When mixing a specimen and a reagent or reagents, a merging portion where a plurality of flow paths merge is provided, and mixing is performed at the merging portion.

In the microchip disclosed in Patent Document 2, two types of samples RG1 and RG2 are merged at the junction JCT. Then, a microchip is disclosed in which the two kinds of joined samples flow as a phase-separated phase flow and flow through the path A3, and are again separated into the samples RG1 and RG2 at the downstream branching section BFR and discharged from the discharge port. .
JP 2006-266923 A JP 2006-116479 A

  In the microchip disclosed in Patent Document 1, a long mixing channel 15 is fed in order to sufficiently mix two kinds of liquids. In such a case, when the mixed liquid mixed at a predetermined mixing ratio is to be divided, it is necessary to provide a branch portion after sufficiently mixing in the mixing flow path 15, which limits the degree of freedom in design. I was receiving.

  In addition, the microchip disclosed in Patent Document 2 is to send a sample without causing turbulent flow, and not to mix two types of samples.

  In view of the above problems, the present invention has an object to obtain a microchip that can be branched at a predetermined mixing ratio after a plurality of types of liquids are merged even when the length of a mixing channel is short. To do.

  The above object is achieved by the invention described below.

(1) an upstream opening into which a driving liquid from a connected external micropump is injected;
A plurality of storage portions provided in communication with the upstream opening and storing liquid;
A fine channel for feeding the liquid from the reservoir,
A merging portion that is provided in the fine flow path and merges the liquid sent through the plurality of fine flow paths;
A branch part for diverting the liquid joined at the joining part;
A microchip having
A first inflow path for allowing the first liquid to flow into the junction,
A second inflow path and a third inflow path that join a second liquid different from the first liquid from both sides in the same plane of the first inflow path at the merge portion;
An intermediate flow path for sending the first liquid and the second liquid in a laminar flow from the junction to the branch; and
A first outflow path for diverting the merged liquid of the second liquid sent from the second inflow path and the first liquid from the branch section in a state of forming a laminar flow from the merge section;
A second outflow path for diverting the combined liquid of the second liquid sent from the third inflow path and the first liquid from the branch portion in a laminar state;
A microchip comprising:

(2) The microchip according to (1) can be accommodated,
A micropump for sending the driving liquid to the upstream opening of the housed microchip;
A microchip analysis system comprising:

  According to the present invention, even when the length of the mixing channel is short, it is possible to obtain a microchip that can be branched at a predetermined mixing ratio after a plurality of types of liquids are merged.

  Although the present invention will be described based on an embodiment, the present invention is not limited to the embodiment.

[Analytical system configuration]
FIG. 1 is an external view of a microchip analysis system 8 using the microchip according to the present embodiment. The microchip analysis system 8 is a device that automatically reacts a sample and a reagent previously injected into the microchip 1 and automatically outputs a reaction result.

  A housing 82 of the microchip analysis system 8 includes an insertion port 83 for inserting the microchip 1 into the apparatus, a display unit 84, a memory card slot 85, a print output port 86, an operation panel 87, and an external input / output terminal 88. Is provided.

  The person in charge of inspection inserts the microchip 1 in the direction of the arrow in FIG. 1 and operates the operation panel 87 to start the inspection. In the microchip analysis system 8, the reaction in the microchip 1 is automatically inspected, and when the inspection is completed, the result is displayed on the display unit 84. The inspection result can be output from the print output port 86 or stored in a memory card inserted in the memory card slot 85 by operating the operation panel 87. Further, data can be stored in the personal computer or the like from the external input / output terminal 88 using, for example, a LAN cable. After completion of the inspection, the inspection person takes out the microchip 1 from the insertion port 83.

  FIG. 2 is a schematic perspective view of a microchip analysis system 8 using the microchip according to the present embodiment, and FIG. 3 is a configuration diagram. 2 and 3, the microchip is inserted through the insertion port 83 shown in FIG. 1 and the setting is completed.

  The microchip analysis system 8 includes a driving liquid tank 70 that stores a driving liquid L0 for feeding a sample and a reagent previously injected into the microchip 1, and a micropump 5 for supplying the driving liquid L0 to the microchip 1. The pump connection part 6 that connects the micropump 5 and the microchip 1 so that the driving liquid L0 does not leak, the temperature control unit 3 that controls the temperature of the necessary part of the microchip 1, and the temperature control so that the microchip 1 does not deviate. A chip pressing plate 2 for bringing the chip pressing plate 2 into close contact with the unit 3 and the pump connection unit 6; a pressing plate driving unit 21 for moving the chip pressing plate 2 up and down; a regulating member 22 for positioning the microchip 1 with respect to the micro pump 5 with high accuracy; A light detection unit 4 (4a and 4b) for detecting a reaction state between the specimen and the reagent in the microchip 1 is provided.

  The chip pressing plate 2 is retracted upward from the position shown in FIG. 3 in the initial state. Thereby, the microchip 1 can be inserted / removed in the direction of the arrow X, and the person inspecting inserts the microchip 1 from the insertion port 83 (see FIG. 1) until it comes into contact with the regulating member 22. Thereafter, the chip pressing plate 2 is lowered by the pressing plate driving unit 21 and comes into contact with the microchip 1, and the lower surface of the microchip 1 is in close contact with the temperature adjustment unit 3 and the pump connection unit 6.

  The temperature control unit 3 includes a Peltier element 31 and a heater 32 on the surface facing the microchip 1. When the microchip 1 is set in the microchip analysis system 8, the Peltier element 31 and the heater 32 are attached to the microchip 1. It comes to adhere closely. A part containing the reagent is cooled by the Peltier element 31 so that the reagent is not denatured, or the reaction part 139 where the specimen and the reagent react is heated by the heater 32 to promote the reaction.

  In the light detection unit 4 including the light emitting unit 4a and the light receiving unit 4b, the light from the light emitting unit 4a is irradiated to the microchip 1, and the light transmitted through the microchip 1 is detected by the light receiving unit 4b. The light receiving portion 4b is integrally provided inside the chip pressing plate 2. The light emitting part 4a and the light receiving part 4b are provided so as to face the detected part 148 of the microchip 1 shown in FIG.

  The micropump 5 is located on the pump chamber 52, the piezoelectric element 51 that changes the volume of the pump chamber 52, the first throttle channel 53 located on the microchip 1 side of the pump chamber 52, and the driving fluid tank 70 side of the pump chamber. The second throttle channel 54 is formed. The first throttle channel 53 and the second throttle channel 54 are narrow and narrow channels, and the first throttle channel 53 is longer than the second throttle channel 54.

  When the driving liquid L0 is fed in the forward direction (the direction toward the microchip 1), first, the piezoelectric element 51 is driven so that the volume of the pump chamber 52 is rapidly reduced. Then, a turbulent flow is generated in the second throttle channel 54 that is a short throttle channel, and the channel resistance in the second throttle channel 54 is relatively larger than that of the first throttle channel 53 that is a throttle channel. growing. As a result, the driving liquid L0 in the pump chamber 52 is predominantly pushed toward the first throttle channel 53 and fed. Next, the piezoelectric element 51 is driven so that the volume of the pump chamber 52 is gradually increased. Then, the driving liquid L0 flows from the first throttle channel 53 and the second throttle channel 54 as the volume in the pump chamber 52 increases. At this time, since the length of the second throttle channel 54 is shorter than that of the first throttle channel 53, the channel resistance of the second throttle channel 54 is smaller than that of the first throttle channel 53. Thus, the driving liquid L 0 flows into the pump chamber 52 predominantly from the second throttle channel 54. When the piezoelectric element 51 repeats the above operation, the driving liquid L0 is fed in the forward direction.

  On the other hand, when the driving liquid L0 is fed in the reverse direction (direction toward the driving liquid tank 70), first, the piezoelectric element 51 is driven so that the volume of the pump chamber 52 is gradually reduced. Then, since the length of the second throttle channel 54 is shorter than that of the first throttle channel 53, the channel resistance of the second throttle channel 54 is smaller than that of the first throttle channel 53. . As a result, the driving liquid L0 in the pump chamber 52 is predominantly pushed out toward the second throttle channel 54 and fed. Next, the piezoelectric element 51 is driven so as to rapidly increase the volume of the pump chamber 52. Then, the driving liquid L0 flows from the first throttle channel 53 and the second throttle channel 54 as the volume in the pump chamber 52 increases. At this time, turbulent flow is generated in the second throttle channel 54, which is a short throttle channel, and the channel resistance in the second throttle channel 54 is relatively larger than that of the first throttle channel 53, which is a throttle channel. Become bigger. As a result, the driving liquid L 0 flows into the pump chamber 52 predominantly from the first throttle channel 53. When the piezoelectric element 51 repeats the above operation, the driving liquid L0 is fed in the reverse direction.

  The pump connection portion 6 is formed of a close contact surface made of a resin having flexibility (elasticity, shape followability) such as polytetrafluoroethylene or silicone resin in order to ensure necessary sealing performance and prevent leakage of driving fluid. It is preferred that Such a close contact surface having flexibility may be, for example, due to the constituent substrate of the microchip itself, or may be a separate additional having flexibility attached around the flow path opening in the pump connection portion 6. It may be due to a member.

[Configuration of Microchip 1]
FIG. 4 shows an example of the microchip 1 according to the present embodiment. In the same figure, arrangement | positioning of the microchannel and channel element in the state from which the coating substrate was removed is shown typically.

  The microchip 1 is provided with a fine channel and a channel element for mixing and reacting a liquid specimen (sample) on the microchip 1 using a hydrophobic base material in the same manner as a liquid reagent. Yes. The fine channel is formed in the order of micrometers, for example, the width w is several tens to several hundreds μm, preferably 50 to 300 μm, and the height h is about 25 to 1000 μm, preferably 50 to 300 μm.

  Hereinafter, the reaction and detection steps in the microchip will be described. In the microchip 1 shown in FIG. 4, the two reaction detection flow paths are symmetrically arranged (left half and right half in the figure). For example, the reaction detection channel in the left half is used for detecting the reaction between the sample and the reagent, and the right half is used for detecting the reaction between the internal control and the reagent for monitoring whether the reaction detection is normally performed. . Since the two reaction detection channels are symmetrically arranged and basically have the same channel configuration, only the reaction detection channel for the left half of the sample and the reagent will be described below.

  g (or g1 to g8) is an upstream opening that is released from one surface of the microchip 1 to the outside. The plurality of upstream openings g are aligned with the channel openings provided on the connection surface of the micropump 5 when the microchip 1 is overlapped and connected to the micropump 5 via the pump connection 6. It communicates with the micropump 5. Then, a driving liquid L0 for feeding liquid is injected from the upstream opening.

  ij (or ij1 to ij3) is an injection hole for injecting a liquid such as a reagent or a specimen (hereinafter also simply referred to as a reagent liquid), and is an opening opened to the outside from the upper surface of the microchip 1. The reagent solution is injected with the upstream opening g in the vicinity of each injection hole ij open. The injected liquid is sent through the fine channel toward the nearby upstream opening g. In the present embodiment, a part of the fine channel for storing the liquid is used as the storage part st (or st1 to 8). At the time of reagent solution injection, the upstream opening g and the injection hole ij are opened, and only the injection hole ij is sealed after the reagent injection. Then, a liquid such as a reagent or a specimen is sent through the air by the driving liquid L0 sent from the micropump 5 communicating with the reservoir st and the upstream opening g.

  In the reservoirs st1, st2, and st3, reagent solutions used for gene amplification reactions are stored in advance. The reagent solution stored in the storage units st2 and st3 is different from the first reagent solution L1 (first liquid) stored in the storage unit st1, and is different from the second reagent solution L2 (second liquid). Is stored.

  JC is a junction and SP is a branch. The reagent liquids stored in the upstream storage units st1 to st3 merge at the junction JC and then branch again at the branch SP. Details of the joining and splitting of the two types of liquid will be described later.

  Reference numeral 130 denotes a reagent solution storage unit in which reagent solutions that have joined together on the upstream side are mixed. The specimen is stored in the storage unit st4, and the reagent is stored in the storage unit st5. The reagent solution storage unit 130, the reagent solution in the storage unit st5, and the sample in the storage unit st4 merge in the joint channel 131.

  A mixing flow path 138 is provided downstream of the combined flow path 131 for mixing the sample and the reagent with sufficient molecular diffusion. A reaction unit 139 is provided downstream of the mixing channel 138.

  The reaction unit 139 is a part that heats and reacts the mixed liquid of the sample and the reagent sufficiently mixed in the mixing channel 138. When the microchip 1 is set in the microchip analysis system 8, the reaction unit 139 performs microchip analysis. The heaters 32 of the system 8 are opposed to each other. The gene amplification reaction is performed by heating the reaction unit 139 with the heater 32. The amplification product amplified by the reaction unit 139 by the gene amplification reaction is sent to the detection unit 148 and detected by the light detection unit 4.

  A means for detecting the amplification product in the detected part 148 will be described. The detected part 148 cannot detect the amplified product as it is, and in general, the amplified product is reacted with the reactant carried on the flow path wall of the detected part 148 to thereby detect the amplified product. In addition, a fluorescently labeled probe is bound to the amplification product so that it can be detected optically. At least the detection part of the detected part 148 is made of a transparent material, preferably a transparent plastic, in order to enable optical measurement.

  Here, the genetic test will be specifically described as an example.

  (1) The reagent is a biotin-modified primer, and the sample of the sample is amplified in the reaction unit 139, and the sample after reaction in which the amplified gene is made into a single strand by denaturation treatment is sent to the detection unit 148. A biotin-affinity protein such as streptavidin (avidin, streptavidin, extraavidin, preferably streptavidin) is supported and immobilized in advance on the channel wall of the detection portion 148 as a reactive substance. When the sample after the reaction in the reaction part 139 flows into the detected part 148, the gene of the specimen is fixed to the channel wall of the detected part 148 by a binding reaction between the biotin affinity protein and biotin labeled on the probe substance. Is trapped. The above-described binding reaction between the biotin affinity protein and biotin is a known avidin-biotin reaction.

Further, through a step of trapping an amplification product (in this example, an amplification gene), a probe DNA fluorescently labeled with FITC (Fluorescein isothiocyanate) is passed to the detected portion 148 that traps the amplification gene, and this is immobilized. Hybridize to the gene. (A previously hybridized amplification gene and fluorescently labeled probe DNA may be trapped at the detected portion.)
(2) A gold colloid solution whose surface is modified with an anti-FITC antibody that specifically binds to FITC is allowed to flow into the microchannel, and thereby the gold colloid is adsorbed to the FITC-modified probe hybridized with the gene.

  (3) The concentration of the gold colloid in the fine channel is optically measured.

  As described above, in the detected part 148, each reagent contained in the fine channel is sequentially sent and reacts with the reactants immobilized on the detected part 148. This order is determined in advance. .

  The amplification product sent from the reaction unit 139 to the detection unit 148 starts a reaction with the reactant in the detection unit 148 (for example, an avidin-biotin reaction).

  Next, the feeding of the driving liquid L0 from the upstream opening g6 is started, and the sample (for example, probe DNA) in the storage unit st6 is fed to the downstream detection target 148, whereby the reactants 148 and the reactants in the detection target 148 are high. A hybridization reaction is performed.

  Thereafter, the feeding of the driving liquid L0 from the upstream opening g7 is started, and the dye solution (for example, PEGylated gold colloid) in the storage part st7 is fed to the detected part 148, whereby the antigen-antibody reaction is caused in the detected part 148. Be started. After the gold colloid reacts with the amplification product, an extra gold colloid is present when it is detected by the detected portion 148. In order to wash away this surplus gold colloid, the cleaning liquid in the storage part st8 is sent to the detected part 148 by starting to feed the driving liquid L0 from the upstream opening g8.

  The amplification product that has been sent to the detected portion 148 and subjected to a reaction for detection is detected by the light detecting portion 4. The amplified product after detection is sent to the waste liquid section 160.

[Flow path configuration of main part according to this embodiment]
5 and 6 schematically show the flow path configuration of the main part according to the present embodiment. This corresponds to the broken line region in FIG.

  In the figure, 101 is a first inflow path, 102 is a second inflow path, 103 is a third inflow path, JC is a merge section, 110 is an intermediate flow path, SP is a branch section, and 111 is a first outflow path. , 112 is a second outflow path. The outflow path 111 and the outflow path 112 are each in communication with a separate reagent solution storage unit 130 on the downstream side. Each flow path excluding the injection hole ij and the upstream opening g is formed on the same plane.

  FIG. 5 is a diagram showing an initial state. In the figure, the first reagent liquid L1 injected from the injection hole ij1 (hereinafter simply referred to as reagent liquid L1) is different from the first reagent liquid injected into the storage part st1 from the injection holes ij2 and ij3. The second reagent solution L2 (hereinafter simply referred to as reagent solution L2) is stored in storage units st2 and st3. The storage parts st1, st2, and st3 communicate with different upstream openings g1, g2, and g3, respectively.

  The reagent liquids L1 and L2 are fed to the downstream junction JC by feeding the driving liquid L0 from the upstream openings g1, g2 and g3 by the micropump 5, respectively. The injection pressure of the driving liquid L0 sent from the upstream openings g1, g2, and g3 is set to be substantially the same.

  FIG. 6 shows a state in which the reagent liquids L1 and L2 are joined at the joining part. The reagent liquids L1 and L2 are sent through the air air when the micropump 5 injects the driving liquid L0 into the flow path. Further, as shown in the figure, in the intermediate flow path 110, the reagent liquids L1 and L2 are fed in a laminar flow state in which the flow direction is parallel to the axial direction of the flow path.

Here, in the intermediate flow path 110, the Reynolds number R (= U × 1 × ρ / μ) does not exceed the critical Reynolds number Re (approximately 2000) so that the combined liquid of the reagent liquids L1 and L2 does not become a turbulent flow. The flow rate conditions are set as follows.
U: Flow velocity (m / s)
l: Channel diameter (m)
ρ: Condensed liquid density (kg / m)
μ: Viscosity of combined liquid (kg / ms)
The combined liquid is then sent through the intermediate channel 110 in a laminar state and is diverted to the downstream outflow passages 111 and 112 at the branching portion SP in a laminar state and sent to the reagent solution storage unit 130 on the downstream side. To be liquidated.

  Since the flow is divided in the laminar flow state, all of the second reagent liquid L2 sent from the second inflow path 102 is sent to the first outflow path 111 and sent from the third inflow path 103. The two reagent liquids L2 are all sent to the second outflow path 112.

  Further, the inflow channels 101, 102, 103 and the outflow channels 111, 112 shown in the figure are formed symmetrically about a line extending from the first inflow channel 101 and the branch SP. With this configuration, the first reagent liquid L1 sent from the first inflow path 101 is equally divided and sent to the first outflow path 111 and the second outflow path. In other words, the mixed liquids sent to the outflow paths 111 and 112 have the same mixing ratio of the first reagent liquid L1 and the second reagent liquid L2, respectively, and these mixed liquids contain the left and right reagent liquids. The solution is completely mixed while being fed to the unit 130. That is, even if the length of the intermediate channel 110 is short, the same mixed solution can be sent to the left and right reagent solution storage portions 130.

  According to the present embodiment, two different liquids are merged and separated at the branching portion in a laminar flow state, so even if the length of the intermediate flow path is short, the mixing ratio of the mixed liquid after the diversion Can be set to a predetermined ratio, and as a result, the degree of freedom in designing the flow path of the microchip can be increased.

[Second Embodiment]
A second embodiment will be described with reference to FIG. FIG. 7 schematically shows the flow path configuration of the main part of the microchip. This corresponds to the broken line region in FIG. In the second embodiment, the second reagent solution L2 is stored in the storage unit st12, and the first reagent solution L1 is stored in the storage unit L11.

  SP2 is a second branch section. In the second branch part SP2, the reagent liquid L2 sent from the storage part st12 is divided into the second inflow path 102a and the third inflow path 103a on the upstream side of the junction JC.

  Also in the embodiment shown in the figure, similarly, by supplying the driving liquid L0 from the upstream openings g12 and g11 at a predetermined timing, the reagent liquids L1 and L2 are joined at the joining part JC and remain in the laminar flow state. The intermediate flow path 110, the first outflow path 111, and the second outflow path 112 are fed.

  According to the present embodiment, two different types of liquids are joined to form a joined liquid, and are split at the branch portion in a laminar flow state. The mixing ratio of the merging liquid can be set to a predetermined ratio. Further, since it is not necessary to store the second reagent liquid L2 at a plurality of locations, the management of the reagent is facilitated.

[Flow rate ratio]
Next, the flow rate ratio will be described. In the embodiment described below, the configuration is basically the same as the microchip in the first and second embodiments, but an asymmetric microchip is also included. The asymmetric microchip here means that “the inflow channels 101, 102, 103 and the outflow channels 111, 112 are not formed symmetrically about a line extending from the first inflow channel 101 and the branch SP”. Say things.

Here, the flow rate in each channel is defined. For the intermediate flow path 110,
The flow rate of the first liquid from the first inflow path 101 is a,
(However, the flow rate to the first outflow channel of the first liquid is a1, and the flow rate to the second outflow channel is a2.)
The flow rate of the second liquid from the second inflow path 102 is b1,
The flow rate of the second liquid from the third inflow path 103 is b2,
The flow rate from the first outflow passage 111 is p (= a1 + b1),
The flow rate from the second outflow passage 112 is q (= a2 + b2),
And when
The mixing ratio r1 of the first liquid and the second liquid in the first outflow path 111 and the second outflow path 112 is the same (r1 = a1 / b1 = a2 / b2).

  In such a case, the flow rate ratio r22 (b1 / b2) of the flow rates b1 and b2 is set according to the flow rate ratio r21 (p / q) of the flow rates p and q. Specifically, r21 = r22. By doing in this way, it becomes possible to set the flow rate ratio r21 of the 1st outflow path 111 and the 2nd outflow path 112 to arbitrary values.

  Further, the flow rate ratio r23 (a / b) between the total flow rate b (= b1 + b2) from the second inflow channel 102 and the third inflow channel 103 and the flow rate a from the first inflow channel 101 is set according to the mixing ratio r1. Has been. Specifically, r1 = r23. In this way, the mixing ratio r1 of the two types of liquid can be set to a predetermined ratio.

[Third Embodiment]
A third embodiment will be described with reference to FIG. This figure schematically shows the flow path configuration of the main part of the microchip. This corresponds to the broken line region in FIG. In the third embodiment, the first reagent solution L1 is stored in the storage unit st21, the second reagent solution L2 is stored in the storage units st22 and st23, and the third reagent solution L3 different from the reagent solutions L1 and L2 is stored. Stored in the parts st24 and 25, respectively.

  The third reagent liquid L3 is fed through the fourth inflow path 104 and the fifth inflow path 105. And the inflow channels 104 and 105 merge with the inflow channels 101 to 103 at the junction JC from both sides of the same plane. The reagent liquids L1, L2, and L3 are fed in the laminar flow state at the junction JC and the intermediate flow path 110, and are divided into the first outflow path 111 and the second outflow path 112 at the branch section SP. .

  Since the flow is divided in a laminar flow state, (1) all of the reagent liquid L2 and the reagent liquid L3 sent from the inflow path 102 and the inflow path 104 are sent to the first outflow path 111. (2) All of the reagent solution L2 and the reagent solution L3 sent from the inflow passage 103 and the inflow passage 105 are sent to the second outflow passage 112.

  In addition, the inflow channels 101 to 105 and the outflow channels 111 and 112 shown in the figure are formed symmetrically about a line extending from the first inflow channel 101 and the branch SP. With this configuration, the first reagent liquid L1 sent from the first inflow path 101 is equally divided and sent to the first outflow path 111 and the second outflow path. That is, the mixed liquids sent to the outflow paths 111 and 112 have the same mixing ratio of the reagent liquids L1, L2, and L3, and the mixed liquids are sent to the left and right reagent liquid storage sections 130. It will be in a completely mixed state. That is, the same mixed liquid can be sent to the left and right reagent storage units.

[Flow rate ratio]
Here, the flow rate ratio in the third embodiment will be described. In the embodiment described below, the configuration is basically the same as the microchip in the third embodiment, but an asymmetric microchip is also included.
For the intermediate flow path 110,
The flow rate of the first liquid from the first inflow path 101 is a,
(However, the flow rate to the first outflow channel of the first liquid is a1, and the flow rate to the second outflow channel is a2.)
The flow rate of the second liquid from the second inflow path 102 is b1,
The flow rate of the second liquid from the third inflow path 103 is b2,
The flow rate of the third liquid from the fourth inflow path 104 is c1,
The flow rate of the third liquid from the fifth inflow path 105 is c2,
The flow rate from the first outflow passage 111 is pp (= a1 + b1 + c1),
The flow rate from the second outflow passage 112 is qq (= a2 + b2 + c2),
And when
The mixing ratio r2 (a1: b1: c1) of the first liquid, the second liquid, and the third liquid in the first outflow path 111 is the same as the mixing ratio r2 (a2, b2, c2) in the second outflow path 112. It is.

  Depending on the mixing ratio r2, the total flow rate c (= c1 + c2) from the fourth inflow channel 104 and the fifth inflow channel 105, and the total flow rate b (= b1 + b2) from the second inflow channel 102 and the third inflow channel 103. The flow ratio r31 (a: b: c) with the flow rate a from the first inflow path 101 is set. Specifically, the flow rate ratio r31 and the mixing ratio r2 are the same. By doing in this way, it becomes possible to make the mixing ratio r2 of three types of liquids into a predetermined ratio.

It is an external view of the microchip analysis system 8 using the microchip which concerns on this embodiment. It is a schematic perspective view of the microchip analysis system 8 using the microchip which concerns on this embodiment. It is a schematic perspective view of the microchip analysis system 8 using the microchip which concerns on this embodiment. 1 shows an example of a microchip 1 according to the present embodiment. 1 schematically shows a flow path configuration of a main part of a microchip according to the present embodiment. 1 schematically shows a flow path configuration of a main part of a microchip according to the present embodiment. The flow-path structure of the principal part of the microchip which concerns on 2nd Embodiment is shown typically. The flow path structure of the principal part of the microchip which concerns on 3rd Embodiment is shown typically.

Explanation of symbols

8 Microchip analysis system 1 Microchip 6 Pump connection part g Upstream opening part st Storage part ij Injection hole 101, 102, 103, 104, 105 Inflow path JC Merge part 110 Intermediate flow path SP Branch part 111, 112 Outflow path 139 Reaction Section 148 Detection section 160 Waste liquid section 70 Drive liquid tank L0 Drive liquid

Claims (11)

An upstream opening into which drive fluid from a connected external micropump is injected;
A plurality of storage portions provided in communication with the upstream opening and storing liquid;
A fine channel for feeding the liquid from the reservoir,
A merging portion that is provided in the fine flow path and merges the liquid sent through the plurality of fine flow paths;
A branch part for diverting the liquid joined at the joining part;
A microchip having
A first inflow path for allowing the first liquid to flow into the junction,
A second inflow path and a third inflow path that join a second liquid different from the first liquid from both sides in the same plane of the first inflow path at the merge portion;
An intermediate flow path for sending the first liquid and the second liquid in a laminar flow from the junction to the branch; and
A first outflow path for diverting the merged liquid of the second liquid sent from the second inflow path and the first liquid from the branch section in a state of forming a laminar flow from the merge section;
A second outflow path for diverting the combined liquid of the second liquid sent from the third inflow path and the first liquid from the branch portion in a laminar state;
A microchip comprising: The second liquid is fed from two different reservoirs, and the two reservoirs and the reservoir that stores the first liquid are communicated with the upstream openings different from each other. The microchip according to claim 1. 2. The second liquid according to claim 1, wherein the second liquid is supplied from one reservoir and has a second branch portion that is divided into a second inflow path and a third flow path on the upstream side of the junction. Microchip. 4. The micro of claim 1, wherein a mixing ratio of the first liquid and the second liquid in the first outflow path and a mixing ratio in the second outflow path are the same. Chip. In the merging portion, the second inflow passage and the third inflow passage are in a symmetrical relationship with respect to the first inflow passage, and in the branch portion, the first outflow passage and the second outflow passage are in the branch portion. 5. The microchip according to claim 1, wherein the microchip has a symmetric relationship with respect to the center. The flow rate ratio between the second inflow passage and the third inflow passage is set according to the flow rate ratio between the first outflow passage and the second outflow passage. Microchip. According to the mixing ratio of the first liquid and the second liquid in the first outflow path and the second outflow path,
5. The microchip according to claim 4, wherein a flow rate ratio between a total flow rate of the second inflow channel and the third inflow channel and a flow rate of the first inflow channel is set. A fourth inflow path and a fifth inflow path that merge a third liquid different from the first liquid and the second liquid from both sides in the same plane of the first inflow path in the merge portion;
The microchip according to claim 1, comprising: 9. The microchip according to claim 8, wherein a mixing ratio of the first liquid, the second liquid, and the third liquid in the first outflow path and a mixing ratio in the second outflow path are the same. . According to the mixing ratio of the first liquid, the second liquid, and the third liquid in the first outflow path and the second outflow path,
A flow rate ratio of the total flow rate of the fourth inflow channel and the fifth inflow channel, the total flow rate of the second inflow channel and the third inflow channel, and the flow rate of the first inflow channel is set. The microchip according to claim 9. The microchip according to any one of claims 1 to 10 can be accommodated,
A micropump for sending the driving liquid to the upstream opening of the housed microchip;
A microchip analysis system comprising:

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