JP5273990B2 - Analytical device, analytical apparatus and analytical method using the same - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an analyzing device capable of reducing leakage risk when handling sample liquid. <P>SOLUTION: Though a sectional size in the thickness direction of a measuring spot 29 for holding the sample liquid can be adjusted depending on a measuring condition, for example, the size is constituted to be 1,000-3,000 &mu;m, a channel threshold 28 is provided on a furthermore inner peripheral position than the level of the held sample liquid, and the sectional size (g3) in the thickness direction is restricted to be 50-300 &mu;m by which passage of liquid can be restricted by a capillary force. <P>COPYRIGHT: (C)2009,JPO&amp;INPIT

Description

  The present invention relates to an analysis device used for analyzing a liquid collected from a living organism, an analysis apparatus using the same, and an analysis method. More specifically, the present invention prevents leakage of a sample liquid from the analysis device. Related to biosafety technology.

  Conventionally, as a method for analyzing a liquid collected from a living organism or the like, a method for analyzing using a device for analysis in which a liquid channel is formed is known. The analytical device can control the fluid using a rotating device, and utilizes centrifugal force to dilute the sample liquid, measure the solution, separate the solid component, transfer and distribute the separated fluid, Since a solution and a reagent can be mixed, various biochemical analyzes can be performed.

As shown in FIG. 25, the analytical device described in Patent Document 1 that transfers a solution using centrifugal force injects a sample liquid into an accommodation cavity 72 from an injection port 71 using an insertion instrument such as a pipette, and the analytical device. After the sample solution is transferred to the separation cavity 73 by the rotation of 70 and centrifuged, the solution component is collected in the measurement channel 75 via the connection channel 74, and in the measurement channel 75 by the next rotation of the analyzing device 70. The solution component is transferred to the measurement spot 76, and unnecessary sample liquid in the separation cavity 73 is discharged to the overflow cavity 78 using the siphon effect of the connection flow path 77.
Japanese Patent Laid-Open No. 2007-077866

  However, in Patent Document 1, air holes 81 and 82 communicating with the atmosphere are formed at the inner peripheral positions of the measurement spot 76 and the overflow cavity 78. During the analysis, since the sample liquid is pushed and held in the outer peripheral direction of the measurement spot 76 and the overflow cavity 78 by the centrifugal force accompanying the rotation of the analysis device 70, there is little risk of leakage to the outside. In the process of discarding the analysis device 70 that has been analyzed, there is a high risk that the sample liquid leaks from the air holes 81 and 82 and an operator contacts the sample liquid to cause an infection accident.

  An object of the present invention is to provide an analysis device that can reduce the risk of leakage during handling of a sample liquid held in the analysis device, and an analysis apparatus and an analysis method using the same.

The analytical device of the present invention has a first microchannel structure for transferring a sample liquid toward a measurement spot by a centrifugal force generated when the analysis device is rotated around a rotation center, and accesses the sample at the measurement spot. An analytical device used for reading is provided with another second microchannel structure for holding a sample liquid that has become surplus during transfer of the first microchannel structure, and the second microchannel structure comprises: A first overflow cavity to which a plurality of overflow channels to which surplus sample liquid is transferred at different timings are connected, and a position farther from the rotation center than the first overflow cavity. The first overflow key in a direction transverse to the direction of the centrifugal force at the boundary between the second overflow cavity and the first overflow cavity and the second overflow cavity; A threshold that restricts the thickness of the flow path connecting the bite and the second overflow cavity, and the thickness of the flow path is such that the sample liquid is allowed to flow from the first overflow cavity to the second overflow by the centrifugal force. In a state where the sample liquid can be transferred to the cavity and the centrifugal force does not act, the sample liquid is of a size that prevents the sample liquid from being transferred between the first and second overflow cavities by a capillary force .

The analytical device of the present invention has a first microchannel structure for transferring a sample liquid toward a measurement spot by a centrifugal force generated when the analysis device is rotated around a rotation center, and accesses the sample at the measurement spot. An analytical device used for reading is provided with another third microchannel structure that holds a sample liquid that has become surplus during transfer of the first microchannel structure, and the third microchannel structure comprises: A third overflow cavity fluidly connected to each other, and a fourth overflow cavity formed on the outer peripheral side of the third overflow cavity with respect to the rotation center and communicated with the third overflow cavity. An air hole communicating with the atmosphere side is formed in the third overflow cavity, and the cross-sectional dimension in the thickness direction of the fourth overflow cavity is the third overflow cavity. Characterized in that it is set in gap to the action of capillary force smaller than the cross-sectional dimension in the thickness direction.

The analysis device according to claim 3 of the present invention is characterized in that, in claim 1, an air hole communicating with the atmosphere side is provided in an area on the inner peripheral side of the sill where no capillary force acts .

According to a fourth aspect of the present invention, there is provided an analytical device according to the first or second aspect , wherein the sample liquid is sampled, a rotation driving means for rotating the analytical device around an axis, and the rotation. And analyzing means for accessing and analyzing the sample in the analyzing device based on the solution transferred by the driving means, so that the sample liquid can be transferred to the measurement spot and the overflow cavity by the rotation of the rotating driving means. It is characterized by comprising.

The analysis method according to claim 5 of the present invention is an analysis method using the analysis device according to claim 1 or 2, wherein the analysis device is rotated and spotted on the analysis device. Transferring at least a part of the sample liquid to the measurement spot, transferring other sample liquid to the overflow cavity, mixing the transferred sample liquid and reagent, and rotating the analytical device. And a step of accessing the sample of the measurement spot at a timing when the measurement spot is present at the reading position.

  According to this configuration, the sample liquid held in the measurement spot or overflow cavity can be trapped using capillary force to suppress outflow from the air hole, and the risk of causing an infection accident for the operator. Can be reduced.

Embodiments of an analysis device, an analysis apparatus using the analysis device, and an analysis method according to the present invention will be described below with reference to FIGS.
FIG. 1 shows a state in which the analysis device 1 according to the embodiment of the present invention is set on the rotor 103 of the analyzer, and FIG. 2 shows the surface of the analysis device 1 in contact with the rotor 103 facing upward. It shows a disassembled state.

  The analysis device 1 includes a protective cap 2 for preventing scattering of a sample liquid, a base substrate 3 on which a microchannel structure having fine irregularities on its surface is formed, a cover substrate 4 that covers the surface of the base substrate 3, and a dilution. A diluting unit 5 holding the liquid, and an opening button 6 for discharging the diluting liquid in the diluting unit 5 set in one of the several concave portions 50 formed on the upper surface of the base substrate 3; It is composed of five parts.

  The base substrate 3 and the cover substrate 4 are joined with the dilution unit 5 and the like set therein, and the protective cap 2 is attached to the joined substrate. The opening button 6 is joined around the position of the opening hole 7 formed in the cover substrate 4.

  By covering the openings of several concave portions formed on the upper surface of the base substrate 3 with the cover substrate 4, a flow path connecting between a plurality of storage areas described later (same as measurement spots described later) and the storage areas. Etc. are formed (see FIG. 2). Necessary ones of the storage areas are loaded with reagents necessary for various analyses.

  The analyzing device 1 can collect a sample solution, for example, a solution such as blood, from the inlet 11, and closes the protective cap 2 and sets it on the rotor 103 of the analyzer to analyze the component of the sample solution. It can be carried out. Reference numeral 102 denotes an axial center of the rotor 103 during rotation.

  The analysis device 1 includes a centrifugal force generated by rotating the analysis device 1 around the axial center 102 located on the inner periphery of the sample solution taken in from the injection port 11 and the analysis solution. The capillary cap force of the capillary channel provided in the device 1 is used to transfer the solution inside the analytical device 1, and the protective cap 2 is a sample solution adhering to the vicinity of the inlet 11. Is attached to prevent scattering due to centrifugal force during analysis.

  As a material of the parts constituting the analytical device 1 of the present invention, a resin material having a low material cost and excellent mass productivity is desirable. Since the analysis apparatus analyzes the sample liquid by an optical measurement method that measures light transmitted through the analysis device 1, the material of the base substrate 3 and the cover substrate 4 may be PC, PMMA, AS, MS, or the like. A highly transparent resin is desirable.

  Moreover, as the material of the dilution unit 5, since it is necessary to enclose the dilution liquid inside the dilution unit 5 for a long period of time, a crystalline resin having a low moisture permeability such as PP or PE is desirable. Since the opening button 6 is deformed and used when the dilution unit 5 is opened, a crystalline resin such as PP having a high elastic modulus is desirable. As a material of the protective cap 2, there is no particular problem as long as it is a material with good moldability, and an inexpensive resin such as PP or PE is desirable.

  The base substrate 3 and the cover substrate 4 are preferably joined by a method that hardly affects the reaction activity of the reagent carried in the storage area, such as ultrasonic welding or laser welding, in which reactive gas or solvent is less likely to be emitted during joining. Is desirable.

  Further, a hydrophilic treatment for increasing the capillary force is applied to the portion where the solution is transferred by the capillary force due to the minute gap between the substrates 3 and 4 by joining the base substrate 3 and the cover substrate 4. Specifically, hydrophilic treatment using a hydrophilic polymer or a surfactant is performed. Here, the hydrophilic property means that the contact angle with water is less than 90 degrees, and more preferably, the contact angle is less than 40 degrees.

3 to 6 show an analysis apparatus in which the analysis device 1 is set.
In FIG. 3, the analysis device 1 is mounted on a rotor 103 that rotates about the axis 102 of the analysis apparatus 100 with the base substrate 3 and the cover substrate 4, the cover substrate 4 side facing down. The analysis is performed with the lid 101 closed.

  As shown in FIGS. 4 and 5, the analysis apparatus 100 includes a rotation driving means 107 for rotating the rotor 103, an optical measurement means 109 for optically measuring the solution in the analysis device 1, and the rotor 103. The control means 108 for controlling the rotation speed and direction of rotation, the measurement timing of the optical measurement means, the arithmetic unit 110 for processing the signal obtained by the optical measurement means 109 and calculating the measurement results, and the arithmetic part 110 And a display unit 111 for displaying the obtained result.

  The rotation driving means 107 not only rotates the analyzing device 1 around the axis 102 at a predetermined rotation speed around the axis 102 via the rotor 103 but also a predetermined centering on the axis 102 at a predetermined stop position. The analyzing device 1 can be swung by reciprocating left and right with an amplitude range and period. Here, the motor 104 is used as the rotation driving means 107 to rotate the rotor 103 around the axis 102. The shaft center 102 is attached so as to be rotatable at an inclination angle θ ° around a predetermined position on the shaft center 102.

  Here, the rotational operation and the swinging operation of the analysis device 1 are performed by the single rotational driving means 107. However, in order to reduce the load on the rotational driving means 107, the driving means for the swinging operation is separately provided. It does not matter if it is provided. Specifically, the analyzing device 1 set on the rotor 103 is brought into direct or indirect contact with a vibration means such as a vibration motor prepared separately from the motor 104. The inertial force is imparted to the solution in the analytical device 1 by swinging.

  The optical measuring means 109 detects the amount of transmitted light that has passed through the analysis device 1 out of the laser light source 105 that irradiates the measurement unit of the analysis device 1 with laser light and the laser light emitted from the laser light source 105. The photo detector 106 is provided. When the rotor 103 is made of a material that is inferior in translucency or is not translucent, holes 51 and 52 are formed in the mounting position of the analysis device 1 of the rotor 103.

  Here, a laser light source 105 that can switch the wavelength of the emitted light is used, and a photodetector 106 that can detect light of any wavelength of the emitted light of the laser light source 105 is used.

Note that only a plurality of pairs of laser light sources 105 and photodetectors 106 can be provided in accordance with the types of wavelengths necessary for measurement.
Further, the analysis apparatus 100 can operate an opening means for automatically opening the dilution unit 5 in the analysis device 1, specifically, an opening button 6 of the analysis device 1 set on the rotor 103. The rotor 103 may be provided with an arm capable of moving up and down, and a mechanism for pushing up the opening button 6 by the arm may be provided.

  As shown in FIG. 5, the rotor 103 is attached to an inclined axis 102 and is inclined by an inclination angle θ ° with respect to the horizontal line. The rotor 103 is arranged in the analysis device 1 according to the rotation stop position of the analysis device 1. The direction of gravity applied to the solution can be controlled.

  Specifically, when the analysis device 1 is stopped at the position shown in FIG. 6A (a position near 180 ° when expressed as 0 ° (360 °) directly above), the analysis device 1 Since the lower side 53 of the lower side 53 faces downward as viewed from the front, the solution in the analytical device 1 receives gravity toward the outer peripheral direction (lower side 53).

  When the analysis device 1 is stopped at a position near 60 ° shown in FIG. 6B, the upper left side 54 of the analysis device 1 faces downward as viewed from the front. The solution is subjected to gravity in the upper left direction. Similarly, at the position near 300 ° shown in FIG. 6C, the upper right side 55 of the analytical device 1 faces downward as viewed from the front, so that the solution in the analytical device 1 is gravitational toward the upper right direction. Receive.

  In this manner, by providing the axis 102 with an inclination and stopping the analysis device 1 at an arbitrary position, it can be used as one of driving forces for transferring the solution in the analysis device 1 in a predetermined direction. .

  The magnitude of gravity applied to the solution in the analysis device 1 can be set by adjusting the inclination angle θ of the axis 102, and the amount of liquid to be transferred and the force attached to the wall surface in the analysis device 1. It is desirable to set according to the relationship.

  The inclination angle θ is preferably in the range of 10 ° to 45 °. If the inclination angle θ is smaller than 10 °, the gravity applied to the solution may be too small to obtain the driving force necessary for the transfer. If the angle exceeds 45 °, the load on the shaft center 102 may increase, or the solution transferred by centrifugal force may move freely by its own weight and be uncontrollable.

  In the analyzer 100 of this embodiment, the tilt angle θ is fixed at an arbitrary angle in the range of 10 ° to 45 °, and the motor 104, the laser light source 105, and the photodetector 106 that are the rotation drive means 107 are also tilted. Although it is attached in parallel with the shaft center 102, the inclination angle θ can be adjusted to an arbitrary angle, and the motor 104, the laser light source 105, and the photodetector 106 can be tracked to change the angle so that the analysis can be performed. The optimum inclination angle can be set according to the specifications of the device 1 for use and the transfer process in the device 1 for analysis. Here, when the inclination angle θ can be adjusted to an arbitrary angle, the range of the inclination angle θ is preferably 0 ° to 45 °, and when it is not desired to be affected by gravity, the inclination angle is 0 °, that is, the rotor. 103 can be rotated horizontally.

7 to 14 show details of the analyzing device 1.
FIG. 7 shows a dilution unit opening part of the analytical device 1.
Fig.7 (a) is a top view which shows the attachment position of the opening button 6, FIG.7 (b) shows AA sectional drawing of Fig.7 (a).

  As shown in FIG. 7B, the dilution unit 5 is opened and discharged by pushing up the center of the opening button 6 joined to the cover substrate 4 from below so that the pin 8 is stuck on the surface of the dilution unit 5. The aluminum seal 10 is broken and the dilution unit 5 is opened. Further, when the analysis device 1 is rotated in a state where the dilution unit 5 is opened, the diluted solution in the dilution unit 5 becomes a space formed between the opening hole 7 and the discharge hole 9 (the base substrate 3 and the cover substrate). 4 and a space formed between the cover substrate 4 and the unsealing button 6) and discharged to the holding cavity 14 as the second holding portion.

FIG. 8A is an enlarged perspective view of the vicinity of the injection port of the analysis device 1, and FIG. 8B is a front view thereof. FIG. 9 is a plan view of a joint surface of the base substrate 3 shown in FIG. 2 with the cover substrate 4.
Since the analysis device 1 attaches the sample solution to the injection port 11 so that the sample solution can be sucked by the capillary force of the capillary cavity 17 formed inside, the blood can be directly collected from the fingertip or the like. it can. Here, since the injection port 11 has a shape that protrudes in the direction of the axial center 102 from one side surface of the analysis device 1 main body, a finger or the like comes into contact with a place other than the injection port 11, and blood adheres to it. It has an effect of preventing blood adhering at the time of analysis from being scattered outside.

  Also, cavities 12 and 13 having a cross-sectional dimension in the thickness direction larger than that of the capillary cavity 17 and communicating with the atmosphere are provided on the side surfaces of the capillary cavity 17. By providing the cavities 12 and 13, the sample liquid flowing in the capillary cavity 17 is filled not as a capillary flow in which the side portion precedes, but as a capillary flow in which the central portion precedes, so that the sample liquid flows a plurality of times. Even in the case where the sample liquid is divided and filled, the sample liquid held in the capillary cavity 17 and the central part of the sample liquid collected later flow so as to come into contact with each other first, and the air in the capillary cavity 17 is allowed to flow into the side cavity. 12 and 13 are filled while being discharged. For this reason, even when the amount of the sample liquid to be attached to the injection port 11 is insufficient during collection or when a fingertip or the like is separated from the injection port 11 during collection, the collection into the capillary cavity 17 is completed. It can be collected any number of times. Here, the cross-sectional dimension of the capillary cavity 17 in the thickness direction is 50 to 300 μm, and the cross-sectional dimension of the cavities 12 and 13 in the thickness direction is 1000 to 3000 μm. However, the capillary cavity 17 can collect the sample liquid by capillary force. The dimensions and cavities 12 and 13 are not particularly limited as long as the sample liquid is not transferred by capillary force.

  In addition, the enlarged view of the cross section of each position of AA-AA, BB, CC, DD, and EE shown in FIG. 11 is shown to (a)-(e) of FIG. 20a, 20b1, 20b2, 20c, 20d, 20e, 20f, 20g, 20h and 20i are air holes. Moreover, the position where the hydrophilic treatment is performed is shown by hatching in FIG.

Next, the microchannel configuration of the analytical device and the solution transfer process in Embodiment 1 of the present invention will be described in detail.
FIG. 14 is a block diagram showing the structure of the analytical device 1. The analytical device 1 includes a sample liquid collecting unit 150 for collecting a sample liquid and a dilution for holding a diluent for diluting the sample liquid. A liquid holding unit 151, a separation unit 152 that holds the sample liquid transferred from the sample liquid collecting unit 150, and after collecting the sample liquid containing a predetermined amount of the solid component after centrifugation into a solution component and a solid component; A diluent measuring unit 153 for measuring the diluent transferred from the diluent holding unit 151, a sample solution transferred from the separation unit 152, and a diluent transferred from the diluent measuring unit 153 are held and mixed therein. Thereafter, a mixing unit 154 that measures the diluted solution to an amount necessary for analysis, and a measuring unit 155 that reacts and measures the diluted solution transferred from the mixing unit 154 with the analysis reagent are formed.

  As shown in FIG. 9, the sample liquid collecting unit 150 includes an inlet 11 for collecting a sample liquid, a capillary cavity 17 for collecting a sample liquid through the inlet 11 with a capillary force and holding a predetermined amount, and a capillary tube when collecting the sample liquid. The cavities 12 and 13 are configured to discharge air in the cavities 17.

As shown in FIG. 9, the diluent holding unit 151 holds the diluent in the dilution unit 5, and the diluent is developed by the opening operation described with reference to FIG.
As shown in FIG. 9, the separation unit 152 is formed so as to communicate with the capillary cavity 17 through the cavity 12 on the lower side of the sample liquid collecting unit 150 and transfers the sample liquid transferred from the capillary cavity 17 by centrifugal force. A separation cavity 18 that holds and separates the sample liquid into a solution component and a solid component by centrifugal force, and one of the solid components that is formed between the separation cavity 18 and the diluent measurement unit 153 and separated by the separation cavity 18. A measuring channel 23 serving as a first holding unit that is transferred and held, a connecting channel 21 that connects the measuring channel 23 and the separation cavity 18 to transfer the sample liquid in the separation cavity 18, and a separation A solution component of the sample solution formed between the cavity 18 and the diluent metering unit 153 and separated in the connection channel 21 is preferentially held, and only the solid component is supplied to the metering channel 23. An overflow channel 22 to be sent, a capillary cavity 19 formed in the separation cavity 18 so as to prevent the solution components in the separated separation cavity 18 from being transferred to the metering channel 23, and a separation cavity 18 Via the connection channel 24, a connection channel 24 that is formed on the opposite side of the measurement channel 23 at the boundary and discharges the sample solution that is not required for analysis in the separation cavity 18, the connection channel 21, and the overflow channel 22 It is composed of overflow cavities 25 and 26 for holding unnecessary sample liquid to be transferred. As shown in FIG. 12 (e) showing an enlarged view of the cross section at the EE position shown in FIG. 11, the overflow cavities 25 and 26 are in communication with each other, and the capillary tube at the outer peripheral portion of the rotation when centrifugal force is generated. The overflow cavity 26 as an area has a cross-sectional dimension (g1) in the thickness direction that is smaller than a cross-sectional dimension (g2) in the thickness direction of the overflow cavity 25 in the inner peripheral portion, and has a size that allows capillary force to act. Yes.

  Here, the cross-sectional dimension (g2) in the thickness direction of the connecting channel 21, overflow channel 22, metering channel 23, connecting channel 24, capillary cavity 19, and overflow cavity 26 is configured to be 50 to 300 μm. However, there is no particular limitation as long as the sample liquid can be transferred by capillary force. Moreover, although the cross-sectional dimension (g1) of the thickness direction of the separation cavity 18 and the overflow cavity 25 is comprised by 1000-3000 micrometers, it can adjust according to the quantity of a required sample liquid.

  As shown in FIG. 9, the diluent measuring unit 153 is formed on the lower side of the diluent holding unit 151 and holds a predetermined amount of diluent transferred from the dilution unit 5 by centrifugal force. A connection channel 15 formed between the cavity 14 and the separation unit 152 to transfer the diluent measured in the holding cavity 14 to the mixing unit 154, and on the opposite side of the connection channel 15 with the holding cavity 14 as a boundary. An overflow channel 16 for overflowing out of the holding cavity 14 when the dilution liquid formed and transferred to the holding cavity 14 exceeds a predetermined amount, and a liquid level height held in the holding cavity 14 are defined. An overflow cavity 27 in which the diluent is overflowed via the overflow channel 16, and a measurement spot 29 that holds the overflowed diluent and is used for reference measurement of the optical measuring means 109. Measured diluent held in the spot 29 is reverse flow composed of the threshold 28 for preventing the outflow of the different areas. The position of the threshold 28 is formed at an inner peripheral position with respect to the liquid level of the sample held at the measurement spot 29.

FIG. 10B shows a GG sectional view of the sill 28 portion. The cross-sectional dimension (g3) in the thickness direction is limited to the size at which the capillary force acts.
Here, the cross-sectional dimension in the thickness direction of the connecting channel 15 and the overflow channel 16 is 50 to 300 μm, and the cross-sectional dimension (g3) in the thickness direction of the sill 28 is also 50 to 300 μm. Any dimension can be used as long as it can restrict the passage of.

  The holding cavity 14, the overflow cavity 27, and the measurement spot 29 have a cross-sectional dimension in the thickness direction of 1000 to 3000 μm. Conditions for measuring the required amount of sample liquid and absorbance (optical path length, measurement wavelength, etc.) ) Can be adjusted.

  As shown in FIG. 9, the mixing unit 154 is formed so as to communicate with the measurement channel 23 and the connection channel 15 on the lower side of the separation unit 152 and the diluent measurement unit 153, and is transferred from the measurement channel 23. An operation cavity 30 serving as a third holding unit that holds the sample liquid and the diluent transferred from the holding cavity 14 and mixes the sample liquid and the diluted solution is supplied from an air hole 20c provided in the operation cavity 30 during mixing. The rib 31 formed so as to prevent the liquid from flowing out and the diluted solution held in the operation cavity 30 are formed inside the liquid level with respect to the direction of the axis 102 and mixed to be transferred from the operation cavity 30. A holding cavity 32 as a fourth holding part for holding the diluted solution, and a dilution formed on the lower side of the holding cavity 32 and transferred from the holding cavity 32 by centrifugal force A holding cavity 35 for holding a predetermined amount of liquid, and a capillary section that is formed between the holding cavity 32 and the overflow cavity 27 and suppresses the dilute solution transferred to the holding cavity 32 from flowing out to the overflow cavity 27. 33, a connection channel 34 that suppresses the dilute solution formed between the holding cavity 32 and the holding cavity 35 and transferred to the holding cavity 32 from flowing out to the holding cavity 35, and the holding cavity 35 and the holding cavity 35. Between the holding cavity 35 and the overflow cavity 27, and a connecting flow path 37 that is formed between the measuring cavity 155 and the measuring cavity 155 that is located on the lower side and transfers the diluted solution measured in the holding cavity 35 to the measuring cavity 155. For overflowing the holding cavity 35 when the diluted solution formed and transferred to the holding cavity 35 exceeds a predetermined amount Constituted by the Nagareryuro 36.

  Here, the capillary section 33, the connecting channel 34, the overflow channel 36, and the connecting channel 37 have a cross-sectional dimension in the thickness direction of 50 to 300 μm. Absent. Moreover, although the cross-sectional dimension of the holding | maintenance cavity 32 and the holding | maintenance cavity 35 is 1000-3000 micrometers in thickness direction, it can adjust according to the quantity of a required dilution solution.

  As shown in FIG. 9, the measuring unit 155 is formed to communicate with the holding cavity 35 via the connection channel 37 on the lower side of the mixing unit 154 and is connected from the holding cavity 35 with the reagent carried inside. A measurement spot 38 for reacting and holding the diluted solution transferred through the flow path 37 to perform the first measurement, and a first spot held in the measurement spot 38 which is an operation cavity when viewed from the measurement spot 43. A capillary cavity 39 that is formed on the inner side of the liquid surface height with respect to the direction of the axial center 102 of the reaction liquid, and serves as a receiving cavity for collecting the first reaction liquid in the measurement spot 38 after the measurement of the first reaction liquid, and the measurement spot 38 A capillary cavity 40 for stabilizing the amount of the first reaction liquid formed between the first and second capillary cavities 39 and returning to the measurement spot 38; and the capillary cavity 3 A connection channel 41 that suppresses the first reaction liquid that is formed on the lower side of the sample and collected in the capillary cavity 39 from flowing out to the measurement spot 43, and a connection portion between the capillary cavity 39 and the capillary cavity 40; A rib 42 that breaks the first reaction solution in the capillary cavity 39 by centrifugal force and returns a predetermined amount of the diluted solution to the measurement spot 38, and communicates with the capillary cavity 39 via the connection channel 41 on the lower side of the capillary cavity 39. A measurement spot 43 for reacting and holding the reagent formed and carried inside and the first reaction liquid transferred from the capillary cavity 39 via the connection channel 41 and performing the second measurement; The inner surface of the second reaction liquid held in the measurement spot 43, which is the operation cavity as viewed from the measurement spot 46, is higher than the liquid level with respect to the axial center 102 direction. And a capillary cavity 44 serving as a receiving cavity for collecting the second reaction liquid in the measurement spot 43 after measurement of the second reaction liquid, and the measurement spot 43 formed between the measurement spot 43 and the capillary cavity 44. The capillary cavity 64 as a third connecting portion for stabilizing the amount of the second reaction liquid returning to the step, and the second reaction liquid 62 formed in the lower side of the capillary cavity 44 and collected in the capillary cavity 44 are measured spots. A connection channel 45 that suppresses outflow to 46, and a reagent that is formed on the lower side of the capillary cavity 44 so as to communicate with the capillary cavity 44 via the connection channel 45, and the capillary cavity 44. And a measurement spot 46 for reacting and holding the second reaction liquid transferred through the connection channel 45 and performing the third measurement. Is done.

  Here, the capillary cavity 39, the capillary cavity 40, the connecting channel 41, the capillary cavity 44, and the connecting channel 45 are configured to have a cross-sectional dimension in the thickness direction of 50 to 500 μm. There is no limit. Moreover, although the cross-sectional dimension of the thickness direction of the measurement spot 38, the measurement spot 43, and the measurement spot 46 is 1000-3000 micrometers, the conditions (optical path length, measurement wavelength, sample which measure the quantity and the light absorbency of required dilution solution) It can be adjusted according to the reaction concentration of the solution, the type of reagent, and the like.

Next, the sample solution analysis step of the analysis device 1 will be described in detail by taking the concentration measurement of hemoglobin and HbA1c contained in blood cells in blood as an example.
15 to 22 show the analysis device 1 set on the rotor 103 as viewed from the surface side of the rotor 103, and the rotation direction C1 with respect to the axis 102 is the left rotation in FIG. A rotation direction C2 with respect to the axis 102 indicates a right rotation in FIG.

FIG. 15 shows an injection process and a separation / metering process of the analytical device according to the first embodiment of the present invention.
− Step 1 −
In FIG. 15A, blood as a sample solution is collected from the punctured fingertip or the like through the inlet 11 of the analytical device 1 until the inside of the capillary cavity 17 is filled by the capillary force of the capillary cavity 17. The Here, the sample liquid, for example, about 10 μL of blood can be measured by the volume determined by the gap and the facing area of the capillary cavity 17, but the shape dimension of the capillary cavity 17 is defined according to the amount necessary for the analysis and collected. You can adjust the capacity.

The analysis device 1 that has collected a necessary amount of blood is mounted on the rotor 103 of the analysis apparatus 100, and an unsealing operation is performed by the unsealing means of the dilution unit 5.
− Step 2, Step 3 −
After the opening of the dilution unit 5 is completed, the rotor 103 is rotated (right rotation indicated by C2 and 3000 rpm) so that the blood and the diluent in the capillary cavity 17 are separated from the separation cavity 18 as shown in FIG. The diluted solution in the dilution unit 5 is transferred to the holding cavity 14. Here, when diluting the blood and taking out the measurement component in the blood cell, in order to reduce the variation in dilution due to the influence of the hematocrit value (the ratio of the blood cell component contained in the blood) having individual differences, the separation cavity 18 The blood transported to is separated into a plasma component and a blood cell component by centrifugal force, and high-hematocrit blood on the outer periphery is collected and diluted to reduce variation in dilution.

  In addition, the diluted liquid that has been transferred to the holding cavity 14 during the rotation and has exceeded the specified amount flows into the measurement spot 29 through the overflow channel 16, the overflow cavity 27, and the threshold 28, and is held. .

FIG. 16 shows the centrifugal separation operation in the separation cavity 18 having the capillary cavity 19 and the transfer flow to the operation cavity 30 via the measuring flow path 23.
The capillary cavity 19 of this embodiment is formed in contact with the left side surface in the separation cavity 18, but the same can be said if it is formed in contact with the right side surface in the separation cavity 18. One end of the capillary cavity 19 is formed from the liquid surface of the sample liquid 57 to the outer peripheral position so as to be immersed in the sample liquid held in the separation cavity 18 as shown in FIG.

  The connection channel 24 has a siphon structure that communicates with the outermost peripheral position of the connection channel 21 and bends at an inner peripheral position with respect to the liquid surface of the sample liquid held in the separation cavity 18. The overflow cavity 26 is positioned on the outer periphery of the outermost peripheral position of the connection channel 21 and communicates with the separation cavity 18 via the connection channel 24.

  As shown in FIG. 16 (a), blood 57 collected at the bottom of the separation cavity 18 is separated into a plasma component 57a and a blood cell component 57b by centrifugal force as shown in FIG. 16 (b). When the rotation stops and the centrifugal force disappears, as shown in FIG. 16C, the plasma component 57a in the separation cavity 18 is capillary-transferred to the capillary cavity 19, and the plasma component 57a and the blood cell component 57b in the connection channel 21 are Then, it is capillary-transferred toward the overflow channel 22 connected to the cavity 58 having the air hole 20a communicating with the atmosphere side. The plasma component 57a and the blood cell component 57b in the connection channel 24 are capillary-transferred toward the overflow cavity 26 having the air hole 20d communicating with the atmosphere side. Here, the end of the measurement flow path 23 is connected to the connection flow path 21 at the position where the blood cell component 57b has reached, and as shown in FIG. Only the blood cell component 57b is transferred by the capillary force of the measuring channel 23.

  In this embodiment, since the capillary cavity 19 is formed in the separation cavity 18, most of the plasma component 57 a remaining in the separation cavity 18 can be held by the capillary cavity 19, and a necessary amount of the measurement channel 23 is provided in the measurement channel 23. Only the blood cell component 57b is useful for capillary transfer.

− Step 4 −
After stopping the rotation of the rotor 103 (right rotation indicated by C2 · 3000 rpm) and resting, the rotor 103 is rotated (right rotation indicated by C2 · 2000 rpm) from FIG. The required amount of the blood cell component 57b and the diluted solution of the holding cavity 14 flow into the operation cavity 30 and are mixed and diluted, and the excess blood cell component 57b enters the overflow cavity 26 as shown in FIG. Retained. The optical measurement unit 109 performs reference measurement in which the diluted solution of the measurement spot 29 of the analysis device 1 is read at a timing that is interposed between the laser light source 105 and the photodetector 106. At this time, the wavelength of the laser light source 105 is switched between 535 nm and 625 nm for reference measurement.

− Step 5 −
Next, the analysis device 1 is set to a position near 60 ° shown in FIG. 18A, and the dilution liquid is controlled by controlling the motor 104 at a frequency of 1000 rpm so as to give the analysis device 1 a swing of about ± 1 mm. Stir.

-Step 6-
Thereafter, the analysis device 1 is set at a position near 180 ° shown in FIG. 18B, and the motor 104 is controlled at a frequency of 1000 rpm so as to give the analysis device 1 a swing of about ± 1 mm. Stir.

  Here, the operation cavity 30 and the holding cavity 32 are communicated with each other by a connecting portion 59, and the position of the connecting portion 59 at the time of stirring is held by the operating cavity 30 with respect to the rotation axis 102 that generates centrifugal force. Since the liquid is positioned on the inner peripheral side of the liquid surface of the diluted solution, the diluted liquid during the stirring and mixing does not flow out to the holding cavity 32.

-Step 7-
Next, the analysis device 1 is set at a position near 300 ° shown in FIG. 19A, and the motor 104 is controlled at a frequency of 1000 rpm so as to give the analysis device 1 a swing of about ± 1 mm. The diluted blood cell component 57 b (diluted solution) in the cavity 30 is oscillated and transferred to the holding cavity 32 via the connecting portion 59.

  Here, the diluted solution held in the operation cavity 30 is held by the surface tension acting on the wall surface of the operation cavity 30 even if the analysis device 1 is moved to a position near 300 ° shown in FIG. (Because the surface tension is larger than the gravity acting on the diluted solution), the analytical device 1 is swung to give the diluted solution an inertial force, thereby breaking the surface tension acting on the wall surface of the operation cavity 30 to the diluted solution. The diluted solution can be transferred to the holding cavity 32 by the working inertia force and gravity.

− Step 8 −
Next, the analysis device 1 is defined in the holding cavity 35 from the holding cavity 32 through the connection channel 34 as shown in FIG. 19B by rotating the rotor 103 (right rotation indicated by C2 · 2000 rpm). An amount of diluted solution is transferred. A portion exceeding the predetermined amount of the diluted solution transferred to the holding cavity 35 overflows to the overflow cavity 27 via the overflow channel 36, and only the prescribed amount of the diluted solution 60 is held in the holding cavity 35.

-Step 9, Step 10-
By stopping the rotation of the rotor 103 (right rotation indicated by C2 and 2000 rpm) and making it stand still, as shown in FIG. 20A, the diluted solution in the holding cavity 35 is primed into the connection channel 37, and further FIG. By rotating the rotor 103 from (a) (left rotation indicated by C1 · 2000 rpm), a prescribed amount of the diluted solution held in the holding cavity 35 is transferred to the measurement spot 38 via the connection channel 37 and measured. The denaturing reagent previously supported on the spot 38 is dissolved.

− Step 11 −
Thereafter, at a position near 180 ° shown in FIG. 20B, the motor 104 is controlled at a frequency of 1000 rpm so as to give the analysis device 1 a swing of about ± 1 mm, and the measurement spot 38 of the analysis device 1 is measured. The first reaction liquid 61 is stirred.

  Here, the measurement spot 38 and the measurement spot 43 side communicate with each other via the capillary cavity 40 and the capillary cavity 39. Here, the capillary cavity 40 acts as a second connecting portion, and the position of this capillary cavity 40 during stirring is the liquid of the diluted solution held in the measurement spot 38 with respect to the rotation axis 102 that generates centrifugal force. Since it is located on the inner peripheral side from the surface, the diluted solution being stirred and mixed does not flow out into the capillary cavity 39 on the measurement spot 43 side.

− Step 12, Step 13 −
Next, after the analysis device 1 is stopped and the first reaction solution 61 is denatured, the rotor 103 is rotated (left rotation indicated by C1 · 1500 rpm) to perform the first measurement.

  In the first measurement, the first reaction liquid 61 obtained by the denaturation reaction of the measurement spot 38 of the analytical device 1 is interposed between the laser light source 105 and the photodetector 106 in the light emission state where the wavelength of the laser light source 105 is switched to 535 nm. Read at the timing. The calculation unit 110 processes the measurement value obtained by the first measurement based on a reference value obtained by reading the measurement spot 29 in advance with the wavelength of the laser light source 105 set to 535 nm and displays the denatured hemoglobin concentration as a display unit 111. To display.

  Here, “denaturation” means that a specific part is taken out (exposed) from the structure of the protein, and the antigen-antibody reaction described later is a part exposed from the structure of the protein. This is done with a latex reagent that reacts specifically with “denatured sites”.

− Step 14 −
Next, by controlling the motor 104 at a frequency of 1500 rpm so that the analyzing device 1 is placed at a position near 60 ° shown in FIG. The first reaction liquid 61 held in the measurement spot 38 is capillary-transferred to the capillary cavity 39, and a predetermined amount of the first reaction liquid 61 is held in the capillary cavity 39.

− Step 15 −
Next, the first reaction liquid 61 flows into the measurement spot 43 from the capillary cavity 39 through the connection channel 41 by rotating the rotor 103 (left rotation indicated by C1 and 2000 rpm), and is previously supported on the measurement spot 43. Dissolve the latex reagent.

− Step 16 −
Thereafter, at a position near 180 ° shown in FIG. 21B, the motor 104 is controlled at a frequency of 1000 rpm so as to give the analysis device 1 a swing of about ± 1 mm, and the measurement spot 43 of the analysis device 1 is measured. The second reaction liquid 62 is stirred.

  Here, the measurement spot 43 and the measurement spot 46 are communicated with each other via a capillary cavity 44, and the position of the capillary cavity 64 that connects the measurement spot 43 and the capillary cavity 44 during stirring is determined by centrifugal force. Since the rotation axis 102 that generates rotation is positioned on the inner peripheral side of the liquid surface of the diluted solution held in the measurement spot 43, the diluted solution being stirred and mixed flows out into the capillary cavity 44 on the measurement spot 46 side. There is nothing.

− Step 17, Step 18 −
Next, after the analysis device 1 is stopped and the second reaction liquid 62 is subjected to an antigen-antibody reaction, the rotor 103 is rotated (left rotation indicated by C1 · 1500 rpm) to perform the second measurement.

  In the second measurement, in a light emission state in which the wavelength of the laser light source 105 is switched to 625 nm, the second reaction liquid 62 that has undergone antigen-antibody reaction at the measurement spot 43 of the analytical device 1 is interposed between the laser light source 105 and the photodetector 106. Read at the timing.

− Step 19 −
Next, the analysis device 1 is set to a position near 60 ° shown in FIG. 22A, and the motor 104 is controlled at a frequency of 1500 rpm so as to give the analysis device 1 a swing of about ± 1 mm. The reaction liquid 62 is capillary transferred to the capillary cavity 44.

− Step 20 −
After that, by rotating the rotor 103 (left rotation indicated by C1 and 2000 rpm), a predetermined amount of the second reaction liquid 62 held in the capillary cavity 44 flows into the measurement spot 46 via the connection channel 45, The agglutinating reagent carried on the measurement spot 46 is dissolved.

− Step 21 −
Thereafter, at a position near 180 ° shown in FIG. 22B, the motor 104 is controlled at a frequency of 1000 rpm so as to give the analysis device 1 a swing of about ± 1 mm, and the measurement spot 46 of the analysis device 1 is measured. The third reaction solution 63 is stirred.

− Step 22, Step 23 −
Next, after the analysis device 1 is stopped and the third reaction solution 63 is agglomerated, the rotor 103 is rotated (left rotation indicated by C1 and 1500 rpm) to perform the third measurement.

  The third measurement is a timing at which the third reaction solution 63 in which the measurement spot 46 of the analytical device 1 agglutinates is interposed between the laser light source 105 and the photodetector 106 in a light emission state in which the wavelength of the laser light source 105 is switched to 625 nm. Read with. The calculation unit 110 processes the measurement values obtained by the second measurement and the third measurement, and digitizes the HbA1c concentration by processing the measurement spot 29 based on a reference value read in advance with the wavelength of the laser light source 105 set to 625 nm. The HbA1c% value calculated based on the modified hemoglobin concentration is displayed on the display unit 111.

In the operation cavity 30 and the holding cavity 32, the holding cavity 32 is a receiving cavity.
In the measurement spot 38 and the capillary cavity 39, the measurement spot 38 is an operation cavity, and the capillary cavity 39 is a receiving cavity.

In the measurement spot 43 and the capillary cavity 44, the measurement spot 43 is an operation cavity, and the capillary cavity 44 is a receiving cavity.
In the above embodiment, the access means for reading the reactants at the measurement spots 38, 43, and 46 of the analytical device 1 optically accesses and reads the reaction solution as the reactant at the measurement spots 38, 43, and 46. However, at least one of the measurement spots 38, 43, and 46 is subjected to electrostatic coupling or electromagnetic coupling to the non-contact electrical access for reading, or the measurement spots 38, 43, and 46 are read. An electrode may be provided in at least one of the measurement spots, and the reaction product of the measurement spot may be electrically accessed via the electrode for reading. The reactant is the same whether it is a liquid, a solid, or a semi-solid such as a jelly or gel.

  Because of this configuration, excess blood remains in the areas of the overflow cavities 25 and 26 after the measurement is completed, but by forming the volume of the capillary area of the overflow cavity 26 to be larger than the excess blood, Since excess blood is retained and trapped by the capillary force of the overflow cavity 26, it is prevented from flowing out of the analysis device 1 from the air hole 20d formed at the inner peripheral position of the overflow cavity 26. This can reduce the risk of the operator causing an infection accident.

  In addition, a sample obtained by diluting a blood cell component with a diluent remains in the area of the measurement spot 29 after the measurement is completed. However, since a threshold 28 is formed to limit the flow path to a size where the capillary force acts, the overflow from the measurement spot 29 occurs. It is possible to prevent the blood cell component diluted from flowing out of the analysis device 1 from the air hole 20f on the inner peripheral side of the measurement spot 29 without flowing out into the cavity 27, and the risk of causing an infection accident for the operator. Can be reduced.

  In the above embodiment, the overflow cavity 26 is configured as a capillary area where the capillary force acts on the side of the overflow cavities 25 and 26 that hold excess blood in order to suppress blood from flowing out. However, the cross-sectional dimensions in the thickness direction of the overflow cavity 25 and the overflow cavity 26 are both formed so as not to act on the capillary force, and the boundary between the overflow cavity 25 and the overflow cavity 26 is shown in FIG. Thus, a threshold 90 similar to the threshold 28 formed at the boundary between the measurement spot 29 and the overflow cavity 27 can be provided, and the gap of the flow path can be limited to g3 where the capillary force acts.

  In the embodiment described above, a sill 28 is formed between the measurement spot 29 holding the diluted blood cell component and the overflow cavity 27 to prevent the sample from flowing out. As shown in FIG. 24, the cross-sectional dimension g4 in the thickness direction of the measurement spot 29 is smaller than the cross-sectional dimension g5 in the thickness direction of the overflow cavity 27 and can be configured as a capillary area where a capillary force acts. .

  In the above description, the case of the measurement spot 29 has been described as an example. However, the same applies to the case of the measurement spot 46, and the connection channel 45 provided on the inner peripheral side of the measurement spot 29 is connected to the measurement spot 29. By configuring the gap in which the capillary force acts so that the sample liquid does not flow out into the capillary cavity 44, it is possible to suppress the sample liquid from flowing out from the air holes 20i, thereby protecting the operator from danger.

  INDUSTRIAL APPLICABILITY The present invention can contribute to improving the safety of an analytical device and an analytical apparatus using the analytical device.

The principal part perspective view of the state which set the device for analysis in the analyzer of the embodiment of the present invention Exploded perspective view of the analysis device of the same embodiment External view of the analyzer of the same embodiment Configuration diagram of the analyzer of the same embodiment Sectional view of the analyzer of the same embodiment The figure which shows the rotation stop position of the device for analysis in the embodiment Plan view and sectional view of dilution unit opening part of analysis device in same embodiment Enlarged perspective view and front view of the vicinity of the inlet of the analytical device in the same embodiment A plan view showing a microchannel configuration of the analysis device according to the embodiment The principal part enlarged view and GG sectional drawing in FIG. The top view which shows the cross-sectional position of the device for analysis in the embodiment Sectional drawing of each part of the analytical device in the same embodiment The top view which shows the hydrophilic treatment position of the device for analysis in the embodiment Configuration diagram of analysis device in the same embodiment Explanatory drawing of the injection process and separation / metering process of the analytical device in the same embodiment Action explanatory view of the separation cavity 18 having the capillary cavity 19 and the branching portion of the overflow channel 22 and the connection channel 21 in the same embodiment Explanatory drawing of the weighing process and mixing process of the analytical device in the same embodiment Explanatory drawing of the mixing process of the analytical device in the same embodiment Explanatory drawing of the dilute solution transfer process and the metering process of the analytical device in the same embodiment Explanatory drawing of the transfer process and reagent reaction / measurement process of the analytical device in the same embodiment Explanatory drawing of the transfer process and reagent reaction / measurement process of the analytical device in the same embodiment Explanatory drawing of the transfer process and reagent reaction / measurement process of the analytical device in the same embodiment Sectional view of another embodiment of overflow cavities 25, 26 Sectional view of another embodiment of the measurement spot 29 The top view of the principal part of the device for analysis of patent documents 1

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Analytical device 2 Protective cap 3 Base board 4 Cover board 5 Dilution unit 6 Opening button 7 Opening hole 8 Pin 9 Discharge hole 10 Aluminum seal 11 Inlet 12 and 13 Cavity 14 Holding cavity (2nd holding part)
DESCRIPTION OF SYMBOLS 15 Connection flow path 16 Overflow flow path 17 Capillary cavity 18 Separation cavity 19 Capillary cavity 20a, 20b1, 20b2, 20c-20i Air hole 21, 24 Connection flow path 22 Overflow flow path 23 Metering flow path (1st holding | maintenance part) )
g1 Cross-sectional dimension in the thickness direction of the connecting flow path 21 g2 Cross-sectional dimension in the thickness direction of the overflow flow path 22 Width w2 in a direction intersecting the flow direction of the connecting flow path 21 Direction crossing the flow direction of the overflow flow path 22 Width 25, 27 Overflow cavity 26 Overflow cavity (capillary area)
28 Sill 29 Measurement spot 30 Operating cavity (third holding part)
31 Rib 32 Holding cavity (fourth holding part, receiving cavity)
33 Capillary part 34 Connection channel 35 Holding cavity 36 Overflow channel 37 Connection channel 38 Measurement spot (operation cavity)
39 Capillary cavity (receiving cavity)
40 Capillary cavity (second connecting part)
41 Connection channel (connection part)
42 Rib 43 Measurement spot (operation cavity)
44 Capillary cavity (receiving cavity)
45 connection channel 46 measurement spot 56 hydrophilic treatment position 57 blood 57a plasma component 57b blood cell component 58 cavity 59 connection part 61 first reaction liquid 62 second reaction liquid 63 third reaction liquid 64 capillary cavity (third connection part)
DESCRIPTION OF SYMBOLS 100 Analyzer 101 Cover 102 Axis 103 Rotor 104 Motor 105 Laser light source 106 Photo detector 107 Rotation drive means 108 Control means 109 Optical measurement means 110 Calculation part 111 Display part 150 Sample liquid collection part 151 Diluent holding part 152 Separation part 153 Diluent Measuring unit 154 Mixing unit 155 Measuring unit C1 Left rotation C2 Right rotation θ Tilt angle

Claims (5)

For analysis used for reading to access the sample at the measurement spot, having a first microchannel structure that transfers the sample liquid toward the measurement spot by centrifugal force generated when rotating around the center of rotation . A device,
Providing another second microchannel structure for holding a sample liquid that has become surplus during transfer of the first microchannel structure;
The second microchannel structure is:
A first overflow cavity connected to a plurality of overflow channels through which surplus sample liquid is transferred at different timings ;
A second overflow cavity located farther from the center of rotation than the first overflow cavity;
The boundary of the second overflow cavity between said first overflow cavity, in a direction transverse to the direction of the centrifugal force, the thickness of the flow path connecting the second overflow cavity between said first overflow cavity Have a threshold to restrict,
The thickness of the flow path is
The sample liquid can be transferred from the first overflow cavity to the second overflow cavity by the centrifugal force, and in a state where the centrifugal force does not act , the sample is between the first and second overflow cavities by capillary force. An analytical device that is sized to prevent liquid from being transferred. For analysis used for reading to access the sample at the measurement spot, having a first microchannel structure that transfers the sample liquid toward the measurement spot by centrifugal force generated when rotating around the center of rotation . A device,
Providing another third microchannel structure for holding a sample liquid that becomes surplus during transfer of the first microchannel structure;
The third microchannel structure is:
A third overflow cavity fluidly connected to each other, and a fourth overflow cavity formed on the outer peripheral side of the third overflow cavity with respect to the rotation center and communicated with the third overflow cavity. 3 The overflow cavity has an air hole communicating with the atmosphere side,
The analytical device in which the cross-sectional dimension in the thickness direction of the fourth overflow cavity is smaller than the cross-sectional dimension in the thickness direction of the third overflow cavity and is set to a gap where capillary force acts.   The analysis device according to claim 1, wherein an air hole communicating with the atmosphere side is provided in an area where the capillary force does not act on the inner peripheral side of the sill. The analytical device according to claim 1 or 2, wherein a sample liquid is collected ;
Rotational drive means for rotating the analytical device about an axis;
Analyzing means for accessing and analyzing a sample in the analyzing device based on the solution transferred by the rotation driving means;
An analyzer configured to transfer a sample solution to the measurement spot and the overflow cavity by rotation of the rotation driving means. An analysis method using the analysis device according to claim 1 or 2,
Rotating the analytical device to transfer at least a part of the sample liquid spotted on the analytical device to a measurement spot and transferring the other sample liquid to the overflow cavity;
Mixing the transferred sample solution and reagent;
An analysis method comprising: rotating the analysis device to access a sample of the measurement spot at a timing when the measurement spot is interposed at a reading position.

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