JP2009092391A - Analysis device, and analysis apparatus and analysis method using the same - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an analysis device capable of accurately taking out a specified amount of a solid component in a sample and transferring it to an analysis step. <P>SOLUTION: The analysis device includes: a separation cavity 18 for separating a sample liquid into a solution component and the solid component by using a centrifugal force; a weighing channel 23 for holding a portion of the solid component which has been separated and then transferred; an overflow channel 22 provided between the weighing channel 23 and the separation cavity 18, and connected to a coupling channel 21 for transporting the sample liquid from the separation cavity 18; and a capillary cavity 19 formed inside the separation cavity 18 for temporarily holding the solution component (blood plasma) separated in the separation cavity 18. The blood plasma component 57a remaining in the separation cavity 18 is trapped by the capillary cavity 19. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to an analytical device used for analyzing a liquid collected from a living organism, an analytical apparatus and an analytical method using the analytical device, and more specifically, a liquid solid separated in the analytical device. More particularly, the present invention relates to a technique for collecting blood cell components in blood.

  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. Analytical devices can control fluids using a rotating device, and use centrifugal force to measure solutions, separate solid components, transfer and distribute separated fluids, mix solutions and reagents, etc. Therefore, various biochemical analyzes can be performed.

As shown in FIG. 24A, the analysis device 501 that transfers a solution using centrifugal force centrifuges blood held in the separation chamber 70 by rotation of the analysis device 501. After that, the blood flow component is connected to the measuring flow path 73 from the lower side of the separation chamber 70 via the connection flow path 71 and the overflow flow path 72, and the blood cell component is transferred to the capillary. After the plasma component remaining in the connection channel 71 is trapped in the overflow channel 12 by centrifugation, only the blood cell component can be transferred to the measurement channel 73 to collect a specified amount of blood cell component. The plasma component trapped in the overflow channel 72 is collected in the overflow chamber 74.
JP 2007-78676 A

  In the conventional configuration, when the opening area of the overflow channel 72 is w3 and the opening area of the metering channel 73 is w4 as shown in the enlarged view of FIG. 24B, w3> w4 is set. Thus, the plasma component is preferentially transferred and trapped toward the overflow channel 72 having a large opening area, and the blood cell component is transferred to the measuring channel 73 to collect a specified amount of blood cell component.

  However, the plasma component and the blood cell component that are centrifuged and held in the separation chamber 70 have a lower viscosity than the blood cell component, and the plasma component has a lower viscosity than the blood cell component. In terms of ease of transfer, the plasma component is more easily transferred than the blood cell component.

  Therefore, the plasma component remaining in the separation chamber 70 currently flows into the connection channel 71 from the lower side of the separation chamber 70, and the contamination of plasma cannot be completely suppressed, and the dilution rate is It is a variability factor.

  The present invention solves the above-described conventional problems, and an analytical device that can accurately extract a specified amount of blood cell components in a sample and transfer them to an analysis step regardless of the difference in viscosity between plasma components and blood cell components, An object is to provide an analysis apparatus and an analysis method using the same.

  The analytical device according to claim 1 of the present invention is an analytical device that has a microchannel structure for transferring a sample solution toward a measurement spot by centrifugal force, and is used for reading a reactant in the measurement spot. A separation cavity for separating the sample liquid into a solution component and a solid component using the centrifugal force, and a measuring channel for transferring a part of the solid component separated in the separation cavity and holding the separation cavity. An overflow channel provided between the metering channel and the separation cavity and connected to a connection channel for transferring the sample liquid in the separation cavity; and temporarily separating the separated solution components in the separation cavity And a capillary cavity formed inside the separation cavity so as to be held in the chamber.

  The analysis device according to claim 2 of the present invention is the siphon according to claim 1, wherein the siphon bends at an inner peripheral position with respect to a liquid surface of the sample liquid held in the separation cavity in communication with the outermost peripheral position of the connection channel. A connecting flow path having a structure, and an overflow cavity that is located on the outer periphery of the outermost peripheral position of the connection flow path and communicates with the separation cavity via the connection flow path.

The analysis device according to claim 3 of the present invention is characterized in that, in claim 1, the capillary cavity is formed on one side surface of the separation cavity.
The analysis device according to claim 4 of the present invention is the analysis device according to claim 1, wherein one end of the capillary cavity is formed from the liquid surface of the sample solution to an outer peripheral position so as to be immersed in the sample solution held in the separation cavity. It is characterized by being.

  The analysis apparatus according to claim 5 of the present invention is an analysis apparatus in which the analysis device according to claim 1 that has collected the sample liquid is set, and is a rotation driving unit that rotates the analysis device around an axis. And analysis means for accessing and analyzing the reactant in the analysis device based on the solution transferred by the rotation driving means, and by rotating and stopping the rotation driving means, the sample liquid is converted into solution components and solids. It is characterized in that it can be separated into components and a part of the solid components can be collected.

  An analysis method according to claim 6 of the present invention is an analysis method using the analysis device according to claim 1, wherein the analysis device is set on a rotor having an axis, and the rotor is rotated. The sample liquid spotted on the analytical device is transferred to the separation cavity and centrifuged, and the solution component of the sample liquid after being centrifuged with the rotor stopped is formed inside the separation cavity. While being held in the capillary cavity, the solution component of the sample solution flowing from the separation cavity to the connecting passage and the solid component of the solid component are removed by the overflow channel communicating with the connecting passage, and the solid component is turned into the measuring channel. Transferring, rotating the rotor to mix the solid component and the dilute solution in the metering channel, rotating the rotor to read the measurement spot at the reading position Characterized by a step of accessing a reactant of the measurement spot with the timing of intervention.

  According to the analysis device of the present invention, the analysis apparatus using the analysis device, and the analysis method, it is possible to accurately transfer a specified amount of solid components from the separation cavity to the measurement flow path, thereby improving the measurement accuracy of the analysis device. be able to.

Hereinafter, embodiments of an analysis device, an analysis apparatus using the analysis device, and an analysis method according to the present invention will be described 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 13 show details of the analysis 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. 10 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. 13 shows the structure of the analytical device 1 in a block diagram. In the analytical device 1, 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 liquid 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.

  Here, the connecting channel 21, overflow channel 22, metering channel 23, connecting channel 24, capillary cavity 19, and overflow cavity 26 have a thickness dimension of 50 to 300 μm. There is no particular limitation as long as the sample liquid can be transferred by force. Moreover, although the cross-sectional dimension of the thickness direction of the separation cavity 18 and the overflow cavity 25 is 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 capillary part 28 for preventing the outflow of the different areas.

  Here, the cross-sectional dimension in the thickness direction of the connecting channel 15, the overflow channel 16, and the capillary portion 28 is configured to be 50 to 300 μm, but there is no particular limitation as long as the capillary force works. 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 through 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.
14 to 22 show the analysis device 1 set on the rotor 103 as viewed from the front 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. 14 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. 14A, 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), whereby the blood and the diluted solution 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 transferred to the blood is separated into a plasma component and a blood cell component by centrifugal force, and high-hematocrit blood at the outer peripheral portion is collected and diluted to reduce variation in dilution.

  In addition, the diluted liquid that is transferred to the holding cavity 14 during the rotation and exceeds the specified amount flows into the measurement spot 29 through the overflow channel 16, the overflow cavity 27, and the capillary portion 28 and is held. The

FIG. 15 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 channel 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. 15A, 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. 15B. When the rotation is stopped and the centrifugal force is lost, as shown in FIG. 15C, 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. 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. 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 reaches, 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. Specifically, as shown in FIG. 16A, in the comparative example in which the capillary cavity 19 is not formed in the separation cavity 18, the plasma component 57a is accumulated at the bottom of the separation cavity 18, and When the capillary is transferred by the capillary force, as shown in FIG. 16 (b), the plasma component 57a accumulated at the bottom of the separation cavity 18 is mixed from the connection channel 21 toward the measurement channel 23, and the necessary amount is obtained. The effectiveness of the capillary cavity 19 can also be seen from the fact that the blood cell component 57b cannot be obtained.

Further, a branch portion between the overflow channel 22 and the connection channel 21 provided between the separation cavity 18 and the measurement channel 23 will be described in detail.
FIGS. 23A and 23B are an enlarged view of a branch portion between the overflow channel 22 and the connection channel 21 and a cross-sectional view of the main part thereof. FIG.23 (b) shows FF sectional drawing in Fig.23 (a). The cross-sectional dimension g2 in the thickness direction of the overflow channel 22 is less than g1 so that the plasma component is not mixed into the measurement channel 23 as much as possible when the cross-sectional dimension in the thickness direction of the connecting channel 21 is 0.2 mm. And the width w2 of the overflow channel 22 in the direction intersecting the flow direction in the overflow channel 22 is a flow in the connection channel 21 of the connection channel 21. It is formed wider than the width w1 in the direction intersecting the direction.

  Thus, by making the cross-sectional dimension g2 in the thickness direction of the overflow channel 22 half of the cross-sectional dimension g1 in the thickness direction of the connection channel 21, the capillary force generated in the overflow channel 22 is connected to the connection channel 21. Therefore, the plasma component is preferentially transferred into the overflow channel 22 at the branch portion between the connecting channel 21 and the overflow channel 22. Furthermore, the width w2 of the overflow channel 22 in the direction intersecting the flow direction in the overflow channel 22 is made wider than the width w1 of the connection channel 21 in the direction intersecting with the flow direction in the connection channel 21. Thus, since the capillary force generated in the overflow channel 22 is larger than the capillary force of the connection channel 21, the plasma component in the connection channel 21 can be reliably transferred to the overflow channel 22. Here, when the cross-sectional dimension g2 is more than half of the cross-sectional dimension g1, the capillary force of the overflow flow path 22 and the connection flow path 21 becomes close to each other due to the difference in the surface state of the flow path, and a part of plasma components Since there is a risk of flowing into the measurement flow path 23, the cross-sectional dimension g2 in the thickness direction of the overflow flow path 22 is preferably less than half of the cross-sectional dimension g1 in the thickness direction of the connection flow path 21.

  Further, since the connecting channel 24 communicates with the outermost peripheral position of the connecting channel 21, the overflow channel is used when the blood cell component 57b held in the measuring channel 23 is transferred to the operation cavity 30 by centrifugal force. 22, the separation cavity 18, the capillary cavity 19, the connection channel 21, and the sample liquid not necessary for the measurement held in the connection channel 24 can be discharged to the overflow cavity 26, and the remaining sample liquid Inflow to the operation cavity 30 due to follow-up can be prevented.

  In this way, the capillary cavity 19 is formed in the separation cavity 18, and the plasma component 57a remaining in the separation cavity 18 is trapped by the capillary cavity 19, thereby eliminating the plasma component mixed into the measurement flow path 23 after centrifugation. In addition, since the plasma component 57a mixed in the connection channel 21 can be sucked up and removed by the capillary flow by the overflow channel 22, the blood cell component 57b is accurately supplied to the measuring channel 23 by a specified amount. Is held and flows into the operation cavity 30 in a later process, and a specified amount of diluent flows accurately from the holding cavity 14 into the operation cavity 30 via the connection channel 15. In other words, the diluted liquid transferred to the holding cavity 14 is overflowed via the overflow channel 16 when the liquid level to be held exceeds the connecting position of the overflow channel 16 and the overflow cavity 27. Since it is discharged to 27, it is held in the holding cavity 14 by a specified amount. Here, since the connecting channel 15 has a siphon shape including a curved pipe disposed radially inward from the connecting position of the overflow channel 16 and the overflow cavity 27, the analysis device 1 is rotating. The diluted solution can be held in the holding cavity 14.

  Further, since the overflow channel 16 that connects the holding cavity 14 and the overflow cavity 27 is a capillary tube, when the analytical device 1 is decelerated and stopped, the dilution liquid is transferred from the holding cavity 14 to the overflow cavity 27 by inertia force or surface tension. Can be prevented by capillary force, and the diluent can be accurately measured.

− 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. The diluted solution during stirring and mixing does not flow out into the holding cavity 32 because the diluted solution is positioned on the inner peripheral side of the liquid surface.

-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.

  The present invention can accurately transfer a specified amount of a solid component from a separation cavity to a measurement channel, so that analysis accuracy can be improved, and an analytical device used for component analysis of a liquid collected from a living organism or the like It is useful as a transfer control means.

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 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 Action explanatory view of the separation cavity 18 of the comparative example which does not have the capillary cavity 19 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 weighing 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 The enlarged view of the branch part of the overflow flow path 22 and the connection flow path 21 of the device for analysis in the same embodiment, and sectional drawing of the principal part Plan view and enlarged view of the main part of the analysis device of Patent Document 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, 26, 27 Overflow cavity 28 Capillary part 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 (6)

An analytical device having a microchannel structure for transferring a sample solution toward a measurement spot by centrifugal force, and used for reading a reactant in the measurement spot,
A separation cavity for separating the sample liquid into a solution component and a solid component using the centrifugal force;
A metering flow path in which a part of the solid component separated in the separation cavity is transferred and held;
An overflow channel provided between the metering channel and the separation cavity and connected to a connection channel for transferring the sample liquid in the separation cavity;
An analytical device comprising a capillary cavity formed inside the separation cavity so as to temporarily hold the separated solution component in the separation cavity. A connected flow path having a siphon structure that communicates with the outermost peripheral position of the connected flow path and bends at an inner peripheral position with respect to the liquid surface of the sample liquid held in the separation cavity;
The analysis device according to claim 1, further comprising an overflow cavity that is located on an outer periphery than the outermost peripheral position of the connection channel and communicates with the separation cavity via the connection channel. The analytical device according to claim 1, wherein the capillary cavity is formed on one side surface of the separation cavity. The analytical device according to claim 1, wherein one end of the capillary cavity is formed from the liquid surface of the sample liquid to an outer peripheral position so as to be immersed in the sample liquid held in the separation cavity. An analysis apparatus in which the analysis device according to claim 1 that has collected a sample liquid is set,
Rotational drive means for rotating the analytical device about an axis;
Analyzing means for accessing and analyzing reactants in the analytical device based on the solution transferred by the rotary drive means;
An analyzer configured to collect a part of the solid component by separating the sample liquid into a solution component and a solid component by rotating and stopping the rotation driving means. An analysis method using the analysis device according to claim 1,
The analysis device is set on a rotor having an axial center, the rotor is rotated, the sample liquid spotted on the analysis device is transferred to the separation cavity and centrifuged, and the rotor is stopped and centrifuged. The solution component of the sample solution that has been separated is held in the capillary cavity formed inside the separation cavity, and the solution component of the solution component and the solid component of the sample solution that flows from the separation cavity to the connection passage Removing in the overflow channel communicating with the connecting passage and transferring the solid component to the metering channel;
Rotating the rotor to mix the solid component and the dilute solution in the metering channel;
An analysis method comprising: rotating the rotor to access a reaction product of the measurement spot at a timing when the measurement spot is present at a reading position.

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