JP4702182B2 - Optical analysis device and optical analysis apparatus - Google Patents

Description

  The present invention relates to an optical analysis device and an optical analysis apparatus for optically analyzing a biological fluid, and more particularly to an analysis device used for measuring a component of a biological fluid in the optical analysis apparatus. The present invention relates to a chamber structure and a liquid sample transfer means.

  2. Description of the Related Art Conventionally, there is an analyzer for analyzing blood characteristics by using an optical disk technology of an optical disk device while using an analytical disk in which blood is collected as a liquid sample and rotating the analytical disk around an axis. Yes (see, for example, Patent Document 1).

  As shown in the exploded perspective view of FIG. 17, the analysis disk 100 has a base substrate 117 on which concentric or spiral tracks 101 exist, and a groove serving as a flow path through which blood is collected and transferred. The spacer substrate 118 and an upper cover 119 in which blood inlets and air ports are formed are bonded to each other on the spacer substrate 118.

  The plan view of FIG. 18 is an enlarged view of one of the flow paths provided in the analysis disk 100. The analysis disk 100 collects a certain amount of blood and separates the blood into a blood cell component and a plasma component, and is disposed outside the axis with respect to the first chamber 200. It has the 2nd chamber 201 to which the plasma component isolate | separated in the chamber 200 is transferred, and the capillary 202 which connects the 1st chamber 200 and the 2nd chamber 201. FIG.

  As an analysis operation using such an analysis disc, blood 208 is filled with an inlet 204 formed in the first chamber 200 with a pipette or the like, and the blood is collected in the first chamber 200 and analyzed. The disk 100 is rotated. Then, the blood is centrifuged in a state where it does not cross the apex 202 a of the capillary 202, that is, in a state where it is held in the first chamber 200.

  After the centrifugation, when the rotation of the analysis disk 100 is stopped, the centrifuged plasma component is transferred to the entrance of the second chamber 201 through the capillary apex 202a by capillary action.

  Then, when the analysis disk 100 is rotated again, the separated plasma component is transferred from the first chamber 200 to the second chamber 201 by centrifugal force and capillary action force. The second chamber 201 can hold a reagent that develops color by reacting with a specific substance to be analyzed in plasma. As a method for applying the reagent, before the upper cover 119 is attached to the upper portion of the spacer substrate 118, the reagent is dropped into the second chamber 201 of the upper cover 119 and dried. After the dried reagent is uniformly applied to the wall surface of the second chamber of the upper cover 119, the upper cover 119 is attached to the upper portion of the spacer substrate 118.

  After the transfer to the second chamber 201 is completed and a color reaction occurs, the analysis disk 100 is rotated along the track 101 from the inner circumference to the outer circumference or from the outer circumference to the inner circumference. The second chamber 201 is scanned by irradiating light. By detecting the transmitted light obtained from the second chamber 201, the amount of a specific substance in the plasma component that has reacted with the reagent can be detected.

Note that by changing the type of reagent held in the second chamber, it is possible to analyze other substances in plasma components, and it is also possible to detect using reflected light as well as transmitted light. . Furthermore, the example in which the above-described flow path is configured by only the first to second chambers has been described. However, the present invention is not limited thereto, and more chambers may be connected to the second and subsequent chambers. Sometimes configured.
Japanese National Patent Publication No. 10-50497

  By the way, in the optical analysis apparatus as described above, the plasma component centrifuged in the first chamber 200 must be reliably transferred through the capillary 202 by a predetermined amount necessary for the analysis in the second chamber 201. I must.

  However, in the above-described conventional analyzer, in order to reduce the size of the analysis disk, it is desired to make the thickness of the first chamber 200 as small as possible partially. The difference with the thickness of the capillary 202 is reduced, the capillary force generated between the first chamber 200 and the capillary 202 is reduced, and sufficient driving force for transferring the plasma component cannot be obtained. There was a problem that blood components could not be transferred to the second chamber 201.

  In addition, when the first chamber 201 is not a separation chamber but is simply a chamber coated with a reagent, it is mixed with blood that has been injected or transferred, and when the reagent is dissolved in the blood, the corner in the chamber is inevitably. The reagent can be unevenly distributed at the end (end). This is because, when the dropped reagent is dried, the reagent is inevitably biased to the corner (end) of the wall surface of the first chamber 201, so that the corner (end) in the chamber is dissolved when dissolved with the injection solution. There was a problem that the concentration of the reaction solution at 1 was high and was not uniform.

  To prevent this, the thickness of the first chamber 200 is desired to be as thin as possible so that the corner (end) region in the chamber is reduced, but for transferring blood to the second chamber 201 Since sufficient transfer driving force cannot be obtained, reliable agitation using this transfer driving force is insufficient, so even if transferred to the second chamber 201, the reaction in the subsequent chambers is hindered. Therefore, there was a problem that analysis with high accuracy was impossible.

  Therefore, the present invention solves the above-mentioned problem, and even when the chamber is thin, it is possible to obtain a transfer driving force that can reliably transfer the solution and to dissolve the reagent uniformly. An object of the present invention is to provide an optical analysis device of an optical analyzer.

  In order to solve the above-described problems, an optical analysis device according to the present invention analyzes light emitted from the liquid sample based on light applied to the liquid sample accommodated in a chamber provided therein, and thereby the liquid sample. A first chamber disposed around a rotation axis of the optical analysis device and configured to be capable of injecting the liquid sample, with respect to the rotation axis as compared to the first chamber. A second chamber that is disposed outside and is connected to the first chamber by a capillary and configured to receive a liquid sample injected into the first chamber through the capillary, the first chamber comprising: A first region having a space that is longer in a direction parallel to the rotation axis than the capillary on the upstream side of the flow path of the liquid sample; A second region having a space in a direction parallel to the rotation axis on the connecting portion side with a length longer than the capillary and shorter in a direction parallel to the rotation axis than the first region; It is characterized by having.

  The present invention is characterized in that a difference in length in a direction parallel to the rotation axis between the first region and the second region in the first chamber is 50 μm or more and 2 mm or less.

  The present invention is also characterized in that, in the first chamber, the volume of the first region is not less than the volume of the capillary.

Further, the present invention is characterized in that in the first chamber, a reagent that reacts with a liquid sample is applied to a wall surface forming the second region.
Further, the present invention is characterized in that the second region is formed by bonding two substrates, and the cross-sectional shape of the substrate perpendicular to the direction in which the liquid sample flows has a concave shape.

  In the present invention, the concave shape is a semicircular shape, and the second region is provided with a semicylindrical wall surface.

  In the second region, the second region has a ground glass-like uneven portion on at least a part of the surface of the substrate having the concave shape, and the height difference in the uneven portion is 0.01 mm or more and 0.5 mm or less. It is characterized by being.

  Further, the present invention is characterized in that the second region has two or more grooves on the surface of the substrate having the concave shape.

  In the second region, the surface of the substrate having the concave shape may have two or more grooves substantially parallel to the flow of the liquid sample.

  In the second region, the substantially parallel grooves are 1 mm or less at intervals of 2 mm or less, and the depth of the grooves is 0.05 mm or more and 1 mm or less. .

  In the second region, the cross-sectional shape of the substrate in the direction in which the liquid sample flows has a semicircular shape or a semielliptical shape on the downstream side.

  Further, the present invention is characterized in that the optical analysis device is a test piece detachable from an analysis apparatus, and the capillary and the chamber are provided on the test piece.

  Further, an analysis apparatus to which the optical analysis device is attached, comprising: a rotation drive unit that rotates the analysis device around an axis, wherein the liquid sample is stored in the first chamber. The plasma component of the liquid sample is transferred to the capillary by stopping the rotation, and the plasma component of the liquid sample is transferred to the second chamber by rotating again.

  According to the optical analysis device of the present invention as described above, since the difference between the thickness of the first chamber 200 and the capillary 202 is small when the thickness of the first chamber 200 is thin, the required amount of Auxiliary to the problem that a sufficient capillary force that can reliably transfer the solution to the second chamber cannot be generated and that the reagent cannot be uniformly stirred in the chamber because the capillary force is insufficient. Since a propulsive transfer force can be generated, reliable transfer is possible.

  In addition, since a sufficient driving force for ensuring the transfer of the solution can be obtained, a stirring action occurs during the transfer, and uniform stirring with the reagent can be achieved, and the subsequent analysis system can be improved. There is an effect.

  In addition, when the dropped reagent is dried, the reagent can be uniformly applied without being biased to the corner (end) of the wall surface of the first chamber 201. Therefore, it is possible to perform uniform stirring when mixing with the solution. There is also.

  Hereinafter, embodiments of the optical analysis device of the present invention will be described in detail with reference to the drawings.

(Embodiment 1)
FIG. 1 shows a configuration diagram of an analyzer according to Embodiment 1 of the present invention. In the lower part of the analyzer, an optical pickup 104 for irradiating the analysis device 100 with light, a traverse motor 105 for moving the optical pickup 104 in the radial direction of the analysis device, and a device for rotating the analysis device 100 are driven. A spindle motor 106 is disposed. These are driven by the CPU 109 and the servo control circuit 107 after the information obtained by reading the track 101 obtained by the optical pickup 104 is calculated by the signal processing circuit 108.

  In the upper part of the analyzer, a photodetector 103 that detects transmitted light 102 that has passed through the device for analysis 100 out of the laser light emitted from the optical pickup 104 is disposed.

  The signal detected by the photodetector 103 is A / D converted by the A / D converter 111, and the A / D converted data is signal-processed by the signal processing circuit 115, and a liquid sample, for example, a specific substance in blood is detected. In addition to the concentration and quantity, the shape and size of the substance are calculated according to the purpose of the analysis. The memory 112 holds a table for converting the value calculated by the signal processing circuit 115 into a value such as the concentration of the specific substance, and stores the obtained value such as the concentration. The obtained analysis values are output to the display unit 120, and these are controlled by the CPU 114.

  In this embodiment, the analysis device having the structure shown in FIG. 17 is used, but the flow path structure is different from that shown in FIG. The optical analysis device will be described as an example.

  The flow channel structure shown in FIG. 2 is for measuring good cholesterol, so-called HDL-C.

  A specific structure includes a first chamber 200 having an inlet 204 for injecting a liquid sample, a second chamber 201 connected by the first chamber 200 and a capillary 202, and a second chamber 201 and a capillary 205. And a fourth chamber 206 connected to the third chamber 203 by a capillary 207. Note that the third chamber 203 and the fourth chamber 206 are coated with reagents necessary for HDL-C analysis.

  Below, along the flow which analyzes HDL-C, the basic operation | movement which the analyzer in this Embodiment analyzes with high precision is demonstrated.

  First, blood 208 is injected from the inlet 204 of the analysis device 100, and the analysis device 100 in a state in which the first chamber 200 is filled with blood is attached to the analysis apparatus, and spin-up performed in a conventional optical device apparatus Process.

  Thereafter, a centrifugal separation process for separating blood into a plasma component 300 and a blood cell component 301 is performed. In the centrifugal separation process, for example, the analysis device 100 is rotated at a rotational speed of 4000 to 6000 rpm for 2 to 3 minutes.

  When the analysis device 100 stops rotating after a predetermined time has elapsed, the plasma component 300 separated in the first chamber 200 is transferred through the capillary 202 and proceeds to the entrance of the second chamber 201. Therefore, when the analysis device 100 is rotated again at 1000 to 3000 rpm, the plasma component flows into the second chamber 201 and the second chamber 201 is filled with the plasma component 300. The volume of the second chamber 201 is designed to be smaller than the volume of the plasma component separated in the first chamber 200. For this reason, since the second chamber 201 is filled with the plasma component, the amount of the plasma component can be measured (quantified) (FIG. 3).

  When the rotation of the analytical device is stopped again, the supernatant plasma component 300 held on the inner peripheral side of the second chamber 201 flows from the second chamber 201 to the capillary 205 and proceeds to the entrance of the third chamber 203. To do. When the analysis device 100 is rotated again at 1000 to 6000 rpm, the plasma component 300 is transferred from the capillary 205 to the third chamber 203 and fills the third chamber 203.

  In the third chamber 203, the reagent previously arranged in the chamber reacts with the transferred plasma component. In the third chamber 203, a reagent that causes an agglutination reaction with a cholesterol component other than HDL-C in the plasma component 300 can be disposed. The reason for arranging such an agglutinating reagent is to remove cholesterol components other than HDL-C, which hinder the optical analysis of HDL-C in later analysis. When the analysis device is stopped or rotated at a low speed for a certain time, an aggregate 303 is generated in the third chamber 203 as shown in FIG.

  After the elapse of a certain time, the analytical device is rotated again at a rotational speed of 3000 to 6000 rpm for about 3 to 10 minutes to move the generated aggregate as shown in FIG. Centrifuge at 303.

  According to the transfer method described above, the plasma component 303 excluding the aggregate 303 is transferred to the fourth chamber 206 (FIG. 7). In the fourth chamber, a reagent 304 that reacts with HDL-C to generate a color reaction is held in advance, and the optical pickup 104 and the photodetector 103 are moved to the fourth chamber 206, and the optical pickup 104 The laser is irradiated, the transmitted light is detected by the photodetector 103, and the absorbance is measured.

  The memory 112 stores a table relating the absorbance and the HDL-C concentration, and the analyzer reads out the HDL-C concentration corresponding to the detected absorbance and outputs it to the display unit 120.

  Here, in the above series of HDL-C concentration measurement, a characteristic configuration of the present embodiment will be specifically described. The present embodiment is characterized in that a sufficient transfer driving force is generated in the second chamber 201 for surely transferring.

  FIG. 11 explains what the sufficient capillary force that can transfer this liquid is.

  FIG. 11 is a plan view showing the second chamber 201 when the plasma is transferred to the second chamber 201 and filled with plasma components. When the analysis device stops rotating, the supernatant plasma component 300 held on the inner peripheral side of the second chamber 201 flows from the second chamber 201 to the capillary 205 and proceeds to the inlet 412 of the third chamber 203. To do.

  In this case, the plasma component does not necessarily need to reach the entrance 412 of the third chamber 203, and travels within the region 411 from the outermost peripheral surface 413 of the second chamber to the entrance 412 of the third chamber 203. Then, when the analysis device 100 is rotated again at 1000 to 6000 rpm, the plasma component 300 is transferred from the capillary 205 to the third chamber 203 and can fill the third chamber 203. .

  Therefore, when the analysis device stops rotating, the plasma component 300 of the second chamber 201 can advance at least beyond the outermost peripheral surface 413 of the second chamber to the range of the region 411 so as to surely advance. Power is needed.

  FIG. 8 is an enlarged view of the second chamber 201 in the present embodiment, and is a cross-sectional view taken along line AA ′ in FIG. FIG. 8 shows a state before the plasma is transferred to the second chamber 201. The second chamber 201 has a first region 401 having a thickness larger than at least the capillary 205 on the upstream side, a thickness greater than the capillary 205 on the side where the capillary 205 is connected, and the first chamber 401. And a second region 402 having a thickness smaller than that of the region 401. That is, a step is provided so that the thickness of the second chamber 201 in the axial direction is shallower on the side closer to the downstream capillary 205, and a cavity 417 is formed so that liquid can flow into the step.

  Next, the dimensional relationship will be described. The dimension 406 in the axial direction of the first region 401 is approximately 600 μm, and the dimension of the dimension 407 in the axial direction of the second region 402 is approximately 200 μm. The dimension 403 in the axial direction of the capillary 205 is about 100 μm, and the dimension 403 in the axial direction of the capillary 205 is about 50 μm. The dimension 408 in the transport direction (track direction) of the first region 401 is about 2 mm, and the dimension 409 in the transport direction (track direction) of the second region 402 is about 8 mm.

  Therefore, by setting the thickness to such a thickness, in addition to the capillary force 418 generated by the difference in size between the second region 402 of the second chamber 202 and the capillary 205 when the liquid is introduced, the same chamber is used. Even in 201, a capillary force (a force generated by a capillary phenomenon) 410 due to a difference in size between the first region 401 and the second region 402 is generated, so that a stronger transfer driving force can be generated. FIG. 9 shows a state in which the second chamber 201 is filled with plasma components when the analysis device 100 is rotated at a rotation speed of 1000 to 3000 rpm.

  In the second chamber 201, after the reagent previously arranged in the chamber and the transferred plasma component reacted, when the rotation of the analyzing device was stopped again, the second chamber 201 was held on the inner peripheral side of the second chamber 201. The supernatant plasma component 300 flows from the second chamber 201 to the capillary 205 and proceeds to the entrance of the third chamber 203.

  At this time, the capillary force 410 acting on the plasma component 405 acts in the direction of the arrow between the first region 401 and the second region 402 in the second chamber 201 as shown in FIG. It becomes a transfer driving force. This transfer driving force generates an action of strengthening the capillary force 418 acting between the second region 402 and the capillary 205, so that the plasma component 405 is reliably sucked up into the capillary 205.

  That is, when the analysis device stops rotating due to the capillary force 410, the plasma component 300 of the second chamber 201 flows into the capillary 205 and reliably exceeds the outermost peripheral surface 413 of the second chamber 411. It is possible to generate a sufficient capillary force that can proceed to within the above range.

Next, the volume of the first region 401 will be briefly described. When the analysis device is stopped, the plasma component 300 flows into the capillary 205, but when the analysis device is rotated (before the stop), the plasma component 300 is not filled with the plasma component on the inner peripheral side of the second region 402. The region also flows into the area by this transfer driving force (not shown). Therefore, the volume of the plasma component filled in the first region 401 at the time of rotation of the analysis device is equal to the volume of the second region 402 that was not filled at the time of rotation of the analysis device (before stopping). It may be larger than the sum of the volume that has flowed into the inner peripheral region and the volume of the plasma component 300 in the capillary 205 that has advanced to the outermost peripheral surface 413 of the second chamber. In other words, the volume of the first region only needs to be large enough to satisfy the above conditions, and is preferably at least the volume of the capillary. However, when the volume of the first region is smaller than the above condition, the plasma component 300 cannot advance to the outermost peripheral surface 413 of the second chamber in the capillary 205 when the analysis device is stopped. As a result, the device can not be transferred to the third chamber 203 even if the device is rotated again.

  In this embodiment, the transfer propulsive force is generated by setting the difference between the axial dimension 406 of the first region 401 and the axial dimension 407 of the second region 402 to about 400 μm. However, due to the structure of the thickness of the device for analysis, if this dimensional difference is 50 μm or more and 2 mm or less (preferably 300 μm or more and 500 μm or less), a sufficient capillary force can be generated. The plasma component 300 in the chamber 201 can be reliably transferred to the third chamber 203 through the capillary 205.

  In addition, when the dimensional difference is 50 μm or less, a capillary force sufficient to transfer the plasma component 300 of the second chamber 201 to the third chamber 203 through the capillary 205 is not generated. As a result, the experiment was not very effective.

  Theoretically, it is possible to make the dimensional difference larger than 2 mm, but the analytical device itself is made as thin as possible, and a small analytical device that can measure the plasma component 300 with as little usage as possible. This is advantageous in terms of reduction in measurement time and cost. Therefore, an analytical device having a dimensional difference chamber greater than 2 mm is not very practical. Furthermore, when the optical disk of the optical disk apparatus is used as it is as the base substrate of the analyzing device and the upper cover has a chamber with a dimensional difference larger than 2 mm, the thickness of the upper cover can be taken into consideration. Obviously, this is not practical because it will exceed about 3-4 mm and the thickness of the analytical device itself will also exceed about 5 mm.

  The generated capillary force is somewhat affected by the surface treatment of the inner walls of the capillary and the chamber, and the higher the hydrophilicity, the higher the capillary force, and also somewhat affected by the cross-sectional shape of the chamber capillary.

  In this embodiment, the external shape of the optical analysis device is conveniently a circular device, but is not limited to a circular device as long as it is a rotatable device, and includes any shape such as a rectangle or an ellipse.

  Further, in this embodiment, as shown in FIG. 1, the optical analyzer includes an analyzer that applies the optical scanning technology of the optical disk device, and an information area (track information and address information) for controlling rotation and signal reading. However, this is not always necessary. The structure of the optical analysis device may be a detachable test piece (panel shape) that does not have an information area (track information or address information) for controlling rotation and signal reading. The test piece may be directly attached to a rotatable plate (not shown) of the apparatus.

  In this embodiment, the injection port 204 is provided on the upper surface of the first chamber 200. However, the injection port is formed (not shown) on the end surface on the center side where the test piece rotates. Thus, after the spotting, the liquid sample may be reliably transferred and stopped to the reagent side by centrifugal force during the test.

  As described above, according to the first embodiment, when transferring from chamber to chamber, the amount necessary for analysis can be reliably transferred, and the reliability of analysis accuracy of HDL-C thereafter can be improved. Can be improved.

(Embodiment 2)
Next, as Embodiment 2 of the present invention, an example will be described in which a reagent necessary for analysis held in the second chamber 201 can be uniformly dissolved. The configurations of the optical analysis apparatus and the analysis device used in the second embodiment are the same as those described in the first embodiment. The difference from Embodiment 1 is that the second chamber 201 of the analytical device is also preliminarily held with a reagent that precipitates components other than HDL-C (including a reagent that hemolyzes blood cell components). . Hereinafter, the operation of the analyzer according to the present embodiment will be described focusing on these different points.

  FIG. 4 shows a state when the plasma component is transferred to the second chamber, and it reacts with the reagent applied to the second chamber.

  FIG. 12 is an enlarged view of the second chamber 201 in the present embodiment, and is a cross-sectional view taken along line AA ′ in FIG. The reagent 414 is applied to the inner wall of the second region 402 having a smaller thickness than the first region 401 by drying the dropped reagent 414. Although it is possible to carry the reagent 414 also in the first region 401, as described later, when the dropped reagent 414 is dried, the reagent is inevitably caused by its surface tension. Due to the property of being collected at the corner, uniformity is not achieved at the time of dissolution with the plasma component. Therefore, as a countermeasure, in the embodiment, the reagent 414 is formed on the inner wall of the second region 402 where the corner region is shallow and narrow. It is desirable to carry

  Here, the following method was used to test how much the reaction is affected by the shape of the wall surface of the second chamber 201.

  The wall surface of the second chamber 201 is processed into a predetermined shape, and after applying a precipitation reagent (sodium phosphotungstate & magnesium chloride) to this chamber 201 and drying, the plasma components are transferred and non-reacted by reaction with the precipitation reagent. After precipitating the HDL-C component, it was carried out by measuring how much non-HDL-C component was contained in the top static.

  As for the shapes of various wall surfaces (inner surfaces), as shown in FIGS. 16a to 16d, an unprocessed wall surface, a ground glass-like wall surface, a wall surface provided with five grooves, a wall surface provided with ten grooves, and a depression at the center. The wall surfaces provided were each of five types. FIG. 20 shows the results obtained by measuring the non-HDL-C component (LDL) to be precipitated as to whether or not the reaction with the precipitation reagent is reliably performed for each of these five types of wall surfaces. Experimental result 1 and experimental result 2 are the results of experiments using two types of original samples with different sample liquid concentrations.

  In the chambers processed into various wall shapes, the precipitates were collected, the top was collected, and the TC concentration and LDL concentration were measured using an automatic analyzer “Hitachi 7020”.

  In the experimental result 1, on the unprocessed wall, when LDL is used as a guideline as a representative of the non-HDL component of the original sample of 103 mg / dl, there is 3 mg / dl of LDL that has not been precipitated by the precipitation reaction treatment. To do. On the other hand, on the ground glass-like wall surface, the wall surface provided with 5 grooves, the wall surface provided with 10 grooves, and the wall surface provided with a depression at the center, LDL not precipitated by the precipitation reaction treatment is 0 mg. / dl.

  Moreover, in the experimental result 2, on the unprocessed wall, when LDL is focused on as a representative of the non-HDL component of the original sample of 183 mg / dl, there is 5 mg / dl of LDL that has not been precipitated by the precipitation reaction treatment. On the other hand, LDL not precipitated by the precipitation reaction treatment is 2 mg / dl on the ground glass wall surface, 3 mg / dl on the wall surface provided with 5 grooves, and 1 mg / dl on the wall surface provided with 10 grooves. dl, and 0 mg / dl on the wall surface with the depression at the center.

  As can be seen from the experimental results, the concentration of LDL of the non-HDL component, which is not precipitated by the precipitation reaction process, is lower than that of the conventional example in which no processing is performed on the wall surface of the second chamber 201. Indicates that it was suppressed.

  This shows that the reaction between the non-HDL component and the precipitating reagent is surely promoted when the predetermined processing is performed rather than when the wall surface is not processed.

  A sample obtained by reacting a plasma component with a precipitating reagent was previously tested with an automatic analyzer as a reference.

  Next, the dimensions will be described.

  FIG. 13 is an enlarged view of the second chamber 201 in the present embodiment, and is a cross-sectional view taken along line B-B ′ in FIG. 11. In FIG. 13, since the shape of the inner wall 120 to which the reagent is applied is semicircular, the upper cover 119 is cut into a semicircular shape, and the second region is formed by bonding at least two substrates. It is configured. FIG. 19 shows a shape in which the wall surface is not subjected to any processing, and is one shape of the prior art in which the shape of the inner wall 120 is substantially linear, and is a cross-sectional view taken along line BB ′ in FIG. is there.

  However, in the case of such a shape, a corner (corner) 416 is inevitably generated on the wall surface 120 of the upper cover 119 in the chamber. In this case, as can be seen from FIG. 21, when the dropped reagent 414 is dried, the reagent inevitably gathers in the region of about 1 to 1.5 mm from the end of the wall surface of the first chamber 201 due to surface tension. Since it is dried as it is, the reagent is biased to the corner (end) of the wall surface of the first chamber 201. For this reason, when the second chamber 201 is dissolved with the plasma component that has been injected or transferred, the reagent is inevitably unevenly distributed in the corner (end) region in the chamber. The concentration of the reaction solution is high at the (end), and the concentration of the reaction solution is low at the center.

  This is the main factor that causes the problem that the concentration is not uniform in the chamber, and the uniform reaction with the reagent is not possible. To prevent this, as shown in FIGS. 13 and 16d, a circular recess is provided so that the central portion of the shape of the inner wall 120 is recessed so that the corner (end) region in the chamber is reduced. However, it can be seen that the unevenness of the reagent applied and dried at the corner (end) can be suppressed. The depth of the central recess is limited by the size of the chamber and the thickness of the analysis device, but is set to about 0.5 mm in the present embodiment in order to round the corners of the wall surface.

  FIG. 14 and FIG. 16 a are the shapes of the other examples of the sectional view of the second region 402 in the second chamber 201. The shape of the inner wall 120 to which the reagent is applied is semicircular (or linear), and is the same as that of FIG. 13 (or FIG. 19), but parallel to the flow of the liquid sample on the surface of the substrate having the concave shape. It has 5 grooves.

  In this example, grooves having a width of about 0.5 mm were provided at intervals of about 1 mm, and the depth of the grooves was about 0.5 mm. By adopting such a structure, as shown in FIG. 21b, when the reagent is applied and dried, the reagent is not biased only at the corner (end) of the wall surface of the second chamber 201, and the groove portion of the entire inner wall 120 surface is formed. Reagents can also be collected and applied and dried. For this reason, it is possible to prevent unevenness due to the deviation of the reagent only in the corner (end) region in the chamber during dissolution with the infused or transferred plasma component, so that the concentration in the chamber is uniform. Property can be improved.

  FIG. 16b shows a wall surface provided with 10 grooves. However, the application state of the reagent when the reagent is applied and dried is compared with FIG. 21b showing the wall surface provided with 5 grooves. Is further shortened, so that the uniformity within the chamber can be further improved.

  Although the depth of the groove is also limited by the size of the chamber and the thickness of the analysis device, in this embodiment, the height difference in the concavo-convex portion is about 0.5 mm, but preferably 0.05 mm or more and 1 mm or less. When the dimension is less than 0.05 mm, it is insufficient to apply and dry the reagent uniformly on the wall surface, so that the effect is not obtained.

  Further, in a chamber having a height difference groove of more than 1 mm, when the dropped reagent 414 is dried, the corner area due to the height difference increases, so that the reagent is applied to the corner area of each groove due to surface tension. Since the gathering reagents are biased, the difference in the contrast of the reagents becomes larger for each groove, so that a very good effect cannot be obtained. Theoretically, it is possible to make the height difference larger than 1 mm. However, since it is desirable to make the thickness of the analytical device itself as thin as possible, an analytical device having a height difference chamber larger than 1 mm is not very realistic. Absent.

  The groove width and spacing are also limited by the size of the chamber and the thickness of the analytical device, but the groove spacing is about 1 mm and the groove width is about 0.5 mm, preferably the groove spacing. Is about 2 mm or less, and the width of the groove is 1 mm or less. If the interval between the grooves is made larger than about 2 mm or the width of the groove is made larger than 1 mm, the number of grooves is reduced, so that the effect is not obtained.

  In FIG. 16 c, a ground glass wall surface is formed on the wall surface 120, and the height difference in the uneven portion is 0.2 mm. Although restricted by the size of the chamber and the thickness of the analysis device, in order to make the corners of the wall round, in this embodiment, the height difference in the concavo-convex part is about 0.2 mm. When the dimension is from 01 mm to 0.5 mm and less than 0.01 mm, it is not sufficient to apply and dry the reagent uniformly on the wall surface, so that the effect is not obtained.

  Further, in a chamber having a height difference groove larger than 0.5 mm, when the dropped reagent 414 is dried, the corner area due to the height difference increases, so that the reagent is provided at each corner of the ground glass-like uneven portion. Collected due to surface tension, but the difference in density of the reagent was not constant, and a very good effect was not obtained. Theoretically, although it is possible to make the height difference larger than 0.5 mm, it is desirable to make the thickness of the analytical device itself as thin as possible. It is not so preferable, and it is not realistic because it is difficult to manufacture and process the ground glass wall.

  By adopting such a structure, the application state of the reagent when the reagent is applied and dried is compared with the conventional wall surface shape (FIGS. 19 and 21a) in which the shape of the inner wall 120 is linear, over the entire wall surface. Since the reagent can be applied (not shown), the uniformity in the chamber can be improved. This can prevent uneven unevenness of the reagent at the corner (side wall surface).

  FIG. 15 shows a shape of another example of the sectional view of the second chamber 201, which is an enlarged view of the second chamber 201 in the present embodiment, and is a sectional view taken along line AA ′ in FIG. It is. The cross-sectional shape 415 on the side from which the liquid sample flows out has at least a semicircular shape or a semielliptical shape. This not only makes the wall surface 120 to which the reagent is applied have a semicircular shape, but also the wall surface on the downstream side of the second chamber 201 has a semicircular or semielliptical shape in the liquid sample transfer direction.

  By adopting such a structure, the corner (corner) generated between the wall surface through which the liquid sample in the second chamber 201 flows out and the cover device can be eliminated, so that the dropped reagent 414 is dried. The occurrence of unevenness due to the bias of the reagent to the corner (corner) can be reduced. This has the effect of preventing the concentration of the reaction solution from increasing at the corner (end) in the chamber during dissolution with the injection solution and improving the uniformity.

  As described above, in any structure of the second chamber 201, when the dropped reagent 414 is dried, it can be prevented that the reagent is unevenly distributed near the wall surfaces 415 and 416 of the wall surface 120. When the reagent is dissolved with the plasma component that has been injected or transferred, the reagent can be diffused throughout the cavity to make the concentration of the reaction solution uniform.

  Note that the present invention is not limited to the structure of the second chamber 201 described in the first and second embodiments, and the number of chambers may be configured in accordance with the purpose of analysis, and if there are two or more chambers, The present invention can be implemented.

  An analysis apparatus according to the present invention is an apparatus that collects a liquid sample in a rotatable device, and performs an analysis on a specific substance in the liquid sample in a second chamber after performing centrifugation in the first chamber. The present invention can be applied, and can be applied not only to the medical field but also to analyzers in the environmental field.

1 is a configuration diagram of an optical analysis device according to Embodiment 1 of the present invention. Plan view of relevant parts of the optical analysis device according to Embodiment 1 of the present invention Plan view of relevant parts of the optical analysis device according to Embodiment 1 of the present invention Plan view of relevant parts of the optical analysis device according to Embodiment 1 of the present invention Plan view of relevant parts of the optical analysis device according to Embodiment 1 of the present invention Plan view of relevant parts of the optical analysis device according to Embodiment 1 of the present invention Plan view of relevant parts of the optical analysis device according to Embodiment 1 of the present invention Plan view of relevant parts of the optical analysis device according to Embodiment 1 of the present invention Plan view of relevant parts of the optical analysis device according to Embodiment 1 of the present invention Plan view of relevant parts of the optical analysis device according to Embodiment 1 of the present invention Plan view of relevant parts of the optical analysis device according to the first and second embodiments of the present invention The principal part top view of the device for optical analysis in Embodiment 2 of this invention Sectional drawing of the principal part of the device for optical analysis in Embodiment 2 of this invention Sectional drawing of the principal part of the device for optical analysis in Embodiment 2 of this invention Sectional drawing of the principal part of the device for optical analysis in Embodiment 2 of this invention Sectional drawing of the principal part of the device for optical analysis (form five grooves) in Embodiment 2 of the present invention Sectional drawing of the principal part of the optical analysis device (form 10 grooves) in Embodiment 2 of the present invention Sectional drawing of the principal part of the device for optical analysis in the second embodiment of the present invention (forming a ground glass-like uneven portion) Sectional drawing of the principal part of the device for optical analysis in Embodiment 2 of this invention (a dent is formed in the center part) Exploded perspective view of a conventional optical analysis device Plan view of main parts of a conventional optical analysis device Cross section of the main part of a conventional analytical device (reagent application state) The figure which shows the reaction result of the non-HDL component (LDL) and the precipitation reagent when the wall surface is processed The figure which shows the dry application | coating state of the reagent at the time of apply | coating and drying the reagent on the conventional wall surface (unprocessed) The figure which shows the dry application | coating state of a reagent when a reagent is apply | coated and dried to the wall surface in which the groove | channel was provided.

Explanation of symbols

100 Analytical device (disk)
101 Track 102 Transmitted Light 103 Photodetector 104 Optical Pickup 105 Traverse Motor 106 Spindle Motor 107 Servo Control Circuit 108 Signal Processing Circuit 109, 114 CPU
DESCRIPTION OF SYMBOLS 110 Adjustment circuit 111 A / D converter 112 Memory 115 Signal processing circuit 117 Base substrate 118 Spacer substrate 119 Upper cover 120 Wall surface 200 First chamber 202, 205, 207 Capillary 201 Second chamber 203 Third chamber 204 Inlet 206 Fourth chamber 208 Blood 300, 405 Plasma component 301 Blood cell 303 Aggregate 304, 414 Reagent 400 Centrifugal force 401 First region 402 Second region 403 Siphon thickness (dimension in the axial direction of capillary 205)
404 Siphon width (capillary 205 dimension in track direction)
406 Thickness of the first region (dimension in the axial direction of the first region 401)
407 Thickness of the second region (dimension in the axial direction of the second region 402)
408 Width of the first area (size of the first area 401 in the transfer direction (track direction))
409 Width of the second area (dimension in the transfer direction (track direction) of the second area 402)
410 Capillary force (transfer propulsion force)
411 Region 412 Entrance of third chamber 413 Outermost peripheral surface of second chamber 415 Wall surface (side wall surface, corner)
416 Corner (corner)
417 Cavity 418 Capillary force 420 Groove width 421 Width in the radial direction of the second chamber 422 Distance between the reagent applied to the wall surface and the side wall surface 423 Reagent applied to the groove in the wall surface 424 Groove 425 Uneven wall surface 426 Wall with a dent in the center

Claims (13)

In the optical analysis device for analyzing the liquid sample by analyzing the light emitted from the liquid sample based on the light irradiated to the liquid sample accommodated in the chamber provided therein, the rotation axis of the optical analysis device A first chamber disposed around and configured to be capable of injecting the liquid sample; disposed outside the rotation axis as compared to the first chamber; and connected to the first chamber by a capillary; A second chamber configured to receive a liquid sample injected into the first chamber through a capillary, and the first chamber is disposed upstream of the flow path of the liquid sample from the capillary to the rotating shaft. The length in the direction parallel to the rotation axis is connected to the first region having a space with a long length in the parallel direction and the capillary side. Longer than lari, and than said first region having a second region having a direction of a short space length parallel to the rotation axis, the device for optical analysis, characterized in that. 2. The optical according to claim 1, wherein a difference in length between the first region and the second region in a direction parallel to the rotation axis in the first chamber is 50 μm or more and 2 mm or less. Analytical device. 3. The optical analysis device according to claim 1, wherein a volume of the first region in the first chamber is equal to or greater than a volume of the capillary. The optical analysis device according to any one of claims 1 to 3, wherein a reagent that reacts with a liquid sample is applied to a wall surface that forms the second region in the first chamber. 5. The optical device according to claim 4, wherein the second region is formed by bonding two substrates, and the cross-sectional shape of the substrate perpendicular to the direction in which the liquid sample flows has a concave shape. Analytical device. The device for optical analysis according to claim 5, wherein the cross-sectional shape is a semicircular shape, and the second region includes a semi-cylindrical wall surface. The second region has a ground glass-like concavo-convex portion on at least a part of the surface of the substrate having the concave shape, and a height difference in the concavo-convex portion is 0.01 mm or more and 0.5 mm or less. The optical analysis device according to claim 5 or 6. The optical analysis device according to claim 5, wherein the second region has two or more grooves on the surface of the substrate having the concave shape. 9. The device for optical analysis according to claim 8, wherein the grooves are two or more grooves substantially parallel to the flow of the liquid sample. The said substantially parallel groove | channel in the said 2nd area | region is 1 mm width or less at intervals of 2 mm or less, and the depth of a groove | channel is 0.05 mm or more and 1 mm or less, The device for optical analysis described. The cross-sectional shape of the substrate in the direction in which the liquid sample flows in the second region has a semicircular shape or a semielliptical shape on the downstream side. Optical analysis device. 12. The optical analysis device according to claim 1, wherein the optical analysis device is a test piece configured to be detachable from an optical analysis apparatus, and the capillary and the chamber are provided on the test piece. The optical analysis device according to any one of the above. 13. An analysis apparatus to which the optical analysis device according to claim 1 is attached, comprising: a rotation drive unit that rotates the analysis device around an axis, and a liquid sample is accommodated in the first chamber. The plasma component of the liquid sample is transferred to the capillary by stopping the rotation of the optical analysis device, and the plasma component of the liquid sample is transferred to the second chamber by rotating again. An optical analysis apparatus using the optical analysis device according to claim 1.