Blood coagulation analyzer and blood coagulation analysis method

Abstract

To suppress increase in the size of the device structure, increase the life of the light source, and restrain generations of an optical axis deviation, in a blood coagulation analyzer applying lights with different wavelengths for blood coagulation analysis.SOLUTION: A light irradiation unit 10 of a blood coagulation analyzer 100 includes: a plurality of light sources 20 including a first light source 21 for generating a first-wavelength light for measuring a blood coagulation time, a second light source 22 for generating a second-wavelength light for measuring a synthetic substrate, and a third light source 23 for generating a third-wavelength light for measuring immune nephelometry; and a plurality of optical fiber units 30 facing the light sources 20, respectively.SELECTED DRAWING: Figure 1

Description

[Technical field]

[0001] The present invention relates to a blood coagulation analyzer and a blood coagulation analysis method. [Background technology]

[0002] Patent Document 1 discloses a blood coagulation analyzer in which a light irradiating unit irradiates a measurement container installed in a container installation unit with light of multiple wavelengths for blood coagulation analysis, and a light receiving unit detects the light transmitted through the measurement container. The light irradiating unit in Patent Document 1 includes a halogen lamp, which is a broadband light source, and a filter unit that holds multiple optical filters with different transmission wavelengths along a circumference. The filter unit is configured to rotate each optical filter around a central axis and sequentially arrange each optical filter in the optical path from the light source. As a result, the light irradiating unit sequentially irradiates light of multiple wavelengths onto the measurement container installed in the container installation unit. The light of multiple wavelengths is used for sample measurement of different measurement items. [Prior art documents] [Patent documents]

[0003] [Patent Document 1] JP 2008-46031 A Summary of the Invention [Problem to be solved by the invention]

[0004] The blood coagulation analyzer of the above-mentioned Patent Document 1 is equipped with a halogen lamp, which is large compared to semiconductor light-emitting elements such as LEDs, and a filter unit equipped with a rotation mechanism, so the device configuration is large. In addition, the light source life of the halogen lamp is short.

[0005] To solve this problem, if multiple LEDs, which have a longer life span than halogen lamps, are simply used and the light from each LED is made incident on an optical fiber coupler via multiple mirrors and dichroic mirrors, precise adjustment of the optical axes to align the optical axes of the multiple light sources is required. Therefore, in a blood coagulation analyzer that irradiates light of multiple wavelengths for blood coagulation analysis, a configuration is desired that prevents the device from becoming large, has a long light source life, and can easily prevent the occurrence of optical axis misalignment.

[0006] The present invention is directed to a blood coagulation analyzer that irradiates light of multiple wavelengths for blood coagulation analysis, which prevents the device configuration from becoming large, has a long light source life, and easily prevents the occurrence of optical axis misalignment. [Means for solving the problem]

[0007] A blood coagulation analyzer according to a first aspect of the present invention comprises a light irradiating unit that irradiates light onto a container containing a measurement sample including a specimen and a reagent, a light receiving unit that receives the light irradiated from the light irradiating unit, and an analysis unit that analyzes the specimen based on an electrical signal output from the light receiving unit. The light irradiating unit comprises a first light irradiating unit including a first light source that emits light of a first wavelength and a first optical fiber unit arranged opposite the first light source, a second light irradiating unit that includes a second light source that emits light of a second wavelength different from the first wavelength and having a weaker light intensity than light of the first wavelength, a light collecting unit arranged corresponding to the second light source, and a second optical fiber unit arranged corresponding to the second light source via the light collecting unit.

[0008] A blood coagulation analysis method according to a second aspect of the present invention includes irradiating light having a first wavelength emitted from a first light source toward an incident end of a first optical fiber unit disposed opposite the first light source, irradiating a specimen with light having the first wavelength emitted from an exit end of the first optical fiber unit, and collecting light having a second wavelength emitted from a second light source having a light intensity weaker than that of the light having the first wavelength. DepartmentThe light is focused at the incident end of the second optical fiber section, thereby increasing the light utilization efficiency, and is then irradiated toward the incident end of the second optical fiber section. The light of the second wavelength that exits from the exit end of the second optical fiber section is irradiated onto a specimen, and the specimen is analyzed using optical signals obtained from the specimen irradiated with the light of the first wavelength and the light of the second wavelength.

[0009] A blood coagulation analysis method according to a third aspect of the present invention includes irradiating light of a first wavelength emitted from a first light source toward an incident end of a first optical fiber unit arranged opposite the first light source, irradiating a specimen with light of the first wavelength emitted from an output end of the first optical fiber unit, irradiating light of a second wavelength emitted from a second light source having a weaker light intensity than the light of the first wavelength toward the incident end of the second optical fiber unit while focusing the light with a focusing lens to increase the light utilization efficiency, irradiating the specimen with light of the second wavelength output from the output end of the second optical fiber unit, and analyzing the specimen using optical signals obtained from the specimen irradiated with the light of the first wavelength and the light of the second wavelength. Effect of the Invention

[0010] According to the present invention, in a blood coagulation analyzer that irradiates light of multiple wavelengths for blood coagulation analysis, the size of the device configuration can be prevented from increasing, the light source life can be extended, and the occurrence of optical axis misalignment can be easily prevented. [Brief description of the drawings]

[0011] [Figure 1] 1 is a schematic diagram showing an overview of a blood coagulation analyzer according to one embodiment. [Diagram 2] FIG. 1 is a schematic plan view for explaining an example of the overall configuration of a blood coagulation analyzer. [Diagram 3] 4 is a schematic cross-sectional view showing a specific configuration example of a light irradiation unit. FIG. [Figure 4] FIG. 4 is a perspective view showing a configuration example of a homogenizing member. [Diagram 5] 1A and 1B are diagrams for explaining characteristics of an optical bandpass filter. [Figure 6] 4 is an enlarged cross-sectional view showing an example of the configuration of a holding portion of a fourth light source in FIG. 3. [Figure 7]4 is an enlarged cross-sectional view showing an example of the configuration of a holder for a fifth light source in FIG. 3. [Figure 8] 13 is a schematic cross-sectional view showing another configuration example of the light irradiation unit. FIG. [Figure 9] 4 is a schematic diagram showing a configuration for guiding light from a light emitting section to a detection unit. FIG. [Figure 10] 4 is an enlarged cross-sectional view showing a configuration example of a container installation part of the detection unit. FIG. [Figure 11] 3 is a block diagram showing an example of the control configuration of the measurement unit shown in FIG. 2. [Figure 12] 5 is a diagram for explaining light emission control of each light source by a control unit. FIG. [Figure 13] FIG. 2 is a diagram showing an example of the configuration of a drive circuit for a light source. [Figure 14] 5 is a diagram for explaining current value control of a light source by a control unit. FIG. [Figure 15] FIG. 2 is a block diagram showing a configuration example of an analysis unit. [Figure 16] FIG. 2 is a conceptual diagram for explaining an analysis process performed by an analysis unit. [Figure 17] 3 is a flowchart for explaining the operation of the blood coagulation analyzer shown in FIG. 2. [Figure 18] FIG. 3 is a diagram for explaining the operation of the blood coagulation analyzer shown in FIG. 2. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0012] Hereinafter, an embodiment will be described with reference to the drawings.

[0013] [Overview of blood coagulation analyzers] As shown in Fig. 1, the blood coagulation analyzer 100 is an apparatus that irradiates a measurement sample prepared by adding a reagent to a specimen with light, detects transmitted light or scattered light of the light irradiated onto the measurement sample, and analyzes the specimen based on the detected light. The specimen is plasma or serum separated from blood. The blood coagulation analyzer 100 analyzes the specimen using a coagulation method, a synthetic substrate method, an immunoturbidimetric method, or an agglutination method.

[0014] The blood coagulation analyzer 100 comprises a light irradiating unit 10 that irradiates light onto a container 15 containing a measurement sample including a specimen and a reagent, a light receiving unit 11 for detecting the light irradiated from the light irradiating unit 10 and transmitted through the container 15, and an analysis unit 12 for analyzing the specimen based on an electrical signal output from the light receiving unit 11.

[0015] The container 15 is a cuvette for containing a measurement sample in which a specimen and a reagent are mixed. The container 15 is formed of a translucent resin or glass, and is preferably sufficiently transparent so as not to affect the irradiated light. The container 15 has, for example, a cylindrical shape with an open top and a closed bottom. In FIG. 1, the container 15 has a cylindrical body 15a that opens upward, and a flange 15b provided at the upper end of the body 15a. The diameter of the lower part of the body 15a is smaller than that of the upper part. The shape of the container 15 is not limited to that shown in the figure.

[0016] The light irradiation unit 10 includes a plurality of light sources 20 and a plurality of optical fiber units 30 provided opposite to each light source 20. The light irradiation unit 10 may further include a holding member 40 for holding each light source 20 and the incident end 31 of each optical fiber unit 30. By providing the holding member 40, each light source 20 and the incident end 31 of each optical fiber unit 30 can be more easily held. Each light source 20 and each incident end 31 may be fixed individually without providing the holding member 40.

[0017] The light source 20 includes a plurality of light sources used in blood coagulation analysis. Specifically, the plurality of light sources 20 includes a first light source 21 for generating light of a first wavelength for blood coagulation time measurement, a second light source 22 for generating light of a second wavelength for synthetic substrate measurement, and a third light source 23 for generating light of a third wavelength for immunoturbidimetric measurement. The plurality of light sources 20 may further include light sources other than the first light source 21, the second light source 22, and the third light source 23.

[0018] The light source 20 generates light of a predetermined wavelength according to the measurement item. For example, light in a wavelength band of 620 nm to 690 nm can be used as the light of the first wavelength generated by the first light source 21. More preferably, light in a wavelength band of 630 nm to 680 nm can be used. The first wavelength is a predetermined wavelength selected suitable for a reagent added to the specimen, and is, for example, 660 nm. In the coagulation method, the measurement sample is irradiated with light of the first wavelength, and the coagulation time required for fibrinogen in the specimen to be converted to fibrin is measured based on an electrical signal of transmitted light or scattered light from the specimen. Measurement items in the coagulation method include PT (prothrombin time), APTT (activated partial thromboplastin time), Fbg (fibrinogen amount), etc.

[0019] The second wavelength light generated by the second light source 22 may be, for example, light in a wavelength band of 390 nm to 420 nm. More preferably, light in a wavelength band of 400 nm to 410 nm may be used. The second wavelength is, for example, 405 nm. In the synthetic substrate method, the measurement sample is irradiated with light of the second wavelength, and the degree of color development due to the action of a chromogenic synthetic substrate on an enzyme in the measurement sample is measured based on an electrical signal of the transmitted light from the sample. Measurement items in the synthetic substrate method include ATIII (antithrombin III), α2-PI (α2-plasmin inhibitor), PLG (plasminogen), etc.

[0020] The third wavelength light generated by the third light source 23 may be, for example, light in a wavelength band of 690 nm to 820 nm. More preferably, light in a wavelength band of 700 nm to 810 nm may be used. The third wavelength is, for example, 800 nm. In the immunoturbidimetric method, a reagent that causes an antigen-antibody reaction with coagulation and fibrinolytic factors in the sample is added to the sample, and the substance contained in the reagent aggregates as a result of the antigen-antibody reaction. The measurement sample is irradiated with light of the third wavelength, and the aggregation rate of the substance containing the reagent in the measurement sample is measured based on the electrical signal of the transmitted light or scattered light from the sample. Measurement items in the immunoturbidimetric method include D-dimer, FDP (fibrin degradation product), etc.

[0021] By providing light sources 20 individually for each measurement item, it is possible to use light sources that generate light in a narrow wavelength band centered on the wavelength used for measurement, rather than broadband light sources that cover a wide wavelength band, such as halogen lamps. For example, the first light source 21 can be a light source that includes the first wavelength and hardly includes the second and third wavelengths. Therefore, as the light source 20, a relatively narrowband light source with the wavelength used for measurement as the center wavelength can be used, and for example, a semiconductor light emitting element such as an LED (light emitting diode) or a semiconductor laser can be used.

[0022] The optical fiber section 30 has a cable-like structure including an incident end 31 and an exit end 32. The optical fiber section 30 has a function of guiding light irradiated to the incident end 31 to the exit end 32. The optical fiber section 30 is composed of one or more optical fibers.

[0023] The optical fiber sections 30 are provided corresponding to the respective light sources 20. That is, one optical fiber section 30 is provided for each light source 20. In the configuration example of Fig. 1, the optical fiber section 30 includes an optical fiber section 30a corresponding to the first light source 21, an optical fiber section 30b corresponding to the second light source 22, and an optical fiber section 30c corresponding to the third light source 23. When the light source 20 includes a light source other than the first light source 21 to the third light source 23, an optical fiber section corresponding to that light source is provided separately.

[0024] In the configuration further including the holding member 40, the holding member 40 has a function of holding the light source 20 and the incident end 31 of the optical fiber section 30 to maintain their relative positional relationship. The holding member 40 includes, for example, a plurality of light source holding sections 41 that hold the light sources 20, and a plurality of incident end holding sections 42 that are provided at positions facing the light sources 20 held by the light source holding sections 41 and hold the incident end 31 of the optical fiber section 30. As a result, the holding member 40 holds the light sources 20 and the incident end 31 of the optical fiber section 30 so as to face each other. The light source holding section 41 and the incident end holding section 42 are provided for each pair of one light source 20 and the incident end 31 of the optical fiber section 30 corresponding to that light source 20. The light source holding section 41 and the incident end holding section 42 hold the light source 20 and the incident end 31 of the corresponding optical fiber section 30 in positions close to each other. The holding member 40 holds the light source 20 in a state in which the optical axis of the light source 20 and the central axis of the optical fiber section 30 are approximately aligned. Instead of providing the holding member 40, a light source holding portion 41 and an incident end holding portion 42 may be provided individually for each pair of a light source 20 and an incident end 31.

[0025] The light receiving unit 11 includes a photoelectric conversion element that converts the received light into an electrical signal and outputs it. The blood coagulation analyzer 100 may include an amplifier circuit that amplifies the electrical signal output from the photoelectric conversion element of the light receiving unit 11. The light receiving unit 11 has a function of outputting an electrical signal according to the amount of received light to the analysis unit 12. For example, the light receiving unit 11 is disposed so as to face the output end 32 of the optical fiber unit 30. By disposing a container 15 containing a measurement sample between the light receiving unit 11 and the output end 32, the light receiving unit 11 detects light irradiated from the light irradiating unit 10 and transmitted through the container 15. The light transmitted through the container 15 is transmitted light or scattered light due to the light irradiated to the measurement sample. The transmitted light or scattered light of the light irradiated to the sample is transmitted through the container 15 and received by the light receiving unit 11. The light receiving unit 11 may be configured to receive both transmitted light and scattered light.

[0026] 1 shows a configuration example in which the light emitted from the emission end 32 of the optical fiber unit 30 is directly irradiated onto the container 15 and transmitted through the container 15 before being received by the light receiving unit 11, but other optical elements may be provided between the emission end 32 of the optical fiber unit 30 and the light receiving unit 11. For example, when irradiating light onto a plurality of containers 15, an optical element may be provided for distributing the light from the emission end 32 of the optical fiber unit 30 to each container 15. In addition, a lens or an optical filter having a predetermined optical characteristic may be disposed immediately before the container 15 or between the container 15 and the light receiving unit 11.

[0027] The analysis unit 12 is composed of a computer equipped with a processor, a memory, and the like. The analysis unit 12 may be configured as an analysis unit by making a general-purpose computer execute a program for sample analysis, or may be configured by dedicated hardware. The analysis unit 12 records data of the electrical signal output from the light receiving unit 11, and performs analysis of the sample according to the measurement item. The change in the electrical signal output from the light receiving unit 11 represents the change in the amount of light received by the light receiving unit 11. In the measurement using the above-mentioned first light source 21 to third light source 23, the analysis unit 12 can analyze the sample based on the change in the electrical signal output from the light receiving unit 11 during a predetermined measurement time. In the case of the coagulation method, the analysis unit 12 analyzes the blood coagulation time, in the case of the synthetic substrate method, the analysis unit 12 analyzes the absorbance change during the process in which the chromogenic synthetic substrate develops color, and in the case of the immunoturbidimetric method, the analysis unit 12 analyzes the absorbance change due to the antigen-antibody reaction of the reagent. Even when performing analysis by other measurement methods, the analysis unit 12 performs sample analysis from the electrical signal according to the measurement method.

[0028] Next, an analysis method using the blood coagulation analyzer 100 will be described. The blood coagulation analyzer 100 generates light from a plurality of light sources 20 held by a plurality of holding units 40. The blood coagulation analyzer 100 causes light from the plurality of light sources 20 to enter the input ends 31 of a plurality of optical fiber units 30 held by a plurality of holding units 40, respectively. The blood coagulation analyzer 100 then irradiates the light emitted from each output end 32 of the plurality of optical fiber units 30 onto a container 15 containing a specimen, and detects the light transmitted through the container 15. The blood coagulation analyzer 100 analyzes the specimen based on the detected light.

[0029] With the above configuration, the blood coagulation analyzer 100 is provided with a plurality of light sources 20 and a plurality of optical fiber units 30 corresponding to the plurality of light sources 20, and thus blood coagulation analysis can be performed by using a plurality of small, long-life light sources 20 such as LEDs, rather than a combination of a wideband light source such as a halogen lamp and a rotary filter device. This makes it possible to extend the life of the light source compared to a halogen lamp, and to suppress the increase in size of the device configuration. Furthermore, unlike a configuration in which a mirror is placed in the optical path from the light source 20 to guide light to the container 15, the light source 20 and the incident end 31 of the optical fiber unit 30 are opposed to each other, and can be held in positions close to each other by the light source holding unit 41 and the incident end holding unit 42 of the holding member 40, so that the optical axis can be aligned easily and accurately. As a result, in the blood coagulation analyzer 100 that irradiates light of a plurality of wavelengths for blood coagulation analysis, the device configuration can be suppressed from becoming large, the light source life can be long, and the occurrence of optical axis misalignment can be easily suppressed.

[0030] In addition, since the light source 20 and the incident end 31 of the optical fiber unit 30 can be held in positions close to each other, the amount of light lost from the light source 20 until the light is incident on the optical fiber unit 30 can be reduced. This reduces the influence of noise mixed into the electrical signal output from the light receiving unit 11, and a highly reproducible blood coagulation analysis result can be obtained. For example, when the coagulation time is calculated by the percentage detection method as the blood coagulation analysis result, if the influence of noise mixed into the electrical signal output from the light receiving unit 11 is large, even if the same sample is measured multiple times, a different coagulation time may be calculated for each measurement. On the other hand, since the light source 20 and the incident end 31 of the optical fiber unit 30 can be held in positions close to each other, the influence of noise mixed into the electrical signal output from the light receiving unit 11 can be suppressed in the blood coagulation analyzer 100. Therefore, for example, when the coagulation time is calculated by the percentage detection method as the blood coagulation analysis result, a highly reproducible coagulation time can be obtained.

[0031] [Example of blood coagulation analyzer configuration] Hereinafter, a more specific configuration example of the blood coagulation analyzer 100 shown in Fig. 1 will be described with reference to Fig. 2 onwards. Fig. 2 shows one configuration example of an automatic analyzer for blood coagulation analysis.

[0032] (Overall composition) 2, the blood coagulation analyzer 100 includes a measurement section 101, a transport section 102, and an analysis section 12. The light irradiating section 10 and the light receiving section 11 (see FIG. 9) are provided in the measurement section 101.

[0033] In the configuration example of FIG. 2, the blood coagulation analyzer 100 has a function of aspirating a sample from a sample container that contains the sample, and dispensing a fixed amount of the sample into a container 15.

[0034] A sample rack 105 is installed in the transport unit 102. A plurality of sample containers 106 containing samples can be installed in the sample rack 105. The transport unit 102 transports the sample rack 105 installed by the user and positions each sample container 106 at a predetermined sample aspiration position 501 or 502. A label (not shown) on which identification information is recorded in a barcode or the like is attached to the sample rack 105 and the sample container 106. The identification information of the sample rack 105 and the sample container 106 is read by a reader 103 installed midway along the transport path and transmitted to the analysis unit 12. The samples in the sample containers 106 are associated with the measurement results of the samples and managed by the identification information.

[0035] The measurement section 101 is equipped with sample dispensing sections 110 and 120 for aspirating the sample from the sample container 106 and dispensing a fixed amount into the container 15 .

[0036] The specimen dispensing units 110 and 120 are each composed of a dispensing arm that rotatably holds a pipette 111 for dispensing specimens. The pipette 111 is connected to a pump (not shown) and can aspirate and discharge a fixed amount of specimen. The specimen dispensing unit 110 can move the pipette 111 to aspirate a predetermined amount of specimen from a specimen container 106 at a specimen aspirating position 501. The specimen dispensing unit 120 can move the pipette 111 to aspirate a predetermined amount of specimen from a specimen container 106 at a specimen aspirating position 502. The specimen dispensing units 110 and 120 can each move the pipette 111 to discharge the aspirated specimen into a container 15 arranged at a predetermined specimen dispensing position.

[0037] The measurement unit 101 performs optical measurement on a measurement sample prepared by adding a predetermined reagent to a sample aspirated by the sample dispensing unit 110. The blood coagulation analyzer 100 may be configured not to include the transport unit 102 and the sample dispensing unit 110, but to perform measurement on a container 15 into which a fixed amount of sample has been dispensed in advance.

[0038] The measurement unit 101 includes a mechanism for transporting, to each unit, a container 15 that contains a specimen and a reagent and in which a measurement sample is prepared. In the configuration example of FIG. 2, the measurement unit 101 includes a container table 130. The container table 130 has a ring shape in a plan view and can rotate in a circumferential direction. The container table 130 includes a plurality of holding holes 131 arranged along the circumferential direction. Each of the holding holes 131 can accommodate a container 15. The specimen dispensing unit 110 can dispense the aspirated specimen into a new container 15 held on the container table 130 at the specimen dispensing position 503. The specimen dispensing unit 120 can also aspirate a specimen from a container 15 that contains a specimen on the container table 130.

[0039] The measurement unit 101 is equipped with a transport unit 140 that positions a new container 15 at a specimen dispensing position 504. The transport unit 140 can move a mounting table having holding holes for mounting the container 15 along a rail. For example, two holding holes are provided. The specimen dispensing unit 120 can dispense the aspirated specimen into the new container 15 held by the transport unit 140 at the specimen dispensing position 504.

[0040] A large number of new containers 15 are stored in the container storage section 150, and are taken out one by one from the container storage section 150 by the container supply section 151. The containers 15 taken out by the container supply section 151 are gripped and taken out by the gripping mechanism 160. The gripping mechanism 160 can place the taken out containers 15 in the holding holes 131 of the container table 130 or the holding holes of the transfer section 140.

[0041] The measurement section 101 is equipped with a transport section 170. The transport section 170 can move an installation stand having a holding hole, like the transport section 140, along a rail. A new container 15 from the container supply section 151 is taken out by the gripping mechanism 180 and installed in the holding hole of the transport section 170. The transport section 170 can transport the installed new container 15 to a specimen dispensing position 505. The specimen dispensing section 120 can dispense the aspirated specimen into the new container 15 held by the transport section 170 at the specimen dispensing position 505.

[0042] 2, the blood coagulation analyzer 100 has a function of preparing a measurement sample by adding a reagent to the specimen in the container 15. The measurement sample is a mixture of the specimen and the reagent.

[0043] The measurement section 101 includes a reagent table 190 that accommodates a reagent container 191 used in the measurement, and reagent dispensing sections 200 and 210 for aspirating and dispensing reagent from the reagent containers placed on the reagent table 190.

[0044] The reagent table 190 is disposed inside the container table 130, and has a circular shape in a plan view. A plurality of reagent containers 191 can be placed in the circumferential direction on the reagent table 190. The reagent table 190 can rotate in the circumferential direction, and any reagent container 191 can be positioned at a predetermined reagent aspirating position by the rotation.

[0045] The reagent dispensing units 200 and 210 are equipped with a pipette (not shown) for dispensing reagent. The pipette is connected to a pump (not shown) and can aspirate and dispense a fixed amount of reagent. The reagent dispensing unit 200 can aspirate a predetermined amount of reagent from a reagent container 191 positioned at a predetermined reagent aspirating position on the reagent table 190. The reagent dispensing unit 200 can move the pipette to a reagent dispensing position 506 and dispense a predetermined amount of reagent into a container 15 at the reagent dispensing position 506.

[0046] The reagent dispensing unit 210 can aspirate a predetermined amount of reagent from a reagent container 191 at a reagent suction position that is positioned at a predetermined reagent suction position on the reagent table 190. The reagent dispensing unit 210 can move a pipette to a reagent dispensing position 507 and dispense a predetermined amount of reagent into a container 15 at the reagent dispensing position 507.

[0047] The measurement section 101 includes a heating table 220 for holding and heating the containers 15 into which the specimen has been dispensed. The heating table 220 includes a plurality of holding holes 221 for holding the plurality of containers 15 each containing a specimen, and a gripping mechanism 222 for gripping and transporting the containers 15. The heating table 220 includes a built-in heater (not shown) for heating the containers 15 held in the plurality of holding holes 221.

[0048] The heating table 220 has a circular shape in a plan view, and a plurality of holding holes 221 are arranged along the circumferential direction. The heating table 220 is rotatable in the circumferential direction, and can transfer the containers 15 placed in the plurality of holding holes 221 in the circumferential direction by rotation while being heated to a predetermined temperature by a heater. The gripping mechanism 222 can grip and transfer the containers 15, place the containers 15 in the holding holes 221, and remove the containers 15 from the holding holes 221.

[0049] The gripping mechanism 222 can transport the container 15 placed in the transport section 140 to the holding hole 221 of the heating table 220. The gripping mechanism 222 can also take out the container 15 that has been heated in the holding hole 221 of the heating table 220 and transport it to each of the reagent dispensing positions 506 and 507. The gripping mechanism 222 returns the container 15 into which the reagent has been dispensed by the reagent dispensing section 200 to the holding hole 221 of the heating table 220.

[0050] The blood coagulation analyzer 100 may be configured not to include the reagent table 190, the reagent dispensing section 200, and the heating table 220, and to perform measurements on containers 15 that already contain prepared measurement samples.

[0051] The measurement section 101 includes detection units 230 and 240 for performing optical measurement of the measurement sample in the container 15. The two detection units 230 and 240 have the same configuration. Only one of the detection units 230 and 240 may be provided. The detection units 230 and 240 include a container installation section 231 for installing the container 15 containing the specimen, and a light receiving section 11 provided corresponding to the container installation section 231.

[0052] 2, each of the detection units 230 and 240 includes a plurality of container installation parts 231. The detection units 230 and 240 extend linearly along one side of the blood coagulation analyzer 100 in a plan view, and the plurality of container installation parts 231 are linearly arranged at predetermined intervals.

[0053] The measurement section 101 includes gripping mechanisms 180 and 250 for transferring the container 15 to the detection units 230 and 240, respectively.

[0054] The gripping mechanisms 180 and 250 are provided with a moving mechanism (not shown) in each of the three orthogonal axial directions, X, Y, and Z, and can grip and transport the container 15. The gripping mechanism 180 can transport the container 15 between the container supply unit 151 and the transport unit 170 described above. The gripping mechanism 180 can take out the container 15 from the holding hole 221 of the heating table 220, transport it to the reagent dispensing position 506, and install the container 15 after the reagent has been dispensed in the container installation unit 231 of the detection unit 230. The gripping mechanism 250 can take out the container 15 from the holding hole 221 of the heating table 220, transport it to the reagent dispensing position 507, and install the container 15 after the reagent has been dispensed in the container installation unit 231 of the detection unit 240. The gripping mechanisms 180 and 250 can take out the measured container 15 from the container installation unit 231 and transport it to the respective waste outlets 260 and 261.

[0055] Optical measurement is performed on the measurement sample in the container 15 placed in the container placement section 231 of the detection units 230 and 240. The light irradiating section 10 irradiates the container 15 placed in the container placement section 231 of the detection units 230 and 240 with light for measurement. The light receiving section 11 (see FIG. 9) receives transmitted light or scattered light of the light irradiated to the container 15, and outputs an electrical signal according to the amount of light received. The electrical signal is transmitted to the analysis section 12. The analysis section 12 analyzes the sample based on the electrical signal output from the light receiving section 11.

[0056] (Example of the configuration of the light irradiation unit) Fig. 3 shows a configuration example of the light irradiation unit 10. In the configuration example of Fig. 3, the light irradiation unit 10 includes five light sources 320, five optical fiber units 330 provided corresponding to the five light sources 320, and one holding member 340 for holding each light source 320 and an incident end 331 of each optical fiber unit 330. The light sources 320, the optical fiber units 330, and the holding member 340 are accommodated in a housing 310 made of, for example, a metal.

[0057] All five light sources 320 are composed of LEDs. LEDs generally have a lifespan several tens of times longer than that of halogen lamps. This makes it possible to configure a light irradiation unit 10 that is smaller in size and has a longer lifespan than a configuration using a wideband light source such as a halogen lamp and a rotary filter. In addition, since an individual LED can be provided for each wavelength, the emission spectrum and emission intensity of each light source 320 can be individually optimized.

[0058] The light source 320 includes a first light source 321, a second light source 322, and a third light source 323. In the configuration example of Fig. 3, the first light source 321 is a light source for blood coagulation time measurement that generates light of about 660 nm as a first wavelength. The second light source 322 is a light source for synthetic substrate measurement that generates light of about 405 nm as a second wavelength. The third light source 323 is a light source for immunoturbidimetric measurement that generates light of about 800 nm as a third wavelength.

[0059] In the configuration example of FIG. 3, the multiple light sources 320 further include a fourth light source 324 for generating light of a fourth wavelength different from the second wavelength for synthetic substrate measurement. The fourth wavelength is a wavelength selected from the range of 300 nm to 380 nm, similar to the second wavelength. More preferably, light of a wavelength band of 320 nm to 360 nm can be used. In the configuration example of FIG. 3, the fourth wavelength is, for example, 340 nm. The light of the fourth wavelength can be used as a sub-wavelength for synthetic substrate measurement. That is, an analysis can be performed by adopting a signal that provides a more stable detection result compared to an electrical signal corresponding to the light of the second wavelength and an electrical signal corresponding to the light of the fourth wavelength. This allows analysis using a more reliable electrical signal, and even in this case, the size of the device configuration can be suppressed.

[0060] In the configuration example of FIG. 3, the multiple light sources 320 further include a fifth light source 325 for generating light of a fifth wavelength different from the third wavelength for immunoturbidimetric measurement. The fifth wavelength is a wavelength selected from the range of 550 nm to 590 nm, similar to the third wavelength. More preferably, light of a wavelength band of 560 nm to 580 nm can be used. In the configuration example of FIG. 3, the fifth wavelength is, for example, 575 nm. The light of the fifth wavelength can be used as a sub-wavelength for immunoturbidimetric measurement. That is, an analysis can be performed by adopting a signal that provides a more stable detection result compared to an electrical signal corresponding to the light of the third wavelength and an electrical signal corresponding to the light of the fifth wavelength. This allows analysis using an electrical signal with higher reliability, and even in this case, the size of the device configuration can be suppressed.

[0061] The optical fiber units 330 are provided corresponding to the respective light sources 320. The five optical fiber units 330 are composed of optical fiber units 330a, 330b, 330c, 330d, and 330e provided individually for each light source 320 so that light from a first light source 321, a second light source 322, a third light source 323, a fourth light source 324, and a fifth light source 325 enters from the respective entrance ends 331.

[0062] In the configuration example of FIG. 3, each of the optical fiber units 330 includes a plurality of optical fibers 333. The optical fiber units 330 are mixed and bundled together so that the optical fibers 333 corresponding to each light source 320 are distributed approximately uniformly at the output end 332. Here, the term "optical fiber" refers to an optical fiber strand or optical fiber core having one core. Each optical fiber unit 330 is configured as a cable or twisted wire in which a plurality of strands are bundled together. With this configuration, the light of each wavelength separately incident on the input end 331 of each optical fiber unit 330 can be output from a common output end 332 instead of being individually irradiated onto the container 15. Therefore, the configuration for outputting the light of each wavelength can be simplified. In addition, since the light of each wavelength can be output in a state in which the distribution of the light of each wavelength is uniform at the common output end 332, even when the light of each wavelength is output from the common output end 332, the distribution of the light of each wavelength can be prevented from being biased.

[0063] In the configuration example of FIG. 3, five optical fiber parts 330 are twisted together and integrated in the middle, and are configured to have two emission ends 332. The two emission ends 332 are provided to correspond to the two detection units 230 and 240 (see FIG. 2), respectively. The two emission ends 332 are connected to the two outlets 311 provided in the housing 310, respectively. Each emission end 332 includes an approximately equal number of optical fibers 333 constituting each optical fiber part 330. In addition, the optical fibers 333 constituting each optical fiber part 330 are mixed so as to be approximately uniformly distributed within the end face of the emission end 332. The number of optical fibers 333 constituting each optical fiber part 330 is determined according to the number of container installation parts 231 in the detection units 230 and 240. For example, if the number of container installation parts 231 is N and each optical fiber part 330 transmits an amount of light equivalent to M optical fibers to one container installation part 231, each optical fiber part 330 includes N×M optical fibers 333. Each emission end 332 is configured by collecting (N×M) / 2 optical fibers 333 from each optical fiber part 330.

[0064] <Homogenizing member> In the configuration example of FIG. 3, the light irradiation unit 10 further includes a homogenizing member 350 that is disposed adjacent to the exit end 332 of the optical fiber unit 330 and homogenizes the intensity distribution of the light incident from the exit end 332 side and emits the light. Here, each optical fiber 333 disposed at the exit end 332 emits only light of any one of the first wavelength to the fifth wavelength. That is, at the exit end 332, the light emission points for each wavelength are uniformly distributed and disposed. Therefore, by homogenizing the light from the exit end 332 by making it enter the homogenizing member 350, the intensity distribution of each wavelength is homogenized over the entire surface at the exit surface 352 of the homogenizing member 350. This makes it possible to effectively homogenize the variation in light intensity for each wavelength.

[0065] The homogenizing members 350 are disposed at two outlets 311 provided in the housing 310. The incident surface 351 of each homogenizing member 350 faces the corresponding output end 332 of the optical fiber section 330, and the output surface 352 is disposed on the output side of the outlet 311. As a result, light having a homogenized intensity distribution that passes through the homogenizing member 350 is emitted from each outlet 311. The homogenizing member 350 is configured, for example, to cause multiple reflections of the light incident from the incident surface 351 inside and emit the light from the output surface 352. As an example of the homogenizing member 350, FIG. 6 shows a light pipe 353 made of a homogenizer rod in the shape of a polygonal column. The light pipe 353 causes multiple reflections of the incident light inside, thereby emitting light of each wavelength with a uniform intensity distribution from the output surface 352. If the intensity distribution of light of each wavelength is sufficiently uniformed at the emission end 332 of the optical fiber section 330, the uniformizing member 350 does not need to be provided.

[0066] <Retaining member> Returning to FIG. 3, the holding member 340 of the light irradiation unit 10 holds five light sources 320. Therefore, the five light sources 320 are supported by a common holding member 340. The holding member 340 is made of a metal such as aluminum, and is formed in a prismatic shape. In the configuration example of FIG. 3, the light source holding part 341 and the incident end holding part 342 are provided at one end and the other end of the holding member 340, respectively, and are connected to each other by a passage part 344 formed of a through hole penetrating the holding member 340.

[0067] The five light source holding parts 341 are arranged in a straight line along a direction perpendicular to the light emission direction of each light source 320. In each light source 320, a fourth light source 324 is arranged in the center, a fifth light source 325 and a second light source 322 are arranged on both sides of the fourth light source 324, and a first light source 321 and a third light source 323 are arranged on the outermost sides.

[0068] In the configuration example of Fig. 3, a plurality of light source holding parts 341 that hold the light sources 320 and a plurality of incident end holding parts 342 that hold the incident ends 331 of the plurality of optical fiber parts 330 are arranged at positions facing each other linearly in the holding member 340. This makes it possible to easily and accurately align the optical axis of the light source 320 with the axial center of the optical fiber part 330 at the incident end 331. In Fig. 3, the light source holding part 341 and the incident end holding part 342 are arranged at positions facing each other on approximately the same axis line.

[0069] In the configuration example of FIG. 3, as shown in detail in FIG. 6 and FIG. 7, the light source holding part 341 holds the light source 320 via the socket 343. The light source holding part 341 includes a recess 345 connected to the passage part 344, and the socket 343 is a cylindrical member fitted into the recess 345. The light source 320 is fixedly held inside the socket 343. The incident end holding part 342 is formed by the other end part of the passage part 344 which is a through hole penetrating the holding member 340. Therefore, the incident end holding part 342 is a hole part into which the incident end 331 can be inserted, and holds a predetermined length range including the incident end 331 of the optical fiber part 330 inserted therein.

[0070] The light irradiation section 10 may be provided with a member for focusing the light from the light source 320 onto the incident end 331 of the optical fiber section 330, and a member for adjusting the spectral characteristics such as the central wavelength and half-width of the light incident on the incident end 331.

[0071] Optical Bandpass Filter For example, in FIG. 3, the light irradiation unit 10 further includes an optical bandpass filter 360 that transmits only light of a predetermined wavelength band. The optical bandpass filter 360 has a disk-like shape, and transmits only light of a predetermined wavelength band out of the light irradiated to one surface to the other surface. The holding member 340 holds the optical bandpass filter 360 at a position between the light source 320 and the incident end 331 of the corresponding optical fiber unit 330. This allows the central wavelength, half-width, etc. of the light emitted from the light source 320 to be adjusted to have characteristics suitable for measurement, and the light can be incident on the incident end 331. As a result, the measurement accuracy is improved. In addition, there are individual differences in the light source 320, and the central wavelength, half-width, etc. may differ, but the optical bandpass filter 360 absorbs the influence of the individual differences of the light source 320, and a stable measurement result can be ensured.

[0072] Specifically, as shown in FIG. 5, it is assumed that the fifth light source 325 that generates light of the fifth wavelength of, for example, 575 nm emits light with a spectrum SP1 having a center wavelength λ1 slightly shifted from 575 nm and a half-width HW1. The light of the fifth light source 325 passes through the optical bandpass filter 360, and becomes a spectrum SP2 that matches the fifth wavelength of 575 nm and has a sufficiently narrow half-width HW2, and enters the optical fiber unit 330. In FIG. 5, the vertical axis represents relative intensity [%]. That is, the maximum intensity of each of the spectra SP1 and SP2 is set to 100%, and the respective intensity distributions are shown. The maximum intensity (100%) of the spectrum SP1 in FIG. 5 does not coincide with the maximum intensity (100%) of the spectrum SP2, and the absolute values ​​of the light intensity are different.

[0073] 3, the optical bandpass filters 360 are provided for all of the five light sources 320. The characteristics of each optical bandpass filter 360 differ depending on the light source 320.

[0074] 6 and 7, the holding member 340 includes a linear passage portion 344 for arranging the light source 320, the optical bandpass filter 360, and the incident end 331 of the optical fiber portion 330 corresponding to the light source 320 in a linear arrangement, and the optical bandpass filter 360 is arranged so as to block the passage portion 344 between the light source 320 and the incident end 331. This allows the light from the light source 320 to reliably pass through the optical bandpass filter 360 and enter the incident end 331. As a result, even when the optical bandpass filter 360 is provided, the occurrence of light loss can be suppressed.

[0075] Specifically, the passage 344 is a hole extending linearly in the holding member 340 along the optical axis of the light source 320. The light source holding portion 341 includes a recess 345 formed to have an inner diameter larger than that of the passage 344. The optical bandpass filter 360 is disposed at the end of the recess 345 on the side of the incident end holding portion 342. The optical bandpass filter 360 is pressed against the bottom surface of the recess 345 via a ring-shaped elastic member 346 by the tip surface of the socket 343. Thus, the optical bandpass filter 360 is disposed so as to block the passage 344 in which the incident end 331 is disposed. The optical bandpass filter 360 is fixed by the elastic member 346 while being pressed with an appropriate external force that does not cause damage.

[0076] Condenser lens 6 and 7, the light irradiation unit 10 further includes a condenser lens 370 that is provided corresponding to at least one of the multiple light sources 320 and that converges the light emitted from the light source 320 to the incident end 331. The holding member 340 holds the condenser lens 370 at a position between the light source 320 and the incident end 331 of the corresponding optical fiber unit 330. This improves the efficiency of use of the light generated by the light source 320, so that sufficient light intensity can be ensured without increasing the amount of light emitted by the light source 320 or the current value supplied to the light source 320.

[0077] The condenser lens 370 may be provided for all the five light sources 320, but is not necessarily required to be provided when sufficient light intensity can be obtained at a predetermined current value equal to or less than the rated current. It is effective to provide the condenser lens 370 for light sources having relatively low light intensity among the light sources 320. In the case of LED light sources, the amount of light emitted by the LED light sources of 340 nm and 575 nm is small among 660 nm, 405 nm, 800 nm, 340 nm, and 575 nm. Therefore, the condenser lens 370 is provided for the fourth light source 324 (see FIG. 6) and the fifth light source (see FIG. 7) among the five light sources 320 shown in FIG. 3, but is not provided for the first light source 321, the second light source 322, and the third light source 323.

[0078] 6 and 7, the holding member 340 includes a linear passage portion 347 for arranging the light source 320, the condenser lens 370, and the incident end 331 of the optical fiber portion 330 corresponding to the light source 320 in a linear arrangement, and the condenser lens 370 is arranged so as to close the passage portion 347 between the light source 320 and the incident end 331. This makes it possible to easily align the axes of the light source 320, the condenser lens 370, and the incident end 331 of the optical fiber portion 330, and effectively increase the light utilization efficiency.

[0079] Specifically, the socket 343 has a linear passage portion 347 between the light source 320 and the incident end 331 of the optical fiber portion 330. The condenser lens 370 is fitted into the passage portion 347 and held by the socket 343 so as to block the passage portion 347. In the configuration examples of FIGS. 6 and 7, an example is shown in which two condenser lenses 370 are provided linearly side by side. The light from the light source 320 is converged twice by the two condenser lenses 370 and then incident on the incident end 331. As a result, without increasing the distance between the light source 320 and the incident end 331, the emitted light from a wider range of the light source 320 can be incident on the incident end 331. In addition, in order to transmit light by the optical fiber portion 330, it is necessary to make the light incident on the incident end 331 at an incident angle θ that satisfies a predetermined total reflection condition. The condenser lens 370 is configured to condense light so that the light from the light source 320 is incident on the incident end 331 within the range of the incident angle θ. Only one condenser lens 370 may be provided.

[0080] 〈Positional relationship of each part〉 Returning to FIG. 3, the plurality of light source holding portions 341 are arranged side by side at intervals from each other. In the configuration example of FIG. 3, the plurality of light source holding portions 341 are provided so as to be linearly arranged at substantially equal intervals on the holding member 340. By each light source holding portion 341, the plurality of light sources 320 are arranged side by side at intervals from each other. Also, in the configuration example of FIG. 3, the first distance D1 between at least some of the light sources 320 and the incident end 331 of the optical fiber portion 330 is smaller than the second distance D2 between adjacent light sources 320. As a result, since the light source 320 and the incident end 331 of the optical fiber portion 330 can be arranged at positions in the vicinity where they are separated by the first distance D1, the optical axis adjustment between the light source 320 and the incident end 331 can be easily performed.

[0081] In addition, in the configuration example of FIG. 3, for the first light source 321, the second light source 322, and the third light source 323, the first distance D1 is smaller than the second distance D2. For the fourth light source 324 and the fifth light source 325 provided with the condenser lens 370, the first distance D3 is larger than D1. Each distance has a relationship of D1 < D3 < D2.

[0082] In the configuration example of FIG. 3, the optical fiber units 330 are gathered and bundled along the optical fiber unit 330d corresponding to the fourth light source 324, and the optical fiber unit 330d corresponding to the fourth light source 324 is configured to have the shortest length from the input end 331 to the output end 332 among the optical fiber units 330. Here, among the light sources 320, the fourth light source 324 configured as a 340 nm LED light source has the smallest light emission amount. Therefore, with this configuration, the path length of the optical fiber unit 330d corresponding to the fourth light source 324 with the smallest light emission amount is the shortest, so that the optical loss when passing through the optical fiber unit 330 can be reduced accordingly. As a result, it is possible to secure a larger amount of light from the fourth light source 324 with the smallest light emission amount.

[0083] The length from the incident end 331 to the exit end 332 becomes longer as the path length for collecting light along the optical fiber portion 330d becomes longer, and therefore becomes longer the farther away from the central fourth light source 324. Therefore, in the case of the configuration example of Fig. 3, the relationship of the length from the incident end 331 to the exit end 332 of each optical fiber portion 330 is optical fiber portion 330d<330e, 330b<330a, 330c.

[0084] (Another configuration example of the light irradiation unit) FIG. 8 shows another example of the configuration of the light irradiation unit. In the light irradiation unit 10A according to the example of FIG. 8, one outlet 311 is provided in the housing 310. The arrangement of the multiple light sources 320 is the same as that of the example of FIG. 3, but the arrangement positions may be different. The five optical fiber units 330 are held by the holding member 340 at positions where the respective entrance ends 331 face the respective light sources 320, and are twisted together midway to form an integrated unit, so as to have one exit end 332. The twisted and integrated part is housed in a cylindrical holding member 313. At the exit end 332, the optical fibers constituting each optical fiber unit 330 are mixed so as to be distributed approximately uniformly within the end face of the exit end 332.

[0085] The length from the incident end 331 to the exit end 332 is the shortest for the central optical fiber portion 330d corresponding to the fourth light source 324, and increases with increasing distance from the optical fiber portion 330d. Therefore, even in the configuration example of Fig. 8, the relationship in length from the incident end 331 to the exit end 332 of each optical fiber portion 330 is optical fiber portion 330d<330e, 330b<330a, 330c.

[0086] (Light distribution member and detection unit) Next, a description will be given of the configuration for guiding light from the light irradiation section 10 to each of the detection units 230 and 240, and the configuration of the detection unit 230 (240). As described above, the detection units 230 and 240 have the same configuration.

[0087] In the configuration example of FIG. 9, the light irradiation unit 10 includes a light distribution member 380 for distributing light from the bundled emission ends 332 to each of the multiple container installation parts 231. A plurality of light receiving units 11 are provided corresponding to the multiple container installation parts 231 so as to detect the light distributed to each container installation part 231 by the light distribution member 380. This makes it possible to install multiple containers 15 in the multiple container installation parts 231 and perform measurements collectively. In addition, since the light of each wavelength from the first wavelength to the fifth wavelength is uniformly distributed at the emission end 332, light of each wavelength with uniform intensity can be supplied to each container installation part 231 simply by distributing the light from the emission end 332 by the light distribution member 380. As a result, light of uniform intensity can be easily irradiated to each container 15 without providing a light source 320 for each of the multiple container installation parts 231.

[0088] Two light distribution members 380 are provided corresponding to the two detection units 230 and 240. In the configuration example of FIG. 9, each of the detection units 230 and 240 includes twelve container installation parts 231 and one reference light measurement part 232. A total of twelve light receiving parts 11 are provided in each of these container installation parts 231. In addition, the reference light measurement part 232 includes a reference light receiving part 236 that is provided separately from the light receiving part 11 and receives light from the light irradiating part 10 without transmitting the light through the container 15. Each light distribution member 380 distributes light to each of the container installation parts 231 and the reference light measurement part 232 of the respective detection units 230 and 240.

[0089] The light distribution member 380 is, for example, composed of a bundle of multiple optical fibers similar to the optical fiber unit 330. The incident end 381 of each light distribution member 380 is connected to the outlet 311 provided in the housing 310 of the light irradiation unit 10, and is arranged to face the exit surface 352 of the homogenizing member 350. As a result, the light of the first wavelength to the fifth wavelength is incident with homogenized light intensity on each optical fiber constituting the incident end 381 of the light distribution member 380. The exit end 382 of the light distribution member 380 is divided into the total number of the container installation units 231 and the reference light measurement units 232, and is connected to each of the container installation units 231 and the reference light measurement units 232. That is, in the configuration example of FIG. 9, each light distribution member 380 has an exit end 382 branched into 13.

[0090] A configuration example of each container installation section 231 is shown in FIG. 10. In the configuration example of FIG. 10, the detection units 230 and 240 include the container installation section 231 as a hole extending in the vertical direction, and the emission end 382 of the light distribution member 380 is arranged in a hole 233 extending laterally from the container installation section 231. A condenser lens 234 is arranged inside the hole 233. The light receiving section 11 is provided at the end of a hole 235 formed to face the hole 233 across the container installation section 231. As a result, the emission end 382 of the light distribution member 380, the condenser lens 234, the container installation section 231, and the light receiving section 11 are arranged in a straight line. The light emitted from the emission end 382 passes through the condenser lens 234, passes through the container 15 in the container installation section 231 and the measurement sample in the container 15, and is detected by the light receiving section 11. The measurement sample is a mixture of a specimen and a reagent.

[0091] The configuration of each container setting unit 231 and reference light measurement unit 232 is the same. No container 15 is placed in the reference light measurement unit 232. Therefore, the light distributed to the reference light measurement unit 232 is received by the reference light receiving unit 236 without the light from the light irradiating unit 10 passing through the container 15 and the measurement sample. The light receiving unit 11 and the reference light receiving unit 236 each output an electrical signal according to the intensity of the received light.

[0092] (Control unit) 11, the blood coagulation analyzer 100 includes a control unit 400 that controls the operation of the measurement unit 101. The control unit 400 controls the operation of the light source 320. The control unit 400 includes an arithmetic processing device such as a CPU (Central Processing Unit) or an FPGA (field-programmable gate array), and controls each unit in the measurement unit 101 and the transport unit 102 according to a program stored in a storage unit 410. The storage unit 410 includes storage media such as a ROM (Read Only Memory), a RAM (Random Access Memory), and a hard disk, and stores programs and data necessary for the operation of the control unit 400.

[0093] In one configuration example, the control unit 400 controls each of the multiple light sources 320 to emit light in sequence and periodically. Specifically, as shown in FIG. 12, the control unit 400 repeatedly controls the five light sources 320 (i.e., the first light source 321 to the fifth light source 325) to emit light in sequence for a predetermined emission time T2 during an emission cycle T1. Each light source 320 is controlled to emit light in a pulsed manner for the emission time T2. The light receiving unit 11 and the reference light receiving unit 236 individually acquire electrical signals based on light from each light source 320 for each emission cycle T1, shifting the time. With this configuration, light of each wavelength can be individually irradiated at the same light irradiation position. Therefore, even if the wavelength of light used for measurement differs for each specimen, measurement can be performed at a common light irradiation position, so that the device configuration can be simplified, unlike a case in which multiple light irradiation positions dedicated to specific wavelengths are provided corresponding to each light source 320.

[0094] For example, when the main power supply of the analysis unit 12 and the main power supply of the measurement unit 101 are turned on, the control unit 400 controls the light emission of at least some of the light sources 320. More specifically, when the main power supply of the analysis unit 12 and the main power supply of the measurement unit 101 are turned on, the control unit 400 executes the initial setting of the measurement unit 101. When the initial setting of the measurement unit 101 is completed, the measurement unit 101 goes into a standby state. The control unit 400 continues to control each of the multiple light sources 320 to emit light periodically, one by one, in order, at least from when the measurement unit 101 goes into a standby state until a shutdown instruction is received. This eliminates the variation in the amount of light due to the influence of temperature changes immediately after the start of light emission, and stabilizes the light emission state during measurement. The control unit 400 causes, for example, the first light source 321, the second light source 322, the third light source 323, and the fifth light source 325 to emit light even in a standby state other than during measurement operation.

[0095] On the other hand, the characteristics of each light source 320 differ depending on the emission wavelength, and for example, the LED constituting the fourth light source 324 of 340 nm takes a shorter time from the start of emission control until the light amount stabilizes compared to other light sources. Therefore, the control unit 400 controls the emission of some of the light sources 320, for example the fourth light source 324, at the start of the measurement operation and does not emit light in the standby state except during the measurement operation. This can further extend the life of the light source 320.

[0096] In one configuration example, the control unit 400 is configured to control the current value supplied to the light source 320 based on the electrical signal (hereinafter referred to as the reference signal) of the reference light receiving unit 236. This makes it possible to suppress changes in the light intensity of the light source 320, for example, even when the blood coagulation analyzer 100 is operated continuously for a long period of time. For example, in an LED light source, changes in element temperature are likely to affect the amount of light emitted. Therefore, by controlling the current value so that the electrical signal of the reference light receiving unit 236 falls within a predetermined allowable range, it becomes possible to maintain the light intensity of the light source 320 within an appropriate range that allows stable measurement results to be obtained.

[0097] Specifically, the control unit 400 controls the drive circuit 420 of the light source 320 shown in FIG. 13. FIG. 13 shows an example of a drive circuit for controlling the light emission of one light source 320. The drive circuit 420 includes a constant current circuit 421, an RC circuit unit 422, and a switch unit 423. The light source 320 and the constant current circuit 421 are connected in series to a power source in this order. The RC circuit unit 422 and a resistor 424 are connected in parallel to the constant current circuit 421. The constant current circuit 421 supplies a predetermined constant current to the RC circuit unit 422. The constant current circuit 421 allows the current on the resistor 424 side to fluctuate. The RC circuit unit 422 is a parallel circuit of a variable resistor 425, a resistor 426, and a capacitor 427. The RC circuit section 422 delays the rise of the current flowing through the light source 320 according to a time constant proportional to the product of the combined resistance of the variable resistor 425 and the resistor 426 and the capacitance of the capacitor 427. In this way, the RC circuit section 422 prevents a large inrush current from flowing through the light source 320 during switching.

[0098] The RC circuit section 422 and the resistor 424 are connected to the switch section 423. The switch section 423 is composed of a transistor, and controls the on / off of the current supply to the drive circuit 420 by applying a voltage to the gate.

[0099] The control unit 400 applies a pulse signal to the gate of the switch unit 423 to control each of the light sources 320 to emit light at a predetermined light emission period T1 and a predetermined light emission time T2. Since the current flowing through the RC circuit unit 422 is kept constant by the constant current circuit 421, the current value flowing through the resistor 424 changes by changing the resistance value of the variable resistor 425. The current value flowing through the light source 320 is proportional to the ratio (R1 / R2) between the resistance value R1 of the RC circuit unit 422 including the variable resistor 425 and resistor 426 and the resistance value R2 of the resistor 424. The control unit 400 controls the current value supplied to the light source 320 by changing the resistance value of the variable resistor 425 based on the electrical signal of the reference light receiving unit 236.

[0100] The control unit 400 controls the current value of the light source 320 based on a reference value V1 and a lower limit value V2 of the reference signal RS, as shown in FIG. 14, for example. When starting light emission control of the light source 320, the control unit 400 sets the current value CV to the light source 320 so that the reference signal RS approximately matches the reference value V1. The light amount of the LED light source changes depending on the ambient temperature of the LED light source and the change over time of the LED element. Therefore, when the light amount of the light source 320 decreases over time, the intensity of the reference signal RS gradually decreases. When the intensity of the reference signal RS reaches the lower limit value V2, the control unit 400 performs control to correct the current value CV of the light source 320. Specifically, the control unit 400 calculates the corrected current value based on the following formula (1). Current value after correction = (reference value of reference signal / current value of reference signal) × current value before correction (1) The control unit 400 adjusts the resistance value of the variable resistor 425 to correct the current value CV of the light source 320 to the calculated corrected current value. As a result, the light amount of the light source 320, which decreases over time, increases every time the reference signal RS reaches the lower limit value V2, and is maintained within an appropriate range between the reference value V1 and the lower limit value V2.

[0101] (Analysis Department) In the configuration example shown in FIG. 15, the analysis unit 12 includes an arithmetic processing unit 451, a storage unit 452, a display unit 453, and an input unit 454. The arithmetic processing unit 451 includes an arithmetic processing device such as a CPU, and performs analysis processing of a sample according to a program stored in the storage unit 452. The storage unit 410 includes storage media such as a ROM, a RAM, and a hard disk, and stores programs and data required for processing and control of the arithmetic processing unit 451. The display unit 453 includes a display means such as a monitor. The input unit 454 includes input means such as a keyboard and a mouse, and accepts operation inputs from a user. The analysis unit 12 is, for example, configured by a personal computer.

[0102] In the configuration example of FIG. 16, the analysis unit 12 creates a plurality of time series data 460 corresponding to each of the plurality of light sources 320 from the electrical signal output from the light receiving unit 11 for the specimen in the container 15 placed in the container placement unit 231. As described above, the light from the five light sources 320 of the light irradiating unit 10 is supplied to the container placement unit 231 in sequence for each predetermined light emission period T1. Therefore, when the container 15 is placed in the container placement unit 231, the light from the five light sources 320 passes through the container 15 and the measurement sample and is detected in sequence by the light receiving unit 11. As a result, five electrical signals corresponding to the light of the first wavelength to the fifth wavelength, respectively, are output from the light receiving unit 11 to the control unit 400 for each light emission period T1. The analysis unit 12 receives each electrical signal from the control unit 400 and stores it in the memory unit 410.

[0103] During the measurement time T3 during which the container 15 is placed in the container placement section 231, one data item is acquired for each light emission period T1 for the first to fifth wavelengths of light. The five electrical signals have intensities that reflect the state of the measurement sample irradiated with the light. Each time series data 460 includes T3 / T1 pieces of data and is acquired for each wavelength. When irradiating the light with the first to fifth wavelengths of light, five types of time series data 460 are acquired.

[0104] The analysis unit 12, for example, selects time series data 460 corresponding to the measurement item from among the multiple time series data 460, and analyzes the sample. In this manner, the configuration in which time series data 460 for each wavelength is acquired and the time series data 460 to be used for analysis is selected allows common control regarding the acquisition of the time series data 460 regardless of the measurement item. For example, since there is no need to perform control such as reading data from the light receiving unit 11 in accordance with the timing at which light of a specific wavelength is irradiated during the light emission period T1, the control regarding the acquisition of the time series data 460 can be simplified.

[0105] If the measurement item of the sample in the container 15 placed in the container placement section 231 is a blood coagulation measurement, the analysis section 12 calculates the coagulation time, and the concentration or activity of a component contained in the sample from the time series data 460 corresponding to the first wavelength. That is, the analysis section 12 selects the time series data 460 acquired based on the electrical signal of the light from the first light source 321, and calculates the coagulation time based on the change in the amount of received light in the time series data 460. This makes it possible to acquire the coagulation time based on the light from the first light source 321 provided for measuring the coagulation time, thereby obtaining accurate and stable measurement results.

[0106] The analysis unit 12 calculates the clotting time by, for example, a percentage detection method. Specifically, the analysis unit 12 sets the light receiving intensity immediately after the addition of the reagent to 0% and the light receiving intensity at the end of the clotting reaction to 100%, and obtains the time at which the light receiving intensity reaches a preset value from the reaction curve, and sets this as the clotting time. In addition, the analysis unit 12 creates a calibration curve that relates the clotting time to the activity or concentration of the target component of the measurement item and records it in the storage unit 452, and obtains the concentration or activity of the target component of the measurement item based on the calculated clotting time and the calibration curve.

[0107] If the measurement item of the sample in the container 15 installed in the container installation section 231 is the measurement item of synthetic substrate measurement, the analysis section 12 calculates the concentration or activity of the component contained in the sample from the time series data 460 corresponding to the second wavelength. As a result, the synthetic substrate can be measured based on the light from the second light source 322 provided for synthetic substrate measurement, so that a stable measurement result can be obtained with high accuracy. In a configuration in which the fourth light source 324 is provided in addition to the second light source 322, the analysis section 12 calculates the concentration or activity of the component contained in the sample from the time series data 460 corresponding to the second wavelength and / or the fourth wavelength. The analysis section 12 analyzes the process in which the chromogenic synthetic substrate develops color based on the electrical signal corresponding to the light of the second wavelength or the fourth wavelength output from the light receiving section 11. That is, the analysis section 12 selects the time series data 460 acquired based on the electrical signal of the light from the second light source 322 or the fourth light source 324, and analyzes the degree of color development based on the change in the amount of received light in the time series data 460.

[0108] In the synthetic substrate measurement, the analysis unit 12 obtains the amount of change in absorbance, for example, by the Rate method or the Vlin method. The Rate method is a method of analyzing the change in the amount of received light between a predetermined start point and end point in the time series data 460, and calculating the amount of change in absorbance per unit time by linear regression. The Vlin method is a method of setting start and end points in the time series data 460 at which the amount of change in absorbance is maximum and the linear approximation is optimal for each sample, analyzing the change in the amount of received light between the set start and end points, and calculating the amount of change in absorbance per unit time by linear regression. The analysis unit 12 creates a calibration curve that relates the amount of change in absorbance to the activity or concentration of the target component of the measurement item in advance and records it in the storage unit 452, and obtains the concentration or activity of the target component of the measurement item based on the calculated amount of change in absorbance and the calibration curve.

[0109] If the measurement item of the sample in the container 15 installed in the container installation section 231 is the measurement item of the immunoturbidimetric measurement, the analysis section 12 calculates the concentration or activity of the component contained in the sample from the time series data 460 corresponding to the third wavelength. This allows the immunoturbidimetric measurement to be performed based on the light from the third light source 323 provided for the immunoturbidimetric measurement, so that accurate and stable measurement results can be obtained. In a configuration in which the fifth light source 325 is provided in addition to the third light source 323, the analysis section 12 calculates the concentration or activity of the component contained in the sample from the time series data 460 corresponding to the third wavelength and / or the fifth wavelength. The analysis section 12 analyzes the process of the antigen-antibody reaction between the sample and the antibody sensitizing reagent based on the electrical signal corresponding to the light of the third wavelength or the fifth wavelength output from the light receiving section 11. That is, the analysis section 12 selects the time series data 460 acquired based on the electrical signal of the light of the third light source 323 or the fifth light source 325, and analyzes the agglutination rate due to the antigen-antibody reaction based on the change in the amount of received light in the time series data 460.

[0110] In the immunoturbidimetric measurement, the analysis unit 12 determines the amount of change in absorbance by, for example, the Rate method or the Vlin method, as in the synthetic substrate measurement. The analysis unit 12 creates a calibration curve that correlates the amount of change in absorbance with the activity or concentration of the target component of the measurement item and records it in the storage unit 452, and obtains the concentration or activity of the target component of the measurement item based on the calculated amount of change in absorbance and the calibration curve.

[0111] When the light-receiving unit 11 receives the transmitted light of the light irradiated to the measurement sample, the received light intensity is maximum immediately after the reagent is added and decreases over time. On the other hand, when the light-receiving unit 11 receives the scattered light of the light irradiated to the measurement sample, the received light intensity is minimum immediately after the reagent is added and increases over time. Although the direction of increase and decrease in the received light intensity over time differs between transmitted light and scattered light, they are similar in that the coagulation time or the amount of absorbance change is calculated and the measurement item is analyzed using a calibration curve.

[0112] (Measurement operation of blood coagulation analyzer) 2 will be described with reference to Figures 17 and 18. The operation of the measurement unit 101 and transport unit 102 is controlled by the control unit 400. The analysis unit 12 is controlled by an arithmetic processing unit 451. For the components of the measurement unit 101 and transport unit 102, refer to Figure 18 below.

[0113] When the user turns on the main power supply of analysis unit 12 and the main power supply of measurement unit 101, the control operation in Fig. 17 is started. In step S1A, control unit 400 performs initial settings such as initialization processing of measurement unit 101, and in step S1B, calculation processing unit 451 performs initial settings such as initialization processing of analysis unit 12.

[0114] After the initial settings are completed, the control unit 400 transitions to a standby state in step S2A. When transitioning to the standby state, the control unit 400 starts light emission control for periodically emitting light from the first light source 321, the second light source 322, the third light source 323, and the fifth light source 325, other than the fourth light source 324, one by one in order. The light emission control continues until a shutdown instruction, which will be described later, is received.

[0115] In the standby state, the control unit 400 waits for a measurement start instruction from the analysis unit 12. In step S2B, the calculation processing unit 451 judges whether or not to start measurement. The calculation processing unit 451 repeatedly waits in step S2B until it receives an operation input for starting measurement by the user using the input unit 454. When it receives an input operation for starting measurement by the user, in step S3B, the calculation processing unit 451 transmits an instruction to start measurement to the control unit 400.

[0116] Upon receiving an instruction to start measurement from the analysis unit 12, the control unit 400 starts the measurement operation in step S3A. At the timing of starting the measurement operation, the control unit 400 starts light emission control for the fourth light source 324. As a result, the five light sources 320 are controlled to emit light periodically, one by one in order. The control unit 400 also controls the transport unit 102 to transport the sample rack 105 so that the sample container 106 to be aspirated is positioned at the sample aspirating position. During the transport of the sample rack 105, the reader 103 reads out the identification information of the sample rack 105 and the sample container 106.

[0117] In step S4A, the control unit 400 transmits a measurement order inquiry including the read identification information to the analysis unit 12. The calculation processing unit 451 that receives the measurement order inquiry acquires a measurement order for the specimen corresponding to the identification information and transmits it to the control unit 400. The measurement order is recorded in the storage unit 452 or an external host computer connected to the analysis unit 12 in association with the specimen identification information.

[0118] In step S5A, the control unit 400, which has received the measurement order, causes the specimen dispensing unit 110 or 120 to aspirate the specimen and dispense it into a new container 15. In step S6A, the control unit 400 controls the measurement unit 101 to heat the container 15 on the heating table 220 and add a reagent to the container 15 by the reagent dispensing unit 200 or 210. This prepares a measurement sample containing the specimen and the reagent in the container 15. In step S7A, the control unit 400 controls the measurement unit 101 to place the container 15 containing the measurement sample in the container placement unit 231 of the detection unit 230 or 240. Details of the operation of the measurement unit 101 in steps S5A to S10A will be described later.

[0119] After the start of the measurement operation in step S3A, each container installation section 231 is in a state where light of the first to fifth wavelengths is irradiated in order from the light irradiating section 10. As the container 15 is installed in the container installation section 231, the light from the light irradiating section 10 is irradiated onto the container 15, and the light receiving section 11, which receives the light transmitted through the container 15, outputs an electrical signal. The electrical signal is transmitted to the analysis section 12 via the control section 400.

[0120] In step S8A, the control unit 400 determines whether a predetermined measurement time T3 corresponding to the measurement item specified in the measurement order has elapsed since the container 15 was placed in the container placement unit 231. During the predetermined measurement time T3, the acquisition of electrical signals and transmission to the analysis unit 12 are continued. In step S5B, the calculation processing unit 451 of the analysis unit 12 generates five types of time series data 460 for each wavelength of light from the electrical signals for each wavelength received during the measurement time T3.

[0121] The length of the measurement time T3 varies depending on the measurement item as described above. For example, for PT and APTT, which are blood coagulation measurement items, the measurement time T3 is 170 seconds, and for Fbg, the measurement time T3 is 100 seconds. For ATIII, which is a synthetic substrate measurement item, the measurement time T3 is 60 seconds, and for D-dimer, which is a measurement item of immunoturbidimetric measurement, the measurement time T3 is 200 seconds.

[0122] When measurement time T3 has elapsed in step S8A, control unit 400 proceeds to step S9A, where it causes container 15 to be removed from container installation unit 231, and in step S10A, it causes the removed container 15 to be disposed of in waste outlet 260 or 261. Container 15 is transported by gripping mechanism 180 or 250.

[0123] Thus, in steps S7A to S10A, control unit 400 places container 15 containing a measurement sample in container setting unit 231, and controls gripping mechanism 180 or 250 to remove container 15 from container setting unit 231 after measurement time T3 corresponding to the measurement item of the specimen in container 15 placed in container setting unit 231 has elapsed, and discard container 15 into discard port 260 or 2611. Thereby, by simply varying the time for placing container 15 in container setting unit 231, measurements corresponding to various measurement items can be performed using a common device configuration.

[0124] Meanwhile, in the analysis unit 12, in step S6B, the calculation processing unit 451 selects time series data 460 corresponding to the measurement item from the five created time series data 460. In step S7B, the calculation processing unit 451 performs analysis using the selected time series data 460 to generate a measurement result. In step S8B, the calculation processing unit 451 records the obtained measurement result in the memory unit 452, displays the measurement result on the display unit 453, and the like.

[0125] In step S11A, the control unit 400 judges whether or not there is a next sample rack 105 in the transport unit 102, and if there is, returns to step S4A to continue the measurement operation. If there is no next sample rack 105, in step S12A, it judges whether or not a shutdown instruction has been received from the analysis unit 12, and goes into standby state.

[0126] On the other hand, in step S9B, the arithmetic processing unit 451 judges whether or not to perform a shutdown process. If the shutdown process is not to be performed, the arithmetic processing unit 451 continues the analysis operation from steps S4B to S8B based on the electrical signal transmitted in association with the measurement operation of the measurement unit 101. When an input operation for shutdown is received from the user, the arithmetic processing unit 451 transmits a shutdown instruction to the control unit 400 in step S10B.

[0127] When a shutdown instruction is received from the analysis unit 12, the control unit 400 proceeds to step S13A and performs a predetermined shutdown process. In the shutdown process, the control unit 400 stops the light emission control of each light source 320. This causes the light irradiation from the light irradiation unit 10 to stop.

[0128] The control unit 400 turns off the power after the shutdown process in step S13A, and the arithmetic processing unit 451 ends the process and turns off the power after the shutdown process in step S11B.

[0129] (Measurement operation of the measurement unit) Next, the operation of the measurement section 101 in steps S5A to S10A will be described in detail. As shown in Fig. 18, the operation of the measurement section 101 differs depending on whether the container 15 is transferred to the detection unit 230 for measurement or the container 15 is transferred to the detection unit 240 for measurement, and each will be described separately.

[0130] Measurement by the detection unit 230 When a sample is measured by the detection unit 230, the sample dispensing section 110 aspirates the sample from the sample container 106 at the sample suction position 501. The sample dispensing section 110 dispenses the sample into the container 15 held on the container table 130. The container table 130 rotates in the circumferential direction to transport the container 15 to a position where the sample can be aspirated by the sample dispensing section 120. The sample dispensing section 120 aspirates the sample from the container 15 and dispenses the sample into the container 15 held by the transfer section 140 at the sample dispensing position 503 on the container table 130. The transfer section 140 moves to the vicinity of the heating table 220, and the gripping mechanism 222 takes out the container 15 from the transfer section 140 and places it on the heating table 220. If necessary, the gripping mechanism 222 transports the container 15 to the reagent dispensing position 506, and the reagent dispensing section 200 dispenses the adjustment reagent into the container 15. After dispensing, the gripping mechanism 222 returns the container 15 to the warming table 220 .

[0131] When the heating by the heating table 220 is completed, the container 15 transferred to a predetermined removal position by the heating table 220 is taken out by the gripping mechanism 180 and transferred to the reagent dispensing position 506. The reagent dispensing section 200 dispenses the reagent into the container 15. After dispensing the reagent, the gripping mechanism 180 places the container 15 in one of the container installation sections 231 of the detection unit 230. With the placement of the container 15 in the container installation section 231, the light from the light emitting section 10 is irradiated onto the container 15, and the light receiving section 11, which receives the light transmitted through the container 15 and the measurement sample, outputs an electrical signal. The electrical signal is transmitted to the analysis section 12 via the control section 400. During the measurement time T3, the acquisition of the electrical signal continues, and the analysis section 12 generates time series data 460 for each wavelength of light. After the measurement time T3 has elapsed, the gripping mechanism 180 takes out the container 15 from the container installation section 231 and transfers it to the waste outlet 260. The analysis unit 12 selects time series data 460 according to the measurement item, analyzes the selected time series data 460, and displays the analysis results on the display unit 453 and records them in the memory unit 452.

[0132] Measurement by the detection unit 240 When a sample is measured by the detection unit 240, the sample dispensing section 110 aspirates the sample from the sample container 106 at the sample suction position 501. The sample dispensing section 110 dispenses the sample into the container 15 held by the container table 130. The container table 130 rotates in the circumferential direction to transport the container 15 to a position where the sample can be aspirated by the sample dispensing section 120. The sample dispensing section 120 aspirates the sample from the container 15 and dispenses the sample into the container 15 held by the transfer section 170 at the sample dispensing position 504. The transfer section 170 moves to the vicinity of the heating table 220, and the gripping mechanism 222 takes out the container 15 on the transfer section 170 and places it on the heating table 220. If necessary, the gripping mechanism 222 transports the container 15 to the reagent dispensing position 507, and the reagent dispensing section 210 dispenses the adjustment reagent into the container 15. After dispensing, the gripping mechanism 222 returns the container 15 to the warming table 220 .

[0133] When heating by the heating table 220 is completed, the container 15 that has been transferred to a predetermined removal position by the heating table 220 is removed by the gripping mechanism 250 and transferred to a reagent dispensing position 507. The reagent dispensing section 210 dispenses the reagent into the container 15. After dispensing the reagent, the gripping mechanism 250 places the container 15 in one of the container installation sections 231 of the detection unit 240. The measurement operation in the detection unit 240 is the same as that of the detection unit 230. After a predetermined measurement time has elapsed, the gripping mechanism 250 removes the container 15 from the container installation section 231 and transfers it to the waste outlet 261. The operation of the analysis section 12 is the same as when measurement is performed in the detection unit 230.

[0134] The specimen dispensing section 120 can also aspirate the specimen from the specimen container 106 at the specimen aspirating position 502, and dispense the specimen directly into a container 15 transferred to the specimen dispensing position 504 or 505. When the specimen is dispensed into the container 15 at the specimen dispensing position 504, measurement is performed by the detection unit 230. When the specimen is dispensed into the container 15 at the specimen dispensing position 505, measurement is performed by the detection unit 240. The operation after dispensing is as described above.

[0135] It should be noted that the embodiments disclosed herein are illustrative and not restrictive in all respects. The scope of the present invention is defined by the claims rather than the description of the embodiments above, and includes all modifications within the meaning and scope of the claims. [Explanation of symbols]

[0136] 10: light irradiating section, 11: light receiving section, 12: analysis section, 15: container, 20: light source, 21: first light source, 22: second light source, 23: third light source, 30: optical fiber section, 31: incident end, 32: output end, 40: holding member, 41: light source holding section, 42: incident end holding section, 100: blood coagulation analyzer, 180: gripping mechanism, 231: container installation section, 236: reference light receiving section, 250: gripping mechanism, 260: waste outlet, 261: waste outlet, 320: light source, 321: first light source, 322: second light source, 3 23: third light source, 324: fourth light source, 325: fifth light source, 330 (330a to 330e): optical fiber section, 331: incident end, 332: output end, 333: optical fiber, 340: holding member, 341: light source holding section, 342: incident end holding section, 344: passage section, 347: passage section, 350: homogenizing member, 360: optical bandpass filter, 370: condensing lens, 380: light distribution member, 400: control section, 460: time series data, D1: first distance, D2: second distance, D3: first distance

Claims

1. a light irradiation unit that irradiates light onto a container that contains a measurement sample including a specimen and a reagent; a light receiving unit for receiving light irradiated from the light irradiating unit; an analysis unit for analyzing the sample based on an electrical signal output from the light receiving unit, The light irradiation unit includes: A first light irradiation unit including a first light source that emits light of a first wavelength and a first optical fiber unit provided opposite to the first light source; a second light irradiation unit including: a second light source that emits light of a second wavelength different from the first wavelength and having a weaker light intensity than the light of the first wavelength; a light collecting unit provided corresponding to the second light source; and a second optical fiber unit provided corresponding to the second light source via the light collecting unit.

2. the second light source includes a plurality of light sources emitting light having a wavelength different from the first wavelength and a weak light intensity, the second optical fiber section includes a plurality of optical fiber sections provided corresponding to the plurality of light sources, 2. The blood coagulation analyzer according to claim 1, wherein the focusing unit includes a plurality of focusing lenses, each of the plurality of focusing lenses being provided between the plurality of light sources and the plurality of optical fiber units.

3. The blood coagulation analyzer according to claim 1 or 2, wherein each of the plurality of light sources is an LED.

4. 4. The blood coagulation analyzer according to claim 1, further comprising a control unit that controls each of the plurality of light sources to emit light periodically.

5. 5. The blood coagulation analyzer according to claim 1, further comprising: a plurality of light source holding units each holding a plurality of light sources; and a plurality of incident end holding units each holding an incident end of a plurality of optical fiber units facing the light sources held in each light source holding unit.

6. Irradiating light of a first wavelength emitted by a first light source toward an incident end of a first optical fiber portion disposed opposite the first light source; Irradiating a specimen with light of a first wavelength emitted from an emission end of the first optical fiber portion; light having a second wavelength emitted from a second light source, the light having a light intensity weaker than that of the light having the first wavelength, is focused by a focusing section to increase the light utilization efficiency, and the focused light is irradiated toward the incident end of the second optical fiber section; Irradiating a specimen with the light of the second wavelength emitted from an emission end of the second optical fiber portion; A blood coagulation analysis method comprising: analyzing a specimen using optical signals obtained from the specimen irradiated with light of the first wavelength and light of the second wavelength, respectively.

7. the second light source includes a plurality of light sources emitting light having a wavelength different from the first wavelength and a weak light intensity, the second optical fiber section includes a plurality of optical fiber sections provided corresponding to the plurality of light sources, 7. The blood coagulation analysis method according to claim 6, wherein the focusing unit includes a plurality of focusing lenses, each of the plurality of focusing lenses being provided between the plurality of light sources and the plurality of optical fiber units.

8. The blood coagulation analysis method according to claim 6 or 7, wherein each of the plurality of light sources is an LED.

9. 9. The blood coagulation analysis method according to claim 6, wherein each of the plurality of light sources is caused to emit light periodically.

10. The blood coagulation analysis method according to any one of claims 6 to 9, wherein the sample is analyzed based on time series data of a wavelength corresponding to a measurement item among time series data corresponding to each wavelength obtained by cyclically emitting light from a plurality of light sources.

11. Irradiating light of a first wavelength emitted by a first light source toward an incident end of a first optical fiber portion disposed opposite the first light source; Irradiating a specimen with light of a first wavelength emitted from an emission end of the first optical fiber portion; light having a second wavelength emitted from a second light source, the light having a light intensity weaker than that of the light having the first wavelength, is condensed by a condenser lens to increase the light utilization efficiency and is irradiated toward the incident end of the second optical fiber portion; Irradiating a specimen with the light of the second wavelength emitted from an emission end of the second optical fiber portion; A blood analysis method comprising: analyzing a sample using optical signals obtained from the sample irradiated with light of the first wavelength and light of the second wavelength, respectively.

12. light having a third wavelength emitted from a third light source, the light having a light intensity weaker than that of the light having the first wavelength, is condensed by a condenser lens to increase the light utilization efficiency and is irradiated toward the incident end of a third optical fiber portion; Irradiating a specimen with the light of the third wavelength emitted from an emission end of the third optical fiber section; The blood analysis method according to claim 11, further comprising the step of analyzing a sample using optical signals obtained from the sample irradiated with light of the first wavelength, the second wavelength, and the third wavelength, respectively.

13. light of a fourth wavelength emitted from a fourth light source having a light intensity weaker than that of the light of the first wavelength is condensed by a condenser lens to increase the light utilization efficiency and irradiate the light toward the incident end of the fourth optical fiber portion; Irradiating a specimen with the light of the fourth wavelength emitted from an emission end of the fourth optical fiber section; 13. The blood analysis method according to claim 12, further comprising analyzing a sample using optical signals obtained from the sample irradiated with light of the first wavelength, the second wavelength, the third wavelength, and the fourth wavelength, respectively.

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