JP7170026B2 - Blood coagulation analysis method and blood coagulation analyzer - Google Patents

Description

The present invention relates to a blood coagulation analysis method and blood coagulation analyzer.

In Patent Document 1, a light irradiation unit irradiates a measurement container installed in a container installation unit with light of a plurality of wavelengths for blood coagulation analysis, and the light transmitted through the measurement container is detected by a light receiving unit. A blood coagulation analyzer is disclosed. The light irradiation section of Patent Document 1 includes a halogen lamp, which is a broadband light source, and a filter section that holds a plurality of optical filters having different transmission wavelengths along the circumference. The filter section is configured such that each optical filter is rotated around a central axis to sequentially arrange each optical filter in the optical path from the light source. As a result, the light irradiation unit sequentially irradiates the measurement container placed on the container installation unit with light of a plurality of wavelengths. Light of multiple wavelengths is used for analyte measurement of each separate measurement item.

JP-A-2008-46031

The blood coagulation analyzer disclosed in Patent Literature 1 is provided with a halogen lamp which is larger than a semiconductor light emitting element such as an LED, and a filter section provided with a rotating mechanism. Also, the light source life of the halogen lamp is short.

In order to solve such a problem, simply adopting a configuration in which a plurality of LEDs, which have a longer life than halogen lamps, and light from each LED are made to enter an optical fiber coupler through a plurality of mirrors and dichroic mirrors, a plurality of Precise work is required for optical axis adjustment to match the optical axes of the light sources. Therefore, in a blood coagulation analyzer that emits light of a plurality of wavelengths for blood coagulation analysis, it is desirable to have a configuration that suppresses an increase in the size of the device configuration, has a long light source life, and can easily suppress the occurrence of optical axis deviation. It is rare.

The present invention provides a blood coagulation analyzer that irradiates light of a plurality of wavelengths for blood coagulation analysis. It is aimed at

A blood coagulation analysis method according to a first aspect of the present invention generates light with different wavelengths from a plurality of light sources, and transmits the light from the plurality of light sources to a plurality of optical fiber sections provided corresponding to the plurality of light sources. In addition to making each light source incident, for a light source with less light intensity than other light sources among multiple light sources, light is condensed into the corresponding optical fiber part via a condenser lens, so that the light source with less light intensity is incident. The amount of light emitted is brought close to the amount of light incident from other light sources, and the light from multiple light sources is applied through multiple optical fiber units to a container containing a measurement sample containing a specimen and a reagent, and the light emitted from the container is detected. and analyze the analyte based on the detected light.

A blood coagulation analyzer according to a second aspect of the present invention comprises a light irradiation section for irradiating light onto a container containing a measurement sample containing a specimen and a reagent, and a light receiving section for receiving the light irradiated from the light irradiation section. and an analysis unit for analyzing the specimen based on the electrical signal output from the light receiving unit, wherein the light irradiation unit is provided corresponding to each of the plurality of light sources having different wavelengths and the plurality of light sources. light from a light source having a lower light intensity than other light sources among the plurality of light sources is condensed into the corresponding optical fiber portion, thereby allowing a light source having a lower light intensity to be connected to the corresponding optical fiber. and a condensing lens that brings the amount of light incident on the portion closer to the amount of light incident on the corresponding optical fiber portion from another light source .

According to the present invention, in a blood coagulation analyzer that irradiates light of a plurality of wavelengths for blood coagulation analysis, an increase in the size of the device configuration is suppressed, the life of the light source is long, and the occurrence of optical axis deviation is easily suppressed. can.

1 is a schematic diagram showing an overview of a blood coagulation analyzer according to one embodiment; FIG. 1 is a schematic plan view for explaining an example of the overall configuration of a blood coagulation analyzer; FIG. FIG. 4 is a schematic cross-sectional view showing a specific configuration example of a light irradiation unit; FIG. 4 is a perspective view showing a configuration example of a homogenizing member; FIG. 4 is a diagram for explaining the characteristics of an optical bandpass filter; 4 is an enlarged cross-sectional view showing a configuration example of a holding portion of the fourth light source in FIG. 3; FIG. 4 is an enlarged cross-sectional view showing a configuration example of a holding portion of the fifth light source in FIG. 3; FIG. FIG. 4 is a schematic cross-sectional view showing another configuration example of a light irradiation unit; FIG. 4 is a schematic diagram showing a configuration for guiding light from a light irradiation section to a detection unit; 4 is an enlarged cross-sectional view showing a configuration example of a container installation portion of the detection unit; FIG. FIG. 3 is a block diagram showing a control configuration example of the measurement unit shown in FIG. 2; It is a figure for demonstrating the light emission control of each light source by a control part. FIG. 3 is a diagram showing a configuration example of a drive circuit for a light source; It is a figure for demonstrating the current value control of the light source by a control part. 4 is a block diagram showing a configuration example of an analysis unit; FIG. FIG. 4 is a conceptual diagram for explaining analysis processing by an analysis unit; 3 is a flow chart for explaining the operation of the blood coagulation analyzer shown in FIG. 2; 3 is a diagram for explaining the operation of the blood coagulation analyzer shown in FIG. 2; FIG.

Hereinafter, embodiments will be described based on the drawings.

[Overview of blood coagulation analyzer]
As shown in FIG. 1, the blood coagulation analyzer 100 irradiates light onto a measurement sample prepared by adding a reagent to a specimen, detects transmitted light or scattered light of the light irradiated onto the measurement sample, A device that analyzes a sample based on detected light. The analyte is plasma or serum separated from blood. The blood coagulation analyzer 100 analyzes specimens using a coagulation method, a synthetic substrate method, an immunonephelometry, or an agglutination method.

The blood coagulation analyzer 100 includes a light irradiation unit 10 for irradiating a container 15 containing a measurement sample containing a specimen and a reagent with light, and a light receiving unit for detecting the light emitted from the light irradiation unit 10 and transmitted through the container 15 . and an analysis unit 12 for analyzing a sample based on the electrical signal output from the light receiving unit 11 .

A container 15 is a cuvette for containing a measurement sample in which a specimen and a reagent are mixed. The container 15 is made of translucent resin, glass, or the like, and is preferably sufficiently transparent so as not to affect the emitted 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 trunk portion 15a that opens upward, and a collar portion 15b that is provided at the upper end of the trunk portion 15a. The trunk portion 15a has a smaller diameter at its lower portion than at its upper portion. The shape of the container 15 is not limited to that illustrated.

The light irradiation section 10 includes a plurality of light sources 20 and a plurality of optical fiber sections 30 provided facing each light source 20 . A holding member 40 for holding each light source 20 and the incident end 31 of each optical fiber portion 30 may be further provided. When the holding member 40 is provided, each light source 20 and the incident end 31 of each optical fiber portion 30 can be held more easily. Each light source 20 and each incident end 31 may be individually fixed without providing the holding member 40 .

Light source 20 includes multiple 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 measuring blood coagulation time and a second light source for generating light of a second wavelength for measuring synthetic substrates. It includes a light source 22 and a third light source 23 for generating light at a third wavelength for immunoturbidimetry. The multiple 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 .

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

As the second wavelength light generated by the second light source 22, for example, light in a wavelength band of 390 nm to 420 nm can be used. More preferably, light in the wavelength band of 400 nm to 410 nm can 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 the chromogenic synthetic substrate on the enzyme in the measurement sample is measured based on the electrical signal of the transmitted light from the sample. Measurement items of the synthetic substrate method include ATIII (antithrombin III), α2-PI (α2-plasmin inhibitor), PLG (plasminogen), and the like.

As the third wavelength light generated by the third light source 23, for example, light in a wavelength band of 690 nm to 820 nm can be used. More preferably, light in the wavelength band of 700 nm to 810 nm can be used. The third wavelength is 800 nm, for example. In the immunoturbidimetric method, a reagent that causes an antigen-antibody reaction with coagulation/fibrinolytic factors in the specimen is added to the specimen, and substances contained in the reagent agglutinate as a result of the antigen-antibody reaction. The measurement sample is irradiated with light of the third wavelength, and the agglutination speed of the reagent-containing substance in the measurement sample is measured based on the electrical signal of the transmitted light or scattered light from the sample. Items to be measured by immunoturbidimetry include D-dimer and FDP (fibrin degradation product).

By providing a light source 20 individually according to each measurement item, a light source that generates light in a narrow wavelength band centered on the wavelength used for measurement is adopted instead of a broadband light source that covers a wide wavelength band like a halogen lamp. can. For example, the first light source 21 can employ a light source that includes the first wavelength and hardly includes the second and third wavelengths. Therefore, as the light source 20, a relatively narrow-band light source whose center wavelength is the wavelength used for measurement 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.

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

A plurality of optical fiber sections 30 are provided corresponding to each light source 20 . That is, one optical fiber section 30 is provided for each light source 20 . 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. including. 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 the light source is separately provided.

In a configuration further including a holding member 40, the holding member 40 has the function of holding the light source 20 and the incident end 31 of the optical fiber section 30 to maintain their mutual positional relationship. The holding member 40 is provided, for example, at a position facing a plurality of light source holding portions 41 holding each light source 20 and each light source 20 held by each light source holding portion 41 . and a plurality of incident end holders 42 that hold the ends 31 . Thus, the holding member 40 holds the light sources 20 and the incident ends 31 of the optical fiber portions 30 so as to face each other. The light source holding portion 41 and the incident end holding portion 42 are provided for each pair of one light source 20 and the incident end 31 of the optical fiber portion 30 corresponding to the light source 20 . The light source holding portion 41 and the incident end holding portion 42 hold the light source 20 and the corresponding incident end 31 of the optical fiber portion 30 at positions close to each other. The holding member 40 holds the optical axis of the light source 20 and the central axis of the optical fiber portion 30 in a state of substantially matching. Instead of providing the holding member 40 , the light source holding portion 41 and the incident end holding portion 42 may be individually provided for each pair of the light source 20 and the incident end 31 .

The light receiving unit 11 includes a photoelectric conversion element that converts received light into an electrical signal and outputs the electrical signal. Blood coagulation analyzer 100 may include an amplifier circuit that amplifies the electrical signal output from the photoelectric conversion element of light receiving section 11 . The light receiving section 11 has a function of outputting an electrical signal corresponding to the amount of received light to the analyzing section 12 . The light receiving section 11 is arranged, for example, so as to face the output end 32 of the optical fiber section 30 . By placing the container 15 containing the measurement sample between the light receiving unit 11 and the emitting end 32 , the light receiving unit 11 detects the light emitted from the light irradiation unit 10 and transmitted through the container 15 . The light that has passed through the container 15 is transmitted light or scattered light due to the light irradiated on the measurement sample. Transmitted light or scattered light of the light irradiated to the sample is transmitted through the container 15 and received by the light receiving section 11 . The light receiving unit 11 may be configured to receive both transmitted light and scattered light.

Note that FIG. 1 shows a configuration example in which the light emitted from the light emitting end 32 of the optical fiber section 30 is directly irradiated onto the container 15, passes through the container 15, and is received by the light receiving section 11. Another optical element may be provided between the output end 32 of 30 and the light receiving section 11 . For example, when irradiating a plurality of containers 15 with light, an optical element may be provided for distributing the light from the output end 32 of the optical fiber section 30 to each container 15 . Further, a lens or an optical filter having predetermined optical characteristics may be arranged immediately before the container 15 or between the container 15 and the light receiving section 11 .

The analysis unit 12 is configured by a computer including a processor, memory, and the like. The analysis unit 12 may be configured as an analysis unit by causing a general-purpose computer to execute a sample analysis program, or may be configured by dedicated hardware. The analysis unit 12 records the data of the electrical signal output from the light receiving unit 11 and analyzes the specimen according to the measurement items. A change in the electrical signal output from the light receiving section 11 represents a change in the amount of light received by the light receiving section 11 . In the measurement using the first light source 21 to the third light source 23, the analysis unit 12 can analyze the specimen based on the change in the electrical signal output from the light receiving unit 11 during the predetermined measurement time. The analysis unit 12 analyzes the blood clotting time in the case of the coagulation method, analyzes the absorbance change in the process of color development of the chromogenic synthetic substrate in the case of the synthetic substrate method, and, in the case of immunonephelometry, The change in absorbance due to antigen-antibody reaction of the reagent is analyzed. Even when performing analysis by other measurement methods, the analysis unit 12 performs specimen analysis from electrical signals according to the measurement method.

Next, an analysis method by the blood coagulation analyzer 100 will be described. Blood coagulation analyzer 100 generates light from multiple light sources 20 held by multiple holding units 40 . Blood coagulation analyzer 100 allows light from multiple light sources 20 to enter incident ends 31 of multiple optical fiber units 30 held by multiple holding units 40 . The blood coagulation analyzer 100 irradiates the container 15 containing the specimen with the light emitted from each emission end 32 of the plurality of optical fiber units 30 and detects the light transmitted through the container 15 . Blood coagulation analyzer 100 analyzes the specimen based on the detected light.

With the above configuration, the blood coagulation analyzer 100 is provided with a plurality of light sources 20 and a plurality of optical fiber sections 30 corresponding to the plurality of light sources 20, thereby combining a broadband light source such as a halogen lamp and a rotating filter device. Instead, blood coagulation analysis can be performed by using a plurality of small, long-life light sources 20 such as LEDs. As a result, compared to halogen lamps, the life of the light source can be lengthened, and an increase in the size of the device configuration can be suppressed. Furthermore, unlike the configuration in which a mirror is arranged in the optical path from the light source 20 to guide the light to the container 15, the light source 20 and the incident end 31 of the optical fiber portion 30 are opposed to each other, and the light source holding portion 41 of the holding member 40 and the incident end 31 are arranged to face each other. Since they can be held close to each other by the end holding portion 42, optical axis alignment can be performed easily and accurately. As a result, in the blood coagulation analyzer 100 that irradiates light of a plurality of wavelengths for blood coagulation analysis, it is possible to suppress an increase in the size of the device configuration, to have a long light source life, and to easily suppress the occurrence of optical axis deviation. .

Further, since the light source 20 and the incident end 31 of the optical fiber section 30 can be held close to each other, it is possible to reduce the amount of light lost before the light emitted from the light source 20 enters the optical fiber section 30. . As a result, it is possible to reduce the influence of noise mixed in the electrical signal output from the light receiving unit 11, and obtain blood coagulation analysis results with high reproducibility. For example, when calculating the coagulation time by the percent detection method as the result of blood coagulation analysis, if the noise mixed in the electrical signal output from the light receiving unit 11 has a large influence, even if the same sample is measured multiple times, A different clotting time may be calculated for each measurement. On the other hand, in the blood coagulation analyzer 100, the light source 20 and the incident end 31 of the optical fiber section 30 can be held close to each other, thereby suppressing the influence of noise mixed in the electrical signal output from the light receiving section 11. Therefore, for example, when the coagulation time is calculated by the percent detection method as the blood coagulation analysis result, a highly reproducible coagulation time can be obtained.

[Configuration example of blood coagulation analyzer]
A more specific configuration example of the blood coagulation analyzer 100 shown in FIG. 1 will be described below with reference to FIG. 2 onward. FIG. 2 shows one configuration example of an automatic analyzer for blood coagulation analysis.

(overall structure)
In the configuration example of FIG. 2 , the blood coagulation analyzer 100 includes a measurement section 101 , a transport section 102 and an analysis section 12 . The light irradiation section 10 and the light receiving section 11 (see FIG. 9) are provided in the measurement section 101 .

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

A sample rack 105 is installed in the transport section 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 . The sample rack 105 and the sample container 106 are attached with a label (not shown) in which identification information is recorded in a bar code or the like. The identification information of the sample rack 105 and the sample container 106 is read by the reader 103 installed in the transport route and transmitted to the analysis unit 12 . The identification information manages the samples in the sample container 106 and the measurement results of the samples in association with each other.

The measurement unit 101 includes sample dispensing units 110 and 120 for aspirating the sample in the sample container 106 and dispensing a fixed amount of sample into the container 15 .

The specimen pipetting units 110 and 120 are composed of pipetting arms that rotatably hold pipettes 111 for specimen pipetting. The pipette 111 is connected to a pump (not shown), and can aspirate and discharge a fixed amount of sample. The specimen dispensing unit 110 can aspirate a predetermined amount of specimen from the specimen container 106 at the specimen aspiration position 501 by moving the pipette 111 . The specimen dispensing unit 120 can aspirate a predetermined amount of specimen from the specimen container 106 at the specimen aspiration position 502 by moving the pipette 111 . The sample dispensing units 110 and 120 can each move the pipette 111 to discharge the aspirated sample into the container 15 arranged at a predetermined sample dispensing position.

The measurement unit 101 optically measures a measurement sample prepared by adding a predetermined reagent to the sample aspirated by the sample dispensing unit 110 . Blood coagulation analyzer 100 may be configured to perform measurement on container 15 into which a fixed amount of sample has been previously dispensed, without including conveying unit 102 and sample dispensing unit 110 .

The measurement unit 101 has a mechanism for transferring a container 15 containing a sample and a reagent to prepare a measurement sample to each unit. 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 plan view and can rotate in the circumferential direction. The container table 130 includes a plurality of holding holes 131 arranged along the circumferential direction. One container 15 can be installed in each holding hole 131 . The sample dispensing unit 110 can dispense the aspirated sample into the new container 15 held on the container table 130 at the sample dispensing position 503 . The sample dispensing unit 120 can also aspirate the sample from the container 15 containing the sample on the container table 130 .

The measurement section 101 includes a transfer section 140 that positions a new container 15 at the sample dispensing position 504 . The transfer section 140 can move an installation table having a holding hole for installing the container 15 along the rail. For example, two holding holes are provided. The specimen dispensing section 120 can dispense the aspirated specimen into the new container 15 held by the transfer section 140 at the specimen dispensing position 504 .

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 container 15 taken out by the container supply unit 151 is gripped by the gripping mechanism 160 and taken out. The gripping mechanism 160 can set the taken-out container 15 in the holding hole 131 of the container table 130 or the holding hole of the transfer section 140 .

The measuring section 101 has a transfer section 170 . The transfer section 170 can move an installation table having a holding hole like the transfer section 140 along the rail. A new container 15 in the container supply section 151 is picked up by the gripping mechanism 180 and placed in the holding hole of the transfer section 170 . The transfer unit 170 can transfer the installed new container 15 to the sample dispensing position 505 . The specimen dispensing section 120 can dispense the aspirated specimen into the new container 15 held by the transfer section 170 at the specimen dispensing position 505 .

In the configuration example of FIG. 2, the blood coagulation analyzer 100 has a function of adding a reagent to the sample in the container 15 to prepare a measurement sample. A measurement sample is a mixture of a specimen and a reagent.

The measurement unit 101 includes a reagent table 190 that accommodates reagent containers 191 used for measurement, and reagent dispensing units 200 and 210 for aspirating and discharging reagents from the reagent containers placed on the reagent table 190 .

The reagent table 190 is arranged inside the container table 130 and has a circular shape in plan view. A plurality of reagent containers 191 can be installed on the reagent table 190 along the circumferential direction. The reagent table 190 is rotatable in the circumferential direction, and can position any reagent container 191 at a predetermined reagent aspirating position by rotation.

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

The reagent dispensing unit 210 can aspirate a predetermined amount of reagent from the reagent container 191 at the reagent aspirating position positioned at the predetermined reagent aspirating position on the reagent table 190 . The reagent dispensing section 210 can move the pipette to the reagent dispensing position 507 and discharge a predetermined amount of reagent into the container 15 at the reagent dispensing position 507 .

The measurement unit 101 includes a heating table 220 for holding and heating the container 15 into which the sample is dispensed. The heating table 220 includes a plurality of holding holes 221 for respectively holding a plurality of containers 15 containing specimens, and a grasping mechanism 222 for grasping and transferring the containers 15 . The heating table 220 incorporates heaters (not shown) for heating the containers 15 respectively held in the plurality of holding holes 221 .

The heating table 220 has a circular shape in 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 by rotation while being heated to a predetermined temperature by the heater. The gripping mechanism 222 can grip and transfer the container 15 , set the container 15 in the holding hole 221 , or remove the container 15 from the holding hole 221 .

The gripping mechanism 222 can transfer the container 15 placed on the transfer section 140 to the holding hole 221 of the heating table 220 . Also, the gripping mechanism 222 can take out the container 15 heated in the holding hole 221 of the heating table 220 and transfer it to the reagent dispensing positions 506 and 507, respectively. 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 .

Blood coagulation analyzer 100 may be configured to perform measurement on container 15 in which a prepared measurement sample is previously accommodated without reagent table 190, reagent dispensing unit 200, and heating table 220. .

The measurement section 101 includes detection units 230 and 240 for optically measuring the measurement sample in the container 15 . The two detection units 230 and 240 have the same configuration. Only one of detection units 230 and 240 may be provided. The detection units 230 and 240 each include a container setting portion 231 for setting the container 15 containing the sample, and a light receiving portion 11 provided corresponding to the container setting portion 231 .

In the configuration example of FIG. 2 , each of the detection units 230 and 240 has a plurality of container installation portions 231 . Detecting units 230 and 240 extend linearly along one side of blood coagulation analyzer 100 in a plan view, and a plurality of container mounting portions 231 are linearly arranged at predetermined intervals.

Measuring portion 101 includes gripping mechanisms 180 and 250 for transferring container 15 to detection units 230 and 240, respectively.

The gripping mechanisms 180 and 250 are provided with moving mechanisms (not shown) in the X, Y, and Z directions, which are orthogonal three-axis directions, and can grip and transfer the container 15 . The gripping mechanism 180 can transfer the container 15 between the container supply section 151 and the transfer section 170 described above. The gripping mechanism 180 can take out the container 15 from the holding hole 221 of the heating table 220, transfer it to the reagent dispensing position 506, and install the container 15 after the reagent has been dispensed on the container installation portion 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, transfer it to the reagent dispensing position 507, and install the container 15 after the reagent has been dispensed on the container installation portion 231 of the detection unit 240. . It should be noted that the gripping mechanisms 180 and 250 can take out the measured container 15 from the container setting portion 231 and transfer it to the respective disposal ports 260 and 261, respectively.

Optical measurement is performed on the measurement sample in the container 15 installed in the container installation portion 231 of the detection units 230 and 240 . The light irradiation section 10 irradiates the container 15 installed in the container installation section 231 of the detection units 230 and 240 with light for measurement. The light receiving unit 11 (see FIG. 9) receives transmitted light or scattered light of the light irradiated to the container 15 and outputs an electric signal corresponding to the amount of received light. The electrical signal is sent to the analyzer 12 . The analysis unit 12 analyzes the specimen based on the electrical signal output from the light receiving unit 11 .

(Configuration example of light irradiation unit)
FIG. 3 shows a configuration example of the light irradiation unit 10. As shown in FIG. 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 incident ends of the light sources 320 and the optical fiber units 330. 331 and one retaining member 340 for retaining . Light source 320 , optical fiber section 330 and holding member 340 are housed in housing 310 made of metal, for example.

All of the five light sources 320 are composed of LEDs. LEDs generally have a lifespan several tens of times longer than that of halogen lamps. As a result, compared to a configuration using a broadband light source such as a halogen lamp and a rotating filter, it is possible to configure the light irradiation unit 10 that is smaller and has a longer life. Also, since a separate LED can be provided for each wavelength, the emission spectrum and emission intensity of each light source 320 can be individually optimized.

Light source 320 includes first light source 321 , second light source 322 and 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 emits light of approximately 660 nm as the first wavelength. The second light source 322 is a light source for synthetic substrate measurement that generates light of about 405 nm as the second wavelength. The third light source 323 is a light source for immunonephelometry that generates light of about 800 nm as the third wavelength.

In the configuration example of FIG. 3, the plurality of light sources 320 further includes 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 or more and 380 nm or less, like the second wavelength. More preferably, light in the wavelength band of 320 nm to 360 nm can be used. In the configuration example of FIG. 3, the fourth wavelength is 340 nm, for example. The fourth wavelength light can be used as a sub-wavelength for synthetic substrate measurements. That is, compared with the electrical signal corresponding to the light of the second wavelength and the electrical signal corresponding to the light of the fourth wavelength, the signal from which more stable detection results are obtained can be used for analysis. . As a result, analysis using electrical signals with higher reliability can be performed, and even in this case, an increase in the size of the device configuration can be suppressed.

In the configuration example of FIG. 3, the plurality of light sources 320 further includes a fifth light source 325 for generating light of a fifth wavelength different from the third wavelength for immunonephelometry. The fifth wavelength is a wavelength selected from the range of 550 nm or more and 590 nm or less, like the third wavelength. More preferably, light in the wavelength band of 560 nm to 580 nm can be used. In the configuration example of FIG. 3, the fifth wavelength is 575 nm, for example. Light at the fifth wavelength can be used as a sub-wavelength for immunoturbidimetry. In other words, compared with the electrical signal corresponding to the light of the third wavelength and the electrical signal corresponding to the light of the fifth wavelength, it is possible to adopt the signal from which more stable detection results are obtained and perform the analysis. . As a result, analysis using electrical signals with higher reliability can be performed, and even in this case, an increase in the size of the device configuration can be suppressed.

The optical fiber section 330 is provided corresponding to each light source 320 . The five optical fiber units 330 are arranged for each light source 320 so that the light from the first light source 321, the second light source 322, the third light source 323, the fourth light source 324, and the fifth light source 325 are incident from the respective incident ends 331. It is composed of optical fiber portions 330a, 330b, 330c, 330d and 330e provided individually.

In the configuration example of FIG. 3, each of the plurality of optical fiber sections 330 includes a plurality of optical fibers 333 . The plurality of optical fiber portions 330 are mixed and bundled at the output end 332 so that the plurality of optical fibers 333 corresponding to the respective light sources 320 are distributed substantially uniformly. Here, "optical fiber" means an optical fiber bare wire or optical fiber core wire having one core. Each optical fiber portion 330 is configured as a cable or twisted wire in which a plurality of strands are bundled. With this configuration, the light of each wavelength separately incident on the incident end 331 of each optical fiber portion 330 can be emitted from the common emitting end 332 instead of irradiating the container 15 individually. Therefore, the configuration for emitting light of each wavelength can be simplified. In addition, since the light of each wavelength can be emitted from the common emission end 332 in a uniform distribution, even when the light of each wavelength is emitted from the common emission end 332, the distribution of the light for each wavelength is not biased. can be suppressed.

In the configuration example of FIG. 3 , five optical fiber sections 330 are twisted and integrated in the middle, and configured to have two output ends 332 . Two emission ends 332 are provided to correspond to the two detection units 230 and 240 (see FIG. 2), respectively. The two output ends 332 are connected to two outlets 311 provided in the housing 310, respectively. Each output end 332 includes an approximately equal number of optical fibers 333 forming each optical fiber portion 330 . Also, the optical fibers 333 forming each optical fiber portion 330 are mixed so as to be distributed substantially uniformly within the end face of the output end 332 . The number of optical fibers 333 forming each optical fiber section 330 is determined according to the number of container installation sections 231 in the detection units 230 and 240 . For example, when the number of container installation units 231 is N, and each optical fiber unit 330 transmits the light amount of M optical fibers to one container installation unit 231, each optical fiber unit 330 has N×M optical fibers. of optical fibers 333. Each output end 332 is configured by collecting (N×M)/2 optical fibers 333 from each optical fiber portion 330 .

<Equalization member>
In the configuration example of FIG. 3, the light irradiating section 10 is arranged adjacent to the output end 332 of the optical fiber section 330, and has a uniform intensity distribution for making the intensity distribution of the light incident from the output end 332 side uniform. It further includes a curing member 350 . Here, each optical fiber 333 arranged at the emission end 332 emits only light of any one of the first to fifth wavelengths. That is, at the output end 332, the light emitting points for each wavelength are uniformly distributed. Therefore, by making the light from the output end 332 incident on the homogenizing member 350 and homogenizing it, the intensity distribution of each wavelength is homogenized over the entire plane on the output surface 352 of the homogenizing member 350 . . As a result, variations in light intensity for each wavelength can be effectively equalized.

The homogenizing members 350 are respectively arranged in two outlets 311 provided in the housing 310 . Each homogenizing member 350 has an incident surface 351 facing each output end 332 of the optical fiber portion 330 , and an output surface 352 arranged on the exit side of the outlet 311 . As a result, light whose intensity distribution has been made uniform through the uniformizing member 350 is emitted from each outlet 311 . The homogenizing member 350 is configured, for example, to internally multiple-reflect the light incident from the entrance surface 351 and to emit the light from the exit surface 352 . As an example of the uniformizing member 350, FIG. 6 shows a light pipe 353 comprising a polygonal prismatic homogenizer rod. The light pipe 353 internally multiple-reflects the incident light, thereby emitting light of each wavelength from the emission surface 352 with a uniform intensity distribution. If the intensity distribution of light of each wavelength is sufficiently homogenized at the output end 332 of the optical fiber portion 330, the homogenizing member 350 may not be provided.

<Holding member>
Returning to FIG. 3 , the holding member 340 of the light irradiation section 10 holds five light sources 320 . Therefore, five light sources 320 are supported by a common holding member 340 . The holding member 340 is made of metal such as aluminum, and has a prism shape. In the configuration example of FIG. 3, the light source holding portion 341 and the incident end holding portion 342 are provided at one end and the other end of the holding member 340, respectively, and pass through the holding member 340 through passage portions 344 formed of through holes. connected to each other.

The five light source holders 341 are arranged linearly in a direction orthogonal to the light emission direction of each light source 320 . Each light source 320 has a fourth light source 324 arranged in the center, a fifth light source 325 and a second light source 322 arranged on both sides of the fourth light source 324, and a first light source 321 and a third light source 323 arranged on the outermost side. ing.

In the configuration example of FIG. 3 , a plurality of light source holders 341 that hold the light sources 320 and a plurality of incident end holders 342 that respectively hold the incident ends 331 of the plurality of optical fiber portions 330 are mutually held by the holding member 340 . They are arranged in straight lines facing each other. As a result, the optical axis of the light source 320 and the axial center of the optical fiber portion 330 at the incident end 331 can be easily aligned with high accuracy. In FIG. 3, the light source holding portion 341 and the incident end holding portion 342 are arranged at positions facing each other on substantially the same axis.

In the configuration example of FIG. 3, the light source holder 341 holds the light source 320 via the socket 343, as shown in detail in FIGS. The light source holding portion 341 includes a recess 345 connected to the passage portion 344 , and the socket 343 is a cylindrical member fitted into the recess 345 . Light source 320 is fixedly held inside socket 343 . The incident end holding portion 342 is configured by the other end portion of a passage portion 344 that is a through hole passing through the holding member 340 . Therefore, the incident end holding portion 342 is a hole into which the incident end 331 can be inserted, and holds a predetermined length range including the incident end 331 of the optical fiber portion 330 by inserting it therein.

The light irradiation section 10 includes a member for concentrating the light from the light source 320 onto the incident end 331 of the optical fiber section 330, and a spectral characteristic such as the center wavelength and the half-value width of the light incident on the incident end 331. You may provide the member for.

<Optical bandpass filter>
For example, in FIG. 3, the light irradiation section 10 further includes an optical bandpass filter 360 that transmits only light in a predetermined wavelength band. The optical band-pass filter 360 has a disk-like shape and transmits only light in a predetermined wavelength band out of the light irradiated on 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 section 330 . As a result, the center wavelength, half-value width, etc. of the light emitted from the light source 320 can be adjusted to have characteristics suitable for measurement, and the light can be incident on the incident end 331 . As a result, measurement accuracy is improved. In addition, the light source 320 also has individual differences, and the center wavelength, half-value width, etc. may differ. can be done.

Specifically, as shown in FIG. 5, for example, a fifth light source 325 that generates light of a fifth wavelength of 575 nm is a spectrum SP1 having a center wavelength λ1 slightly shifted from 575 nm and a half width HW1. Assume it emits light. When the light from the fifth light source 325 passes through the optical bandpass filter 360 , it 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 section 330 . In FIG. 5, the vertical axis represents the relative intensity [%]. That is, the respective intensity distributions are shown with the maximum intensity in each of the spectra SP1 and SP2 set to 100%. The maximum intensity (100%) of the spectrum SP1 and the maximum intensity (100%) of the spectrum SP2 in FIG. 5 do not match, and the absolute values of the light intensity are different.

In the configuration example of FIG. 3, optical bandpass filters 360 are provided for all five light sources 320 . The characteristics of each optical bandpass filter 360 are different for each light source 320 .

As shown in FIGS. 6 and 7, the holding member 340 is for linearly 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. Including a linear passage portion 344 , the optical bandpass filter 360 is arranged between the light source 320 and the incident end 331 so as to block the passage portion 344 . As a result, the light from the light source 320 can 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, it is possible to suppress the occurrence of light loss.

Specifically, the passage portion 344 is a hole extending linearly inside 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 a larger inner diameter than the passage portion 344 . The optical bandpass filter 360 is arranged inside the concave portion 345 at the end on the incident end holding portion 342 side. The optical band-pass filter 360 is pressed against the bottom surface of the recess 345 by the tip surface of the socket 343 via the ring-shaped elastic member 346 . Thereby, the optical bandpass filter 360 is provided so as to block the passage portion 344 in which the incident end 331 is arranged. The optical band-pass filter 360 is fixed by the elastic member 346 while being pressed with a moderate external force that does not cause damage.

<Condenser lens>
6 and 7, the light irradiation unit 10 is provided corresponding to at least one of the plurality of light sources 320, and serves to converge the light emitted from the light source 320 onto the incident end 331. Further includes a condenser lens 370 . 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 portion 330 . As a result, it is possible to improve the utilization efficiency 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 value of the current supplied to the light source 320. .

The condensing lens 370 may be provided for all the five light sources 320, but it is not necessary to provide it if sufficient light intensity can be obtained with a predetermined current value equal to or lower than the rated current. It is effective to provide the condensing lens 370 for a light source with relatively low light intensity among the light sources 320 . In the case of LED light sources, among 660 nm, 405 nm, 800 nm, 340 nm, and 575 nm, the LED light sources of 340 nm and 575 nm emit less light. 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. The second light source 322 and the third light source 323 are not provided.

6 and 7, the holding member 340 is a straight line 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 straight line. The condensing lens 370 is arranged between the light source 320 and the incident end 331 so as to block the passage 347 . 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.

Specifically, socket 343 has a linear passage portion 347 between light source 320 and incident end 331 of optical fiber portion 330 . The condenser lens 370 is held in the socket 343 so as to be fitted in the passage portion 347 and close the passage portion 347 . The configuration examples of FIGS. 6 and 7 show examples in which two condensing lenses 370 are arranged in a straight line. Light from the light source 320 is converged twice by the two condenser lenses 370 and enters the incident end 331 . As a result, the emitted light from the light source 320 in a wider range can enter the incident end 331 without increasing the distance between the light source 320 and the incident end 331 . In order to transmit light through the optical fiber portion 330, the light must be incident on the incident end 331 at an incident angle θ that satisfies a predetermined total reflection condition. Condensing lens 370 is configured to condense light so that light from light source 320 is incident on incident end 331 within the range of incident angle θ. Only one condenser lens 370 may be provided.

<Positional relationship of each part>
Returning to FIG. 3, the plurality of light source holders 341 are arranged side by side while being spaced apart 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 approximately equal intervals on the holding member 340 . The plurality of light sources 320 are spaced apart from each other and arranged side by side by each light source holding portion 341 . In addition, 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 the adjacent light sources 320 . As a result, the light source 320 and the incident end 331 of the optical fiber portion 330 can be arranged at positions close to each other separated by the first distance D1. can be done.

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 greater than D1. Each distance has a relationship of D1<D3<D2.

3, the plurality of optical fiber sections 330 are gathered and bundled along an optical fiber section 330d corresponding to the fourth light source 324, and the optical fiber section 330d corresponding to the fourth light source 324 is configured such that the length from the incident end 331 to the exit end 332 of the plurality of optical fiber portions 330 is the shortest. Here, among the light sources 320, the light emission amount of the fourth light source 324 composed of the LED light source of 340 nm is the smallest. Therefore, with this configuration, the path length of the optical fiber portion 330d corresponding to the fourth light source 324 with a small amount of light emission is the shortest, so the light loss when passing through the optical fiber portion 330 can be reduced accordingly. As a result, it becomes possible to secure a larger amount of light from the fourth light source 324 which emits a small amount of light.

Since the length from the incident end 331 to the exit end 332 increases as the path length for gathering along the optical fiber portion 330d increases, the distance from the central fourth light source 324 increases. Therefore, in the configuration example of FIG. 3, the length relationship from the incident end 331 to the emitting end 332 of each optical fiber portion 330 is the optical fiber portions 330d<330e, 330b<330a, 330c.

(Another configuration example of the light irradiation section)
FIG. 8 shows another configuration example of the light irradiation unit. In the light irradiation unit 10A according to the configuration example of FIG. 8, one outlet 311 is provided in the housing 310 . The arrangement of the plurality of light sources 320 is the same as in the configuration example of FIG. 3, but the arrangement positions may be changed. The five optical fiber sections 330 are held by a holding member 340 at a position where each incident end 331 faces each light source 320 , are twisted together in the middle, and are configured to have one output end 332 . The twisted and integrated part is accommodated in a cylindrical holding member 313 . At the output end 332 , the optical fibers forming each optical fiber portion 330 are mixed so as to be distributed substantially uniformly within the end face of the output end 332 .

The length from the incident end 331 to the exit end 332 is the shortest in 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, also in the configuration example of FIG. 8, the length relationship from the incident end 331 to the emitting end 332 of each optical fiber portion 330 is 330d<330e, 330b<330a, 330c.

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

In the configuration example of FIG. 9 , the light irradiation section 10 includes a light distribution member 380 for distributing light from the bundled output ends 332 to each of the plurality of container installation sections 231 . A plurality of light receiving portions 11 are provided corresponding to the plurality of container setting portions 231 so as to detect the light distributed to each container setting portion 231 by the light distribution member 380 . Accordingly, it is possible to install a plurality of containers 15 in a plurality of container installation portions 231 and collectively measure them. In addition, since the light of each wavelength from the first to fifth wavelengths is uniformly distributed at the output end 332 , the light from the output end 332 is distributed by the light distribution member 380 , so that each container installation portion 231 It can provide light of each wavelength with uniform intensity. As a result, even if the light source 320 is not provided for each of the plurality of container installation portions 231, each container 15 can be easily irradiated with light of uniform intensity.

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 has 12 container installation units 231 and one reference light measurement unit 232 . A total of 12 light receiving units 11 are provided in each of these container installation units 231 . Further, the reference light measuring unit 232 is provided with a reference light receiving unit 236 which is provided separately from the light receiving unit 11 and receives the light from the light irradiation unit 10 without passing through the container 15 . Each light distribution member 380 distributes light to each of the container placement section 231 and the reference light measurement section 232 of the respective detection units 230 and 240 .

The light distribution member 380 is composed of, for example, a bundle of optical fibers similar to the optical fiber section 330 . An incident end 381 of each light distribution member 380 is connected to an outlet 311 provided in the housing 310 of the light irradiation section 10 and arranged to face the exit surface 352 of the uniformizing member 350 . As a result, the light beams of the first to fifth wavelengths are incident on the individual optical fibers forming the incident end 381 of the light distribution member 380 with uniform light intensities. The output 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 connected to the container installation units 231 and the reference light measurement units 232 respectively. there is That is, in the configuration example of FIG. 9, each light distribution member 380 has 13 branched emission ends 382 .

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

The configurations of the individual container installation units 231 and the reference light measurement units 232 are common. The container 15 is not installed in the reference light measuring section 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 irradiation unit 10 passing through the container 15 and the measurement sample. The light receiving section 11 and the reference light receiving section 236 each output an electrical signal corresponding to the received light intensity.

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

In one configuration example, the control unit 400 controls each of the plurality of light sources 320 to periodically emit light one by one. Specifically, as shown in FIG. 12, the control unit 400 sequentially turns on the five light sources 320 (that is, the first light source 321 to the fifth light source 325) for a predetermined light emission time T2 during the light emission cycle T1. Control to emit light is repeated. Each light source 320 is controlled to emit pulsed light with a light emission time T2. The light receiving section 11 and the reference light receiving section 236 individually acquire electrical signals based on the light from the respective light sources 320 at each light emission period T1, with a temporal shift. 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 sample, measurement can be performed at a common light irradiation position. Unlike , the device configuration can be simplified.

For example, when the main power source of the analysis unit 12 and the main power source of the measurement unit 101 are turned on, the control unit 400 controls light emission of at least some of the light sources 320 . More specifically, when the main power of the analysis unit 12 and the main power of the measurement unit 101 are turned on, the control unit 400 performs initial setting of the measurement unit 101 . When the initial setting of the measuring section 101 is completed, the measuring section 101 enters a standby state. The control unit 400 continues the control of causing each of the plurality of light sources 320 to periodically emit light one by one, at least until the measurement unit 101 enters the standby state and receives a shutdown instruction. As a result, it is possible to eliminate variations in the amount of light due to the influence of temperature changes immediately after the start of light emission, and to stabilize the light emission state during measurement. The control unit 400 causes 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 the measurement operation.

On the other hand, each light source 320 has different characteristics depending on the emission wavelength. For example, in the case of the 340 nm LED that constitutes the fourth light source 324, the time required from the start of light emission control until the light amount stabilizes is shorter than that of the other light sources. . Therefore, the control unit 400 performs light emission control for 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 other than during the measurement operation. Thereby, further extension of the life of the light source 320 can be achieved.

In one configuration example, the control section 400 is configured to control the current value supplied to the light source 320 based on the electrical signal from the reference light receiving section 236 (hereinafter referred to as the reference signal). As a result, for example, even when blood coagulation analyzer 100 continues to operate for a long period of time, it is possible to prevent the amount of light from light source 320 from changing. For example, in an LED light source, changes in the temperature of the element tend to affect the amount of light emitted. Therefore, by controlling the current value so that the electric signal of the reference light receiving section 236 is within a predetermined allowable range, the light intensity of the light source 320 can be maintained within an appropriate range for obtaining stable measurement results.

Specifically, the control unit 400 controls the driving circuit 420 of the light source 320 shown in FIG. FIG. 13 shows an example of a drive circuit for controlling light emission of one light source 320. In FIG. The drive circuit 420 includes a constant current circuit 421 , an RC circuit section 422 and a switch section 423 . Light source 320 and constant current circuit 421 are serially connected to the power supply in this order. An RC circuit section 422 and a resistor 424 are connected in parallel to the constant current circuit 421 . A constant current circuit 421 supplies a predetermined constant current to the RC circuit section 422 . The constant current circuit 421 allows the current on the resistor 424 side to fluctuate. RC circuit section 422 is a parallel circuit of variable resistors 425 and 426 and capacitor 427 . RC circuit section 422 delays the rising of the current flowing through light source 320 in accordance with a time constant proportional to the product of the combined resistance of variable resistor 425 and resistor 426 and the capacitance of capacitor 427 . Thereby, the RC circuit section 422 suppresses a large rush current from flowing to the light source 320 at the time of switching.

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

The control unit 400 applies a pulse signal to the gate of the switch unit 423 to control each light source 320 to emit light with a predetermined light emission cycle T1 and a predetermined light emission time T2. Since the current flowing through the RC circuit section 422 is kept constant by the constant current circuit 421, changing the resistance value of the variable resistor 425 changes the value of the current flowing through the resistor 424 side. The current value flowing through the light source 320 is proportional to the ratio (R1/R2) of the resistance value R1 of the RC circuit section 422 including the variable resistor 425 and the resistor 426 and the resistance value R2 of the resistor 424 . The control section 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 from the reference light receiving section 236 .

The control unit 400 controls the current value of the light source 320 based on the reference value V1 and the lower limit value V2 of the reference signal RS, as shown in FIG. 14, for example. 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 when the light emission control of the light source 320 is started. The amount of light emitted from the LED light source changes depending on the ambient temperature of the LED light source and aging of the LED elements. Therefore, when the amount of light from the light source 320 decreases over time, the intensity of the reference signal RS gradually decreases. The control unit 400 performs control to correct the current value CV of the light source 320 when the intensity of the reference signal RS reaches the lower limit value V2. Specifically, the control unit 400 calculates the corrected current value based on the following formula (1).
Current value after correction = (standard value of reference signal/current value of reference signal) x 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 current value after correction. As a result, the amount of light from the light source 320, which decreases over time, increases each time the reference signal RS reaches the lower limit value V2 and is maintained within the appropriate range between the reference value V1 and the lower limit value V2.

(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 sample analysis processing according to a program stored in the storage unit 452 . Storage unit 410 includes storage media such as ROM, RAM, and hard disk, and stores programs and data necessary for processing and control of arithmetic processing unit 451 . The display unit 453 includes display means such as a monitor. The input unit 454 includes input means such as a keyboard and a mouse, and accepts user operation input. The analysis unit 12 is configured by, for example, a personal computer.

In the configuration example of FIG. 16 , the analysis unit 12 detects a plurality of time points corresponding to each of the plurality of light sources 320 from the electrical signals output from the light receiving unit 11 for the sample in the container 15 installed in the container installation unit 231 . Create series data 460 . As described above, the light from the five light sources 320 of the light irradiation unit 10 is sequentially supplied to the container installation unit 231 at each predetermined light emission period T1. Therefore, when the container 15 is placed on the container setting portion 231, the lights from the five light sources 320 are transmitted through the container 15 and the measurement sample and detected by the light receiving portion 11 in order. As a result, five electrical signals respectively corresponding to the lights of the first to fifth wavelengths are output from the light receiving section 11 to the control section 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 storage unit 410 .

During the measurement time T3 during which the container 15 is set on the container setting part 231, one piece of data is obtained for each light emission cycle T1 for each of the light of the first to fifth wavelengths. The five electrical signals have intensities reflecting the state of the measurement sample irradiated with light. Each time-series data 460 includes T3/T1 pieces of data and is acquired for each wavelength. When the light of the first to fifth wavelengths is applied, five types of time-series data 460 are acquired.

The analysis unit 12 selects, for example, time-series data 460 corresponding to a measurement item from among multiple pieces of time-series data 460 and analyzes the sample. By acquiring the time-series data 460 for each wavelength and selecting the time-series data 460 to be used for analysis in this way, the control for acquiring the time-series data 460 can be shared regardless of the measurement items. For example, since it is not necessary to perform control to read 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 cycle T1, control regarding acquisition of the time-series data 460 can be simplified. .

If the measurement item of the sample in the container 15 installed in the container installation unit 231 is a blood coagulation measurement measurement item, the analysis unit 12 extracts the coagulation time and the sample from the time-series data 460 corresponding to the first wavelength. Calculate the concentration or activity of the ingredients involved. That is, the analysis unit 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 changes in the amount of light received in the time-series data 460 . As a result, the coagulation time can be obtained based on the light from the first light source 321 provided for coagulation time measurement, so that accurate and stable measurement results can be obtained.

Analysis unit 12 calculates the coagulation time by, for example, a percent detection method. Specifically, the analysis unit 12 sets the intensity of the received light immediately after addition of the reagent to 0%, the intensity of the received light at the end of the coagulation reaction to 100%, and obtains the time when the intensity of the received light reaches a predetermined value from the reaction curve. , the coagulation time. In addition, the analysis unit 12 prepares in advance a calibration curve that relates the coagulation time and the activity or concentration of the target component of the measurement item and records it in the storage unit 452. Based on the calculated coagulation time and the calibration curve, Get the concentration or activity of the target component of the measurement item.

If the measurement item of the sample in the container 15 installed in the container installation unit 231 is a synthetic substrate measurement item, the analysis unit 12 determines the components contained in the sample from the time-series data 460 corresponding to the second wavelength. Calculate the concentration or activity of 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 accurate and stable measurement results can be obtained. In a configuration in which the fourth light source 324 is provided in addition to the second light source 322, the analysis unit 12 determines the concentration of the component contained in the sample from the time-series data 460 corresponding to the second wavelength and/or the fourth wavelength. Or calculate the activity. The analysis unit 12 analyzes the color development process of the chromogenic synthetic substrate based on the electrical signal corresponding to the light of the second wavelength or the fourth wavelength output from the light receiving unit 11 . That is, the analysis unit 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 determines the degree of color development based on the change in the amount of light received in the time-series data 460. to analyze.

In synthetic substrate measurement, the analysis unit 12 obtains the amount of change in absorbance by, for example, the Rate method or the Vlin method. The Rate method is a method of analyzing changes 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. In the Vlin method, a start point and an end point are set 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, and the time between the set start point and the end point is measured. This is a method of analyzing the amount change and calculating the amount of absorbance change per unit time by linear regression. The analysis unit 12 prepares in advance a calibration curve that relates the amount of change in absorbance and the activity or concentration of the target component of the measurement item and records it in the storage unit 452. Based on the calculated amount of change in absorbance and the calibration curve, Get the concentration or activity of the target component of the measurement item.

If the measurement item of the sample in the container 15 installed in the container installation unit 231 is an immunonephelometry measurement item, the analysis unit 12 determines from the time-series data 460 corresponding to the third wavelength that Calculate the concentration or activity of the component. As a result, immunonephelometry can be performed based on the light from the third light source 323 provided for immunonephelometry, and 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 unit 12 determines the concentration of the component contained in the sample from the time-series data 460 corresponding to the third wavelength and/or the fifth wavelength. Or calculate the activity. The analysis unit 12 analyzes the process of 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 unit 11 . That is, the analysis unit 12 selects the time-series data 460 acquired based on the electrical signal of the light from the third light source 323 or the fifth light source 325, and based on the change in the amount of light received in the time-series data 460, antigen-antibody Aggregation rate by reaction is analyzed.

In the immunoturbidimetric measurement, the analysis unit 12 obtains the amount of change in absorbance by, for example, the Rate method or the Vlin method, similarly to the synthetic substrate measurement. The analysis unit 12 prepares in advance a calibration curve that relates the amount of change in absorbance and the activity or concentration of the target component of the measurement item and records it in the storage unit 452. Based on the calculated amount of change in absorbance and the calibration curve, Get the concentration or activity of the target component of the measurement item.

When the light-receiving unit 11 receives the transmitted light of the light irradiated to the measurement sample, the light-receiving intensity is maximum immediately after addition of the reagent, and decreases with the lapse of time. On the other hand, when the light receiving section 11 receives the scattered light of the light irradiated to the measurement sample, the received light intensity is the lowest immediately after addition of the reagent and increases with the lapse of time. Transmitted light and scattered light differ in the direction in which the received light intensity increases and decreases over time, but they are similar in that the coagulation time or absorbance change amount is calculated and the measurement items are analyzed using a calibration curve.

(Measurement operation of blood coagulation analyzer)
The measurement operation of blood coagulation analyzer 100 in the configuration example of FIG. 2 will be described with reference to FIGS. 17 and 18. FIG. Operation control of the measurement unit 101 and the transport unit 102 is performed by the control unit 400 . The analysis unit 12 is controlled by the arithmetic processing unit 451 . Hereinafter, FIG. 18 will be referred to for each part of the measurement part 101 and the transport part 102 .

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

After completing the initial setting, the control unit 400 shifts to the standby state in step S2A. After transitioning to the standby state, the control unit 400 causes the first light source 321 other than the fourth light source 324, the second light source 322, the third light source 323, and the fifth light source 325 to periodically emit light one by one. Start controlling. Light emission control continues until a shutdown instruction, which will be described later, is received.

In the standby state, the control section 400 waits for a measurement start instruction from the analysis section 12 . The arithmetic processing unit 451 determines whether to start measurement in step S2B. The arithmetic processing unit 451 repeats step S<b>2</b>B and waits until receiving an operation input for starting measurement by the user using the input unit 454 . Upon receiving the user's input operation to start measurement, the arithmetic processing unit 451 transmits an instruction to start measurement to the control unit 400 in step S3B.

Upon receiving the measurement start instruction 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 section 400 starts light emission control for the fourth light source 324 . As a result, the five light sources 320 are controlled to periodically emit light one by one. Further, the control unit 400 controls the transport unit 102 to transport the sample rack 105 so that the sample container 106 to be aspirated is arranged at the sample aspirating position. While the sample rack 105 is being transported, the reader 103 reads the identification information of the sample rack 105 and the sample container 106 .

In step S4A, the control unit 400 transmits to the analysis unit 12 an inquiry about the measurement order including the read identification information. Upon receiving the measurement order inquiry, the arithmetic processing unit 451 acquires the sample measurement order 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.

Upon receiving the measurement order, the control unit 400 causes the sample dispensing unit 110 or 120 to aspirate the sample and dispense it into a new container 15 in step S5A. The control unit 400 controls the measurement unit 101 to heat the container 15 on the heating table 220 and add the reagent to the container 15 by the reagent dispensing unit 200 or 210 in step S6A. Thereby, a measurement sample containing the specimen and the reagent is prepared in the container 15 . In step S7A, the control section 400 controls the measurement section 101 to install the container 15 containing the measurement sample in the container installation section 231 of the detection unit 230 or 240. FIG. Details of the operation of the measurement unit 101 in steps S5A to S10A will be described later.

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 from the light irradiation section 10 is sequentially irradiated. As the container 15 is placed on the container placement portion 231, the light from the light irradiation portion 10 is applied to the container 15, and the light receiving portion 11 receives the light transmitted through the container 15 and outputs an electric signal. The electrical signal is transmitted to the analysis section 12 via the control section 400 .

In step S8A, the control section 400 determines whether or not a predetermined measurement time T3 corresponding to the measurement item specified in the measurement order has elapsed after the container 15 was placed on the container placement section 231. FIG. Acquisition of the electrical signal and transmission to the analysis unit 12 are continued during the predetermined measurement time T3. In step S5B, the arithmetic 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.

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

When the measurement time T3 elapses in step S8A, the control unit 400 advances to step S9A to remove the container 15 from the container setting unit 231, and discards the removed container 15 to the disposal port 260 or 261 in step S10A. Transfer of container 15 is accomplished by gripping mechanism 180 or 250 .

As described above, in steps S7A to S10A, the control unit 400 installs the container 15 containing the measurement sample in the container installation unit 231, and corresponds to the measurement item of the sample in the container 15 installed in the container installation unit 231. After the measurement time T3 elapses, the gripping mechanism 180 or 250 is controlled so that the container 15 is taken out from the container placement section 231 and the container 15 is discarded into the disposal port 260 or 2611 . As a result, only by varying the installation time of the container 15 on the container installation section 231, measurements corresponding to various measurement items can be performed with a common device configuration.

On the other hand, in the analysis unit 12, in step S6B, the arithmetic processing unit 451 selects the time series data 460 corresponding to the measurement item from among the five time series data 460 created. In step S7B, the arithmetic processing unit 451 uses the selected time-series data 460 to perform analysis and generate measurement results. In step S8B, the arithmetic processing unit 451 performs recording of the obtained measurement result in the storage unit 452, display of the measurement result on the display unit 453, and the like.

In step S11A, the control section 400 determines whether or not there is the next sample rack 105 in the transport section 102. If there is the next sample rack 105, the process returns to step S4A to continue the measurement operation. If there is no next sample rack 105, in step S12A, it is determined whether or not a shutdown instruction has been received from the analysis unit 12, and the standby state is entered.

On the other hand, in step S9B, the arithmetic processing unit 451 determines whether or not to perform shutdown processing. When the shutdown process is not performed, the arithmetic processing unit 451 continues the analysis operations from steps S4B to S8B based on the electrical signal transmitted along with the measurement operation of the measurement unit 101. FIG. Upon receiving a shutdown input operation from the user, the arithmetic processing unit 451 transmits a shutdown instruction to the control unit 400 in step S10B.

When the shutdown instruction is received from the analysis unit 12, the control unit 400 proceeds to step S13A and performs predetermined shutdown processing. In the shutdown process, the controller 400 stops light emission control of each light source 320 . Thereby, light irradiation from the light irradiation unit 10 is stopped.

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

(Measurement operation of the measurement unit)
Next, details of the operation of the measurement unit 101 in steps S5A to S10A will be described. As shown in FIG. 18, the operation of the measurement unit 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. do.

<Measurement by detection unit 230>
When the sample is measured by the detection unit 230 , the sample dispensing section 110 aspirates the sample from the sample container 106 at the sample aspirating position 501 . The specimen dispensing unit 110 dispenses specimens into the containers 15 held on the container table 130 . The container table 130 rotates in the circumferential direction to transfer the container 15 to a position where the specimen dispensing section 120 can aspirate. The sample dispensing unit 120 aspirates the sample in the container 15 and dispenses the sample into the container 15 held by the transfer unit 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 picks up the container 15 on the transfer section 140 and places it on the heating table 220 . If necessary, the gripping mechanism 222 transfers 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, gripping mechanism 222 returns container 15 to heating table 220 .

When the heating by the heating table 220 is completed, the container 15 transferred to the predetermined take-out position by the heating table 220 is taken out by the grasping mechanism 180 and transferred to the reagent dispensing position 506 . A reagent dispensing unit 200 dispenses a reagent into the container 15 . After dispensing the reagent, the gripping mechanism 180 installs the container 15 on one of the container installation portions 231 of the detection unit 230 . As the container 15 is placed on the container placement portion 231, the light from the light irradiation portion 10 is applied to the container 15, and the light receiving portion 11 receives the light transmitted through the container 15 and the measurement sample and outputs an electrical signal. The electrical signal is transmitted to the analysis section 12 via the control section 400 . During the measurement time T3, acquisition of electrical signals is continued, and time-series data 460 is generated for each wavelength of light in the analysis unit 12 . After the measurement time T3 elapses, the gripping mechanism 180 takes out the container 15 from the container installation section 231 and transfers it to the disposal port 260 . The analysis unit 12 selects the 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 on the storage unit 452 .

<Measurement by detection unit 240>
When the sample is measured by the detection unit 240 , the sample dispensing section 110 aspirates the sample from the sample container 106 at the sample aspirating position 501 . The specimen dispensing unit 110 dispenses specimens into the containers 15 held on the container table 130 . The container table 130 rotates in the circumferential direction to transfer the container 15 to a position where the specimen dispensing section 120 can aspirate. The sample dispensing unit 120 aspirates the sample in the container 15 and dispenses the sample into the container 15 held by the transfer unit 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 picks up the container 15 on the transfer section 170 and places it on the heating table 220 . If necessary, the gripping mechanism 222 transfers 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, gripping mechanism 222 returns container 15 to heating table 220 .

When the heating by the heating table 220 is completed, the container 15 transferred to the predetermined take-out position by the heating table 220 is taken out by the grasping mechanism 250 and transferred to the reagent dispensing position 507 . A reagent dispensing unit 210 dispenses a reagent into the container 15 . After dispensing the reagent, the gripping mechanism 250 installs the container 15 on one of the container installation portions 231 of the detection unit 240 . The measurement operation in detection unit 240 is similar to detection unit 230 . After a predetermined measurement time has elapsed, the gripping mechanism 250 takes out the container 15 from the container installation section 231 and transfers it to the disposal port 261 . The operation of the analysis unit 12 is the same as when the detection unit 230 performs measurements.

The sample dispensing unit 120 can also aspirate the sample from the sample container 106 at the sample aspirating position 502 and directly dispense the sample into the container 15 transferred to the sample dispensing position 504 or 505 . When the sample is dispensed into the container 15 at the sample dispensing position 504, the detection unit 230 performs measurement. When the sample is dispensed into the container 15 at the sample dispensing position 505, the detection unit 240 performs measurement. The operation after dispensing is as described above.

It should be noted that the embodiments disclosed this time should be considered as examples and not restrictive in all respects. The scope of the present invention is indicated by the scope of the claims rather than the description of the above-described embodiments, and includes all modifications within the meaning and scope equivalent to the scope of the claims.

10: light irradiation unit, 11: light receiving unit, 12: analysis unit, 15: container, 20: light source, 21: first light source, 22: second light source, 23: third light source, 30: optical fiber unit, 31: Incident end 32: Emitting end 40: Holding member 41: Light source holder 42: Incident end holder 100: Blood coagulation analyzer 180: Grasping mechanism 231: Container installation unit 236: Reference light receiving unit , 250: gripping mechanism, 260: disposal port, 261: disposal port, 320: light source, 321: first light source, 322: second light source, 323: third light source, 324: fourth light source, 325: fifth light source, 330 (330a to 330e): optical fiber portion, 331: incident end, 332: outgoing end, 333: optical fiber, 340: holding member, 341: light source holding portion, 342: incident end holding portion, 344: passage portion, 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 (19)

Generate light with different wavelengths from multiple light sources,
The light from the plurality of light sources is made incident on each of the plurality of optical fiber portions provided corresponding to the plurality of light sources, and the light source having a lower light intensity than the other light sources among the plurality of light sources , by condensing light onto the corresponding optical fiber portion via a condensing lens, the amount of light incident from the light source having a low light intensity is brought close to the amount of light incident from the other light source;
irradiating a container containing a measurement sample containing a specimen and a reagent with light from the plurality of light sources through the plurality of optical fiber units;
detecting light emitted from the container;
A blood coagulation analysis method, comprising analyzing the specimen based on the detected light. The plurality of light sources includes a first light source for generating light of a first wavelength, a second light source for generating light of a second wavelength different from the first wavelength, the first wavelength and the second light source. A blood coagulation analysis method according to claim 1, comprising a third light source for generating light of a third wavelength different from the wavelength. 3. The blood coagulation analysis method according to claim 1, wherein said plurality of light sources include a first light source for coagulation method, a second light source for synthetic substrate method, and a third light source for agglutination method. 4. The blood coagulation analysis according to claim 2 or 3, wherein said plurality of light sources further comprises a fourth light source for generating light of a fourth wavelength different from said first light source, said second light source and said third light source. Method. 5. The plurality of light sources of claim 4, further comprising a fifth light source for generating light of a fifth wavelength different from the first light source, the second light source, the third light source and the fourth light source. Blood coagulation analysis method. The blood coagulation analysis method according to any one of claims 1 to 5, wherein each of said plurality of light sources is an LED. The blood coagulation analysis method according to any one of claims 1 to 6, wherein each of said plurality of light sources emits light periodically. Analyzing the sample based on the time-series data of the wavelength corresponding to the measurement item of the sample among the time-series data corresponding to each wavelength obtained by periodically emitting light from the plurality of light sources. The blood coagulation analysis method according to 7. causing light from the plurality of light sources to enter the respective incident ends of the plurality of optical fiber sections;
The blood coagulation analysis method according to any one of claims 1 to 8, wherein the container is irradiated with the light emitted from the emission ends of the plurality of optical fiber units. Acquiring time-series data of wavelengths corresponding to measurement items of the specimen among time-series data corresponding to each wavelength obtained by light generated from each of the plurality of light sources;
In the case of a measurement item using a coagulation method, the coagulation time, the concentration or activity of a component contained in the sample is calculated from the time-series data corresponding to the first wavelength,
In the case of measurement items using the synthetic substrate method, calculating the concentration or activity of the component contained in the sample from the time-series data corresponding to the second wavelength,
3. The blood coagulation analysis method according to claim 2, wherein, in the case of a measurement item using an agglutination method, the concentration or activity of a component contained in the sample is calculated from the time-series data corresponding to the third wavelength. a light irradiation unit that irradiates a container containing a measurement sample containing a specimen and a reagent with light;
a light receiving unit for receiving light emitted from the light emitting unit;
an analysis unit for analyzing the specimen based on the electrical signal output from the light receiving unit;
The light irradiation unit is
a plurality of light sources with different wavelengths;
a plurality of optical fiber portions provided corresponding to each of the plurality of light sources;
By condensing light from a light source having a lower light intensity than other light sources among the plurality of light sources into a corresponding optical fiber portion, the amount of light incident on the corresponding optical fiber portion from the light source having a lower light intensity is reduced to the above and a condensing lens that approximates the amount of light incident on the corresponding optical fiber portion from another light source . The plurality of light sources includes a first light source for generating light of a first wavelength, a second light source for generating light of a second wavelength different from the first wavelength, the first wavelength and the second light source. 12. The blood coagulation analyzer of claim 11, comprising a third light source for generating light of a third wavelength different from the wavelength. 13. The blood coagulation analyzer according to claim 11, wherein said plurality of light sources include a first light source for coagulation method, a second light source for synthetic substrate method, and a third light source for agglutination method. 14. The blood coagulation analysis according to claim 12 or 13, wherein said plurality of light sources further comprises a fourth light source for generating light of a fourth wavelength different from said first light source, said second light source and said third light source. Device. 15. The plurality of light sources of claim 14, further comprising a fifth light source for generating light of a fifth wavelength different from the first light source, the second light source, the third light source and the fourth light source. Blood coagulation analyzer. The blood coagulation analyzer according to any one of claims 11 to 15, wherein each of said plurality of light sources is an LED. a plurality of light source holding units that hold the plurality of light sources, and a plurality of incident end holding units that hold the incident ends of the plurality of optical fiber units facing the light sources held by the light source holding units; The blood coagulation analyzer according to any one of claims 11 to 16, comprising: 11. Each of the plurality of optical fiber sections includes a plurality of optical fibers, and the plurality of optical fibers corresponding to the respective light sources are mixed and bundled so as to be distributed substantially uniformly at the output end. 18. The blood coagulation analyzer according to any one of items 1 to 17. Further comprising a control unit for controlling the light source,
The blood coagulation analyzer according to any one of claims 11 to 18, wherein said controller controls each of said plurality of light sources to emit light periodically.

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