JPH11295305A - Mechanism for agitating reactant liquid in whole blood hemocyte immunoassay device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To obtain a reactant liquid agitating mechanism capable of agitating a reagent and a whole blood sample for immunoassay through the use of a dispenser for transferring liquids used for immunoassay, contributing to the compactness and simplification of a device constitution. SOLUTION: In a whole blood hemocyte immunoassay device provided with a immunoassay part to perform immunoassay and a hemocyte number measuring part to measure the number of hemocytes, the same whole blood sample is used for both measuring parts, and the results of immunoassay are corrected through the use of a hematocrit value obtained by hemocyte number measurement. In this case, a flow photometric cell 20 for immunoassay is connected via a channel to the bottom part of a sample receiving cell 19 to house a reagent and a whole blood sample for immunoassay. A dispenser 23 for transferring liquids is connected to the outlet-side channel of the flow photometric cell 20 via a three-way solenoid vale 12b. Then by reciprocating a reactant liquid in the sample receiving cell 19 between the sample receiving cell 19 and the flow photometric cell 20 by the dispenser 23, the reactant liquid is agitated.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention includes an immunoassay section for performing an immunoassay and a blood cell count and a measurement section for performing a blood cell count measurement. In both of these sections, the same whole blood sample is used and the result of the immunoassay is obtained. The present invention relates to a reaction liquid stirring mechanism in a whole blood blood cell immunoassay apparatus which is corrected using a hematocrit value obtained by a blood cell count measurement.

[0002]

2. Description of the Related Art There is an inflammatory marker as a technique for observing the presence, degree, and progress of inflammation occurring in the body.
Representative of this inflammation marker are white blood cell count,
There are blood sedimentation value, acute phase protein, serum protein fractionation value, serum sialic acid, and the like, and these are measured in combination to help diagnose inflammation. Among them, measurement of leukocyte count and C-reactive protein (CRP), which is an acute phase protein, is particularly useful for diagnosing inflammation and infectious disease. The blood cell counter was measured individually, and the latter was measured individually using an immunoassay device.

However, when the measurement is performed individually using the above-mentioned blood cell counter and immunoassay device, the sample (specimen) used for the measurement is whole blood in the former, and is mainly serum in the latter. When obtaining whole blood as a specimen, it is necessary to separately collect blood in a state containing an anticoagulant and in a state without the anticoagulant, while the serum needs to wait for blood coagulation and perform centrifugation. Is not suitable for facilities that cannot always have a specialized laboratory technician, such as small clinics and clinics, remote clinics, holiday clinics, and emergency laboratories.

[0004] On the other hand, there is an immunoassay apparatus that can measure whole blood, but when whole blood is used as a sample, the target immunoassay is not present in blood cells, but only in serum / plasma. In addition, an error occurs due to a variation in the hematocrit value having a relatively large individual difference.

[0005]

The above-mentioned whole blood blood cell immunoassay apparatus has been researched and developed by the present inventors to solve such problems of the prior art, and has already been disclosed in Japanese Patent Application No. 9-279.
No. 963. The whole blood cell immunoassay has the following advantages. Since the result of the immunoassay is corrected using the hematocrit value obtained by the blood cell count measurement, an accurate immunoassay can be performed even though whole blood is used as the sample. Since blood cell counting and measurement of immunity parameters can be performed simultaneously with whole blood, specimens need only be handled with whole blood, and there is no need for serum separation, and measurement can be started shortly after blood collection.
The measurement can be easily performed even by a non-specialized inspection technician. As a result of the above, it is particularly useful for emergency and early diagnosis of inflammation and infectious diseases, as well as small clinics and clinics, remote clinics, holiday clinics, emergency laboratories, etc.
A desired inspection can be performed. The probe unit, calculation / control unit, display / output device, etc. can be used in common for blood cell count measurement and immunoassay. Can be achieved.

The present invention is a further improvement of the whole blood blood cell immunoassay apparatus described above. The present invention utilizes a liquid transfer infusion device used for immunoassay, and provides a reagent for immunoassay and whole blood. It is an object of the present invention to provide a reaction liquid stirring mechanism that can efficiently stir a sample and contribute to downsizing and simplification of the device configuration.

[0007]

In order to solve the above-mentioned problems, the present invention comprises an immunoassay section for performing an immunoassay and a blood cell count and a measurement section for performing a blood cell count measurement. In a whole blood blood cell immunoassay apparatus that uses a sample and corrects the result of the immunoassay using the hematocrit value obtained by the blood cell count measurement, the reaction solution stirring mechanism is configured as follows. That is, a flow photometric cell for immunoassay is connected to the bottom of a sample receiving cell containing a reagent for immunoassay and a whole blood sample via a flow path, and a three-way solenoid valve is connected to a flow path on the outlet side of the flow photometric cell. A liquid transfer infusion device is connected via the, and prior to the immunoassay, the reaction solution in the sample receiving cell is reciprocated back and forth between the sample receiving cell and the flow photometric cell by the injector. The liquid is agitated.

[0008] According to the reaction solution stirring mechanism having the above-described structure, the three-way solenoid valve communicates the flow metering cell with the infusion device, and the sample receiving cell contains the reagent for immunoassay and the whole blood sample. When the infusion set for liquid transfer slides a plurality of times to reciprocate the reaction solution in the sample receiving cell back and forth between the sample receiving cell and the flow photometric cell, a connection portion between the sample receiving cell and the flow path, Since the flow path cross section changes at the inlet and the outlet of the flow photometric cell, respectively, turbulence occurs in the reaction liquid at those portions where the flow path cross section changes, and stirring is performed efficiently. .

If the reaction solution is stirred by inserting a rotor such as a propeller into the sample receiving cell, a means for washing the rotor and a means for moving the rotor into and out of the sample receiving cell may be used. , They need space for them,
The mechanical vibrations caused by these drives are likely to adversely affect the optical measurement by the flow photometering cell, but according to the above configuration, the reaction liquid is only reciprocated back and forth, so that the adverse effects due to the mechanical vibrations In addition, the liquid is reciprocated using a liquid transfer infusion device used for immunoassay, and the infusion device is also used for liquid movement during immunoassay and liquid movement during stirring. Therefore, the device configuration can be made compact and simple.

[0010]

Embodiments of the present invention will be described with reference to the drawings. 1 to 8 show an example of a whole blood blood cell immunoassay employing a reaction liquid stirring mechanism according to the present invention.

First, FIG. 2 is a perspective view of the whole blood cell immunoassay apparatus with the side panel removed, and FIG. 3 is a view schematically showing the entire configuration of the whole blood cell immunoassay apparatus. is there. FIG. 4 is a diagram of a main part of the whole blood blood cell immunoassay apparatus viewed from above, and FIG. 5 is a view schematically showing a configuration of a main part of the whole blood cell immunoassay apparatus.

In these figures, 1 is an apparatus case,
On the front surface 2 side, a sample setting section 5 for setting a sample container 4 containing whole blood 3 as a sample is formed in a state in which it is recessed inward. Reference numeral 6 denotes a measurement key constituted by a door 7 for opening and closing the sample setting unit 5, and is configured to be turned on (switch ON) by closing the door 7. The door 7 is configured to swing back and forth with the lower end as a fulcrum in the front-rear direction. Inside the door 7, a plurality of sample containers 4 of different sizes can be selected and set on the upper surface. The sample container holder 8 having the above-mentioned hole is provided so as to be rotatable around the vertical axis and swingable in the front-rear direction integrally with the door 7.

Below the side surface 9 of the apparatus case 1, an immunoassay unit 10 for performing an immunoassay and a blood cell counting / measuring unit 11 for performing a blood cell measurement are viewed from the front side in order from the side closer to the front surface 2. An electromagnetic valve portion 12 that is arranged in a straight line and includes a plurality of electromagnetic valves 12a is provided. Above the side surface 9, the immunoassay unit 1 arranged in a straight line between the sample setting unit 5 and the blood cell count measurement unit 11 is arranged.
Probe unit 13 as a sampling mechanism that moves linearly along zero and blood cell count measurement unit 11
Is provided.

In FIG. 3, reference numeral 14 denotes a dispenser, 15 denotes a diluting liquid container, 16 denotes a hemolytic reagent container, and 17 denotes a liquid discharging pump. These 15 to 17 are all connected to the electromagnetic valve section 12. I have. Reference numeral 18 denotes a waste liquid container connected to the pump 17.

In the present embodiment, the immunoassay section 10 is configured to measure CRP (C-reactive protein which is an acute phase protein) by a latex immunoturbidimetry. That is, in FIGS. 3 and 5, reference numeral 19 denotes a reagent receiving cell having an open top surface, and a light irradiating portion 20 a formed of a light emitting diode on both sides is provided at the bottom of the sample receiving cell 19.
And a photodetector 20b comprising a photodiode
A flow photometric cell 20 for RP measurement is connected via a flow path 21. A liquid transfer infusion device 23 is connected to the flow path 22 on the outlet side of the flow photometric cell 20 via the three-way solenoid valve 12b. The downstream side of the three-way solenoid valve 12b is connected to the pump 17 via the solenoid valve part 12. Reference numerals 24, 25, and 26 denote reagent containers containing reagents used for CRP measurement, respectively.
Reagent), a buffer (hereinafter, referred to as R2 reagent), and an anti-human CRP-sensitized latex immunoreagent (hereinafter, referred to as R3 reagent).

The reagent receiving cell 19 and the reagent container 24
Are arranged in a straight line with respect to the setting position of the sample container 4 in the sample setting section 5, and these 19 to 26 are arranged in a straight line.
Is a lid 28 that swings up and down by a solenoid 27.
It is configured to be opened and closed in a lump. Reference numeral 29 denotes an electronic cooler 30 made of, for example, a Peltier device.
In the example shown, reagents R2 and R
3 are accommodated therein.

The infusion device 23 not only controls the flow of the reaction solution (reagent for immunoassay and the whole blood sample) in the sample receiving cell 19 to the flow photometric cell 20 at the time of CRP measurement. The sample receiving cell 19, the flow metering cell 20, and the like constitute a reaction solution stirring mechanism as described below. That is, as shown in FIG. 1, in a state where the reaction solution is contained in the sample receiving cell 19, the infusion device 23 slides several times before the CRP measurement, so that the inside of the sample receiving cell 19 is moved. The reaction solution of (1) is transferred to the sample receiving cell 19 and the flow photometric cell
It is configured to reciprocate back and forth over 0.

More specifically, the dispenser 23 is configured such that its sliding stroke is controlled.
A sample receiving cell 19, R1 reagent, R2 reagent, and the specimen at the time when the (whole blood) 3 is accommodated, by a stroke a set corresponding to their total L _1, syringe pump 23 several times (For example, three times), the three-way solenoid valve 12b slides in a state where the flow metering cell 20 communicates with the infusion set 23 to reciprocate the reaction solution back and forth, and the first reaction solution of the carried out stirring at the time of the reaction liquid R3 reagent was added, syringe pump 23 several times until the stroke b end which is set to correspond to the total amount of them L ₂ (for example, 3 times),
By sliding, the reaction liquid reciprocates back and forth,
It is configured to perform the second stirring.

During the CRP measurement, the infusion set 23 slides only once to the end of the stroke b so that the reaction solution flows through the flow photometering cell 20. The stroke of the dispenser 23 and the length of the flow paths 21 and 22 are such that when the dispenser 23 slides to the stroke b end, the foremost end P of the reaction solution in the flow paths 21 and 22 is a three-way solenoid valve. 12b is located upstream (between the three-way solenoid valve 12b and the flow metering cell 20), and the tail Q is located upstream of the flow metering cell 20 (in the illustrated example, within the channel 21 and the sample receiving cell 19). Near the exit). In this state, the three-way solenoid valve 12b switches the flow path, shuts off the infusion device 23, and sets the flow path before and after the three-way electromagnetic valve 12b (the flow path on the flow photometric cell 20 side and the pump 17 side). When the pump 17 is connected, the pump 17 sucks the reaction liquid in the flow path and discharges it to the waste liquid container 18.

According to the reaction solution stirring mechanism, when the reaction solution reciprocates back and forth between the sample receiving cell 19 and the flow photometric cell 20, the connection between the sample receiving cell 19 and the flow path 21, the inlet of the flow photometric cell 20 At the outlet and the outlet, respectively, the cross section of the flow path changes, so that turbulent flow occurs in the reaction liquid at these portions where the cross section of the flow path changes, as shown in FIG.
Since there are many sites where turbulence occurs, stirring is performed efficiently.

Next, in this embodiment, the blood cell counting / measuring unit 11 uses the electric resistance method to measure the WBC (white blood cell count), RBC (red blood cell count), PLT (platelet count), MC
It is configured to measure V (red blood cell volume), Hct (hematcrit value), and Hgb (hemoglobin concentration) by an absorption spectrophotometric method in the cyanmethemoglobin method. That is, in FIG.
Is a WBC / Hgb blood cell count measurement cell (hereinafter simply referred to as WBC
Measurement electrode 31 for measuring WBC
a, 31b and light irradiator 31 for measuring Hgb
c, a light receiving section 31d. 32 is RBC / PLT
With a blood cell count measurement cell (hereinafter simply referred to as RBC cell),
Measuring electrodes 32a for measuring RBC and PLT,
32b. These cells 31 and 32 are shown in FIG.
As shown in the figure, the reagent receiving cell 1 in the immunoassay section 10
9 and reagent containers 24-26. The WBC cell 31 also serves as a waste liquid chamber for cleaning a sampling nozzle 40 described later.

Further, the probe unit 13 is configured, for example, as follows. That is, in FIG. 2 and FIG. 4, reference numeral 33 denotes a nozzle unit, which is appropriately connected to a timing belt 35 provided in a horizontal direction along a base member 34 which is provided upright. It is configured to be fixed by a member 36 so that it can reciprocate horizontally.

More specifically, the nozzle unit 33 is provided between the sample setting section 5 and the blood cell counting / measuring section 11 for performing blood cell measurement. It is configured to reciprocate almost directly above the reagent containers 24-26 of the part 10, the reagent receiving cell 19, the WBC cell 31, and the RBC cell 32. 37 is a motor for driving the timing belt 35, 38 is a pair of guide members for guiding a guided member 39 provided in the nozzle unit 33, and these are attached to the base member 34 via appropriate members. .

Numeral 40 denotes a sampling nozzle, which is attached to a nozzle holder 42 which moves vertically in the nozzle unit 33 by a timing belt 41. The distal end side (lower end side) of the sampling nozzle 40 is configured to pass through a sampling nozzle cleaning device 43 provided in the nozzle unit 33 to clean the outer periphery of the distal end portion. 44 is a motor for driving the timing belt 41. A sensor 45 detects whether or not the sampling nozzle 40 is at the home position (fixed position).

In FIG. 3, reference numeral 46 designates a microcomputer as a control / arithmetic device for controlling various parts of the apparatus comprehensively and performing various arithmetic operations using outputs from the immunological measurement part 10 and the blood cell count measurement part 11. (MP
U) and 47 are drivers for transmitting drive signals to the electromagnetic valve section 12 and the motors 37 and 44 of the probe unit section 13 based on commands from the MPU 46, and 48 are output signals from the immunological measurement section 10 and the blood cell count measurement section 11. To process the MPU
A signal processing unit to be sent to 46, 49 is a device for displaying a result obtained by processing in the MPU 46 and the like, for example, a color display, and 50 is a printer as an output device.

In FIG. 3, the dotted lines show the flow of the specimen 3 and various reagents, the slightly thick dashed line shows the control signal, and the thin dashed line shows the flow of the signal obtained by the measurement. .

The operation of the whole blood cell immunoassay apparatus having the above configuration will be described with reference to FIGS. 6 to 8 showing an example of a measurement procedure.

First, the measurement key 6 is turned on (step S
1), the sampling nozzle 40 at the fixed position is R2
It moves to the position of the reagent (Step S2), and aspirates the R2 reagent (Step S3). After the suction of the reagent, the sampling nozzle 40 moves upward, and its outer surface is washed with a diluting liquid as a washing liquid supplied to the sampling nozzle washer 43. Then, the sampling nozzle 40
Returns to the position of the R2 reagent.

Next, the sampling nozzle 40 is connected to R1
It moves to the position of the reagent (Step S4), and aspirates the R1 reagent (Step S5). After the suction of the reagent, the sampling nozzle 40 moves upward, and its outer surface is washed with a diluting liquid as a washing liquid supplied to the sampling nozzle washer 43. Then, the sampling nozzle 40
Returns to the position of the R1 reagent.

Then, the sampling nozzle 40 moves to the sample setting position (Step S6), and aspirates the sample (whole blood) 3 in the sample container 4 for CRP measurement (Step S7). After this sample aspiration, the sampling nozzle 40
Moves upward, and its outer surface is cleaned by a diluting liquid as a cleaning liquid supplied to the sampling nozzle cleaning device 43. Thereafter, the sampling nozzle 40 returns to the position of the sample 3.

Then, the sampling nozzle 40 moves to the position of the sample receiving cell 19 (step S8), and the sample 3,
The R1 reagent and the R2 reagent are discharged into the sample receiving cell 19 (Step S9).

Thereafter, the dispenser 23 is slid several times by the stroke a to perform the first stirring of the reaction solution (step S10).

The sampling nozzle 4 after the ejection is completed
0 moves to the position of the WBC cell 31 (step S1).
1) The sample 3, R1 reagent, and R2 reagent remaining inside are mixed with the diluent supplied by the pump 17 in WBC.
The liquid is discharged into the cell 31. And the sampling nozzle 4
In the case of 0, the outer surface is cleaned by the diluting liquid as the cleaning liquid supplied to the sampling nozzle cleaning device 43. The waste liquid in this washing is received by the WBC cell 31,
The liquid is discharged to a waste liquid container 18 by a pump 17. The diluent is again supplied from the sampling nozzle washer 43 to the WBC cell 3
1 and discharged to the waste liquid container 18 by the pump 17 to wash the WBC cell 31. The receiving of the waste liquid may be performed by the RBC cell 32.

The sampling nozzle 4 after the cleaning is completed
0 moves to the sample setting position (Step S12), and aspirates the sample 3 in the sample container 4 for CBC measurement (Step S13). After this sample aspiration, the sampling nozzle 40 moves upward and the sampling nozzle washer 4
The outer surface is cleaned by the diluting liquid as the cleaning liquid supplied to 3.

The sampling nozzle 4 after the cleaning is completed
0 indicates that the specimen 3 is discharged into the WBC cell 31, while a predetermined amount of the diluent in the diluent container 15 is injected into the WBC cell 31 via the electromagnetic valve unit 12, and the primary dilution of the CBC specimen is performed ( Step S14).

The sampling nozzle 40 at the position of the WBC cell 31 aspirates the primary diluted CBC sample by a predetermined amount and moves to the RBC cell 32 (step S15).
The aspirated primary diluted CBC sample is transferred to this cell 32
(Step S16) and diluent container 1
A predetermined amount of the diluting liquid in 3 is injected into the RBC cell 32 through the electromagnetic valve section 10, and the secondary dilution of the CBC sample is performed (Step S17).

After the primary dilution and the secondary dilution have been completed, the hemolytic agent in the hemolytic agent container 16 is supplied to the WBC via the electromagnetic valve 12.
A predetermined amount is injected into the cell 31 and the measurement of WBC and Hgb is performed, while the measurement of RBC and PLT is performed in the RBC cell 32 (step S18), and the data at that time is taken into the MPU 46 via the signal processing unit 48. It is.

When the measurement is completed, the WBC cell 31 and R
The BC cell 32 is washed with a diluent (step S1).
9).

As described above, steps S11 to S11
In 19, the CBC measurement is performed in the blood cell counting / measuring unit 11, and during this period (about 60 seconds), the hemolysis reaction proceeds between the specimen 3, the R1 reagent, and the R2 reagent in the reagent receiving cell 19. At the same time, interfering substances are removed.

When the CBC measurement is completed, the sampling nozzle 40 at the position of the RBC cell 32
The WBC cell 31 is moved to the position of the cell 31 and the inner surface of the WBC cell 31 is washed away with the diluent supplied by the pump 17, and the outer surface is washed with the diluent supplied as the cleaning liquid to the sampling nozzle washer 43. The waste liquid at this time is received by the WBC cell 31 and discharged to the waste liquid container 18 by the pump 17. Then, the dilution liquid is supplied to the WBC cell 31 again from the sampling nozzle cleaning device 39 and discharged to the waste liquid container 18 by the pump 17 to clean the WBC cell 31. Thereafter, the sampling nozzle 40 moves to the position of the R3 reagent (Step S2).
0), aspirate R3 reagent (step S21). After the suction of the reagent, the sampling nozzle 36 is connected to the reagent receiving cell 1.
Nine positions are moved (step S22), and the R3 reagent is discharged into the reagent receiving cell 19 (step S23), and the R3 reagent is mixed into the reaction solution of the sample 3, the R1 reagent, and the R2 reagent.

After the discharge of the R3 reagent, the sampling nozzle 40 moves to the position of the WBC cell 31, and the pump 17
The inside surface of the WBC cell 31 is washed away with the diluting solution supplied by the above-described process, and the outer surface thereof is washed with the diluting solution as the cleaning solution supplied to the sampling nozzle washer 43. The waste liquid at this time is received by the WBC cell 31 and discharged to the waste liquid container 18 by the pump 17. Then, the diluting liquid is supplied to the WBC cell 31 again from the sampling nozzle cleaning device 43 and discharged to the waste liquid container 18 by the pump 17 to clean the WBC cell 31.

Then, the dispenser 23 is slid several times by the stroke b to perform the second stirring of the reaction solution (step S24). When the immune reaction occurs, the dispenser 23 is dispensed.
However, by sliding again to the end of the stroke b, the reaction liquid is circulated to the flow photometric cell 20 and the CRP measurement is performed (step S25). It is captured. When the measurement is completed, the reagent receiving cell 19 is washed with the diluent (step S26), and all the measurements are completed (step S2).
7).

In the MPU 46, the RBC (red blood cell count), the red blood cell volume (MC
V), and the like. Further, in the MPU 46, based on data obtained by the CRP measurement performed in the immunoassay section 10, a change in absorbance per predetermined time is obtained from a calibration curve obtained in advance from serum (or plasma) of a known concentration. The CRP concentration in whole blood is obtained.

In this case, for CRP measurement, CBC
Similarly to the measurement, since the whole blood to which the anticoagulant is added is used as the specimen 3, it is necessary to correct a plasma component volume error caused by using this whole blood. Therefore, RBC (red blood cell count) and red blood cell volume (M
CV), the hematocrit value (Hct) is determined, and using this hematocrit value, the CRP concentration in whole blood obtained by CRP measurement is corrected by the following correction formula to determine the CRP concentration in plasma.

That is, the CRP concentration in whole blood is defined as A,
When the hematocrit value is B, the CRP concentration in plasma C
Is determined by the following equation: C = A × 100 / (100−B)

Each measured value obtained by the MPU 46 is stored in, for example, a memory built in the MPU 46, displayed on the display device 49 by item, or output by the printer 50.

As described above, in the whole blood cell immunity measuring apparatus of the present invention, the CBC measurement is performed in the blood cell counting and measuring section 11 while the hemolytic and interfering substance removing reactions are caused in the immunity measuring section 10. Thus, the total time of the CRP measurement and the CBC measurement can be shortened, and the result obtained by the above-described CRP measurement can be smoothly corrected based on the result obtained by the CBC measurement.

FIG. 9 shows another embodiment of the present invention. In the middle of a flow path 21 connecting a reagent receiving cell 19 and a flow photometric cell 20, a flow path portion 21a having a large flow path cross section is provided. It is characterized in that the number of turbulences generated when the reaction solution is reciprocated back and forth by the infusion device 23 is increased, and the stirring efficiency is further improved. Other configurations and operations are shown in FIGS.
Since this is the same as the embodiment described with reference to FIG. 8, the description will be omitted.

[0049]

According to the present invention, a reagent for immunoassay and a whole blood sample can be efficiently agitated by using a liquid transfer infusion device used for immunoassay, and a propeller is provided in a sample receiving cell. When stirring the reaction solution by inserting a rotor such as, means for washing the rotor and means for taking the rotor into and out of the sample receiving cell and their installation space are required. Although mechanical vibrations due to these drives are likely to adversely affect the optical measurement by the flow photometric cell, according to the configuration of the present invention, since the reaction solution only reciprocates back and forth, There is no adverse effect, and the reciprocating movement of the liquid is performed using a liquid transfer infusion device used for immunoassay, and the infusion device is also used for liquid movement during immunoassay and liquid movement during stirring. Has been
The device configuration can be made compact and simple.

[Brief description of the drawings]

FIG. 1 is an explanatory view of a reaction liquid stirring mechanism according to the present invention.

FIG. 2 is a perspective view showing an example of a whole blood blood cell immunoassay apparatus with a side panel removed.

FIG. 3 is a view schematically showing an entire configuration of the whole blood cell immunoassay apparatus.

FIG. 4 is a view of a main part of the whole blood blood cell immunoassay apparatus as viewed from above.

FIG. 5 is a diagram schematically showing a configuration of a main part of the whole blood blood cell immunoassay apparatus.

FIG. 6 is a flowchart showing an example of a measurement procedure together with FIGS. 7 and 8;

FIG. 7 is a flowchart following the part shown in FIG. 6;

FIG. 8 is a flowchart following the part shown in FIG. 7;

FIG. 9 is an explanatory view of a reaction liquid stirring mechanism showing another embodiment of the present invention.

[Explanation of symbols]

Reference numeral 10: immunoassay unit, 11: blood cell count measurement unit, 19: sample receiving cell, 20: flow photometric cell, 23: infusion device.

──────────────────────────────────────────────────続 き Continued on the front page (51) Int.Cl. ⁶ Identification code FI G01N 33/53 G01N 33/53 X

Claims (1)

[Claims] 1. An immunoassay section for performing an immunoassay and a blood cell count and measurement section for performing a blood cell count measurement. The same whole blood sample is used in both of these measurement sections, and the result of the immunoassay is obtained by the blood cell count measurement. In a whole blood blood cell immunoassay apparatus configured to correct using a hematocrick value, a flow photometric cell for immunoassay via a flow path at the bottom of a sample receiving cell containing a reagent for immunoassay and a whole blood sample Connected to a flow path on the outlet side of the flow photometric cell via a three-way solenoid valve, and prior to the immunoassay, the reaction liquid in the sample receiving cell is used by the pipettor. A reaction liquid stirring mechanism in a whole blood blood cell immunoassay apparatus, wherein the reaction liquid is stirred by reciprocating back and forth between the sample receiving cell and the flow photometric cell.