JP5588336B2 - Blood analyzer and blood analysis method - Google Patents

Description

  The present invention relates to a blood analyzer and a blood analysis method for measuring hemoglobin concentration in whole blood and C-reactive protein (hereinafter also referred to as CRP) concentration in plasma using whole blood. .

  In this type of blood analyzer, as shown in Patent Document 1, whole blood and HRP cells (corresponding to WBC cells) for measuring hemoglobin concentration, and CRP cells for measuring CRP concentration, respectively, Reagents necessary for each measurement, including hemolytic reagent, are supplied to generate samples for each measurement, each sample is irradiated with light, and each concentration is calculated from the light intensity of the light transmitted through each cell There is something. In the present application, hemolysis refers to a phenomenon in which the cell membrane of erythrocytes is destroyed.

Japanese Patent Laid-Open No. 11-101798

  However, since each measurement sample is generated separately, the number of times of supply of the sample and the like is increased, and the nozzle used for the supply is washed each time supply is performed, so that the measurement time can be shortened. It is difficult and time consuming.

  Furthermore, in order to ensure measurement accuracy, it is necessary to prepare a certain amount or more of each sample for measurement. Therefore, there is a problem that it is difficult to reduce the usage cost of the reagent by reducing the amount of the reagent used, or to reduce the burden on the subject who collects the blood by reducing the amount of blood collected.

  Therefore, the present invention has been made to solve the above-mentioned problems, and while guaranteeing measurement accuracy, the running cost and the burden on the subject can be reduced, and the hemoglobin concentration in whole blood and the CRP concentration in plasma can be reduced. The main objective is to provide a blood analyzer that can measure quickly and easily.

  That is, the blood analyzer according to the present invention includes a reagent supply unit that supplies a hemolyzing reagent and an immune reagent to whole blood to generate a first sample, a first light source that irradiates light to the first sample, and the first light source. Receiving a light emitted from one light source and transmitted through the first sample, and outputting a first light intensity signal indicating the intensity; and supplying a diluent to the first sample; Diluting means for diluting the first sample at a predetermined magnification to generate the second sample, a second light source for irradiating the second sample with light, and light emitted from the second light source and transmitted through the second sample , A second light detecting means for outputting a second light intensity signal indicating the intensity, an Hgb calculating section for calculating a hemoglobin concentration based on a value of the second light intensity signal, and the first light intensity. C-reactive protein in plasma based on signal value and said hemoglobin concentration It is characterized in that it comprises a CRP calculation unit for calculating a degree.

  In such a case, the second sample is generated by diluting the first sample after being used for the measurement of the CRP concentration, and the hemoglobin concentration is measured using the second sample. The number of times of supply and the number of times of cleaning the nozzle used for supply can be reduced, the measurement time can be shortened, and the labor can be reduced. In addition, since it is not necessary to secure a certain amount or more separately for the hemoglobin measurement sample and the CRP measurement sample, it is possible to reduce the amount of reagent used and reduce the running cost while ensuring the measurement accuracy. It is also possible to reduce the burden on the subject who collects blood by reducing the amount of blood collected.

 Further, when an immunoreagent is supplied to whole blood, for example, CRP in whole blood and an immune component in the immunoreagent undergo an immunoreaction, and the CRP concentration is measured using this reaction product. On the other hand, there is a problem that the reaction product hinders measurement in measuring hemoglobin concentration. On the other hand, since the second sample is produced by diluting the first sample at a predetermined magnification, for example, the influence of an immune reagent such as the reaction product is reduced as much as possible to accurately measure the hemoglobin concentration. can do.

  In addition, in the conventional apparatus, the blood collection container cannot be removed until the whole blood is supplied to each of the plurality of cells after the blood collection container for storing the collected whole blood is set in the apparatus. There is a problem that the operator has to wait. On the other hand, if it is such, the said blood collection container can be removed only by collect | recovering whole blood from the said blood collection container once, and waiting time can be reduced significantly.

  As the influence of the above-described immunoreagent, there are an influence due to the fact that the second sample contains the immunoreagent itself and an influence of an immune reaction between the immunoreagent and the CRP in the second sample. In order to further reduce the influence of the former immunoreagent itself and more accurately calculate the hemoglobin concentration, the immunoreagent diluted to a predetermined magnification with the diluent is used from the second light source or the second light source. A first related value storage unit that stores a first related value that is a value related to the intensity of transmitted light when light is emitted from a light source that emits light including a wavelength range of the light, and the Hgb calculating unit However, it is desirable to calculate the hemoglobin concentration based on the first related value and the value of the second light intensity signal.

  On the other hand, the magnitude of the influence of the latter immune reaction has been found to depend on the CRP concentration in whole blood by the inventor's earnest study. Therefore, in order to further reduce the influence of the immune reaction and more accurately calculate the hemoglobin concentration, a hemolysis reagent and an immune reagent are supplied to whole blood whose C-reactive protein concentration in the whole blood is known. The second related value, which is a value related to the transmitted light intensity when light is emitted from the second light source or the light source that emits light including the wavelength range of light from the second light source to the reference sample generated A second related value storage unit for storing the second related value, the Hgb calculating unit based on the second related value, the value of the first light intensity signal, and the value of the second light intensity signal. It is desirable to calculate the concentration. As a specific example of the method for calculating the hemoglobin concentration, the Hgb calculating unit calculates the C-reactive protein concentration in the whole blood calculated from the second related value and the value of the first light intensity signal. Examples include calculating a correction value and calculating a hemoglobin concentration based on the correction value and the value of the second light intensity signal.

  Each related value includes not only a value indicating transmitted light intensity, light transmittance, or absorbance, but also a value indicating a calibration curve calculated based on transmitted light intensity or the like.

  The blood analysis method used in this blood analyzer is also one aspect of the present invention. That is, the blood analysis method according to the present invention includes a reagent supply step of supplying a hemolyzing reagent and an immune reagent to whole blood to generate a first sample, irradiating the first sample with light, and transmitting the first sample. A first light intensity measuring step for receiving the light and measuring a first light intensity indicating the intensity; supplying a diluent to the first sample; diluting the first sample at a predetermined magnification; A dilution step for generating a sample, a second light intensity measurement step for irradiating the second sample with light, receiving the light transmitted through the second sample, and measuring a second light intensity indicating the intensity; A Hgb calculating step for calculating a hemoglobin concentration in whole blood based on two light intensities, and a CRP calculating step for calculating a C-reactive protein concentration in plasma based on the first light intensity and the hemoglobin concentration. In a method characterized by comprising That.

  According to the present invention configured as described above, the running cost and the burden on the subject can be reduced while ensuring the measurement accuracy, and the hemoglobin concentration in whole blood and the CRP concentration in plasma can be measured easily and rapidly.

The typical equipment block diagram of the blood analyzer in embodiment of this invention. The flowchart which shows the operation | movement procedure of the blood analyzer in the same embodiment. The graph which shows the correlation with the light absorbency computed using the blood analyzer in the same embodiment, and hemoglobin concentration.

  Hereinafter, a blood analyzer 100 according to an embodiment of the present invention will be described with reference to the drawings. The blood analyzer 100 according to the present embodiment measures the hemoglobin concentration in whole blood and the CRP concentration in plasma using whole blood such as human blood or animal blood. Specifically, as shown in FIG. 1, the blood analyzer 100 mainly includes a measurement mechanism 110 and a calculation mechanism 120 that performs calculation processing related to the measurement mechanism 110. Note that whole blood is blood collected from humans or animals, and includes blood cell components and plasma components, and may further include an anticoagulant or a diluent.

  The measurement mechanism 110 includes a cell 10 that contains a sample, a reagent supply means 20 that supplies a reagent to the cell 10, a first light source 30 that irradiates light to the sample contained in the cell 10, and the first First light detection means 40 is provided for receiving light emitted from the light source 30 and transmitted through the sample and outputting a first light intensity signal indicating the intensity of the light.

  Each part will be described in detail. The cell 10 is a container having an internal space for storing a sample. In the internal space, an incident window through which light enters and an exit window through which light exits face each other in parallel, and a discharge port (not shown) for discharging a sample is provided at the center of the bottom surface of the internal space. ing. A predetermined amount of whole blood is supplied to the cell 10 from a blood collection container (not shown) containing the whole blood by a whole blood supply nozzle (not shown).

  The reagent supply means 20 includes a reagent container 21 that contains a hemolytic reagent, a buffer reagent, and an immune reagent, a reagent supply nozzle 22 that supplies each reagent to the cell 10, and a predetermined amount of the reagent supply nozzle 22. And an electromagnetic valve (not shown) for adjusting the opening of the valve body so that each of the reagents passes. The reagent supply means 20 sequentially supplies a hemolysis reagent (for example, a hemolytic saponin solution), a buffer reagent, and an immunological reagent (for example, CRP-X2 (Denka Biotechnology)) to the whole blood accommodated in the cell 10. A first sample is generated. The immunoreagent contains an immune component (here, anti-CRP antibody sensitive latex) that aggregates by causing an immune reaction with CRP in the first sample.

  The 1st light source 30 is arrange | positioned facing the said cell 10, and is LED which inject | emits the light whose peak wavelength is 600 nm or more, and a peak wavelength is 660 nm here.

  The first light detection means 40 is disposed to face the first light source 30 with the cell 10 interposed therebetween, and here is a photodiode.

  The calculation mechanism 120 is a general-purpose or dedicated computer, stores a predetermined program in a memory, and operates the CPU and its peripheral devices in cooperation with each other as the CRP calculation unit 50 and a control unit (not shown). Demonstrate the function. The CRP calculating unit 50 calculates the CRP concentration in plasma based on the value of the first light intensity signal and the hemoglobin concentration described later, and here, it is calculated using a latex immunoturbidimetric method. Specifically, when an immunoreagent is supplied to the first sample, the CRP in the first sample and the immune component in the immunoreagent undergo an immunoreaction and gradually aggregate, so the first in the aggregation process. Measure the amount of time change in the value of one light intensity signal There is a correlation between the amount of change with time and the CRP concentration in whole blood, and a calibration curve showing this correlation is calculated in advance using whole blood whose CRP concentration in whole blood is known, The data is stored in the CRP calculation unit 50. The CRP calculating unit 50 calculates the CRP concentration in whole blood by substituting the time variation of the measured value of the first light intensity signal into the calibration curve. Further, the CRP concentration in the whole blood is corrected using the hemoglobin concentration described later, and the CRP concentration in the plasma is calculated. The control unit outputs a command so that each unit of the blood analyzer 100 operates after a predetermined time has elapsed from the start of measurement.

  Furthermore, the blood analyzer 100 according to the present embodiment includes a configuration for measuring the hemoglobin concentration using the first sample after being used for measuring the CRP concentration. Specifically, the measuring mechanism 110 includes a diluting means 60 for supplying a diluent to the cell 10, a second light source 70 for irradiating the cell 10 with light, and a sample emitted from the second light source 70 and transmitted through the sample. And second light detection means 80 for receiving the light and outputting a second light intensity signal indicating the intensity of the light.

  The diluting means 60 supplies a diluting solution to the first sample accommodated in the cell 10 to give the first sample a predetermined magnification (150 to 400 times, here, 306 times, hereinafter also referred to as dilution magnification). To produce a second sample. As with the reagent supply means 20, the dilution means 60 is provided with a dilution liquid container 61 that contains a dilution liquid, a dilution liquid supply nozzle 62 that supplies the dilution liquid to the cell 10, and the dilution liquid supply nozzle 62. And a solenoid valve (not shown) that adjusts the opening of the valve body so that a fixed amount of diluent passes therethrough.

  The 2nd light source 70 is arrange | positioned facing the cell 10, and is LED which inject | emits the light whose peak wavelength is 500-550 nm, and a peak wavelength is 510 nm here.

  The second light detection means 80 is disposed opposite to the second light source 70 with the cell 10 interposed therebetween, and is a photodiode here.

  The arithmetic mechanism 120 functions as an Hgb calculation unit 51 and an Hct conversion unit 57. The Hgb calculation unit 51 calculates a hemoglobin concentration based on the value of the second light intensity signal, and a correction value calculation unit 52 that calculates a correction value for correcting the value of the second light intensity signal; And an Hgb calculating unit main body 53 that calculates a hemoglobin concentration based on the correction value calculated by the correcting unit and the value of the second light intensity signal.

  The correction value calculation unit 52 includes a first related value storage unit 54 that stores a predetermined first related value, a second related value storage unit 55 that stores a predetermined second related value, and the first A correction value calculating unit main body 56 that calculates a correction value based on the related value, the second related value, and the measured value of the first light intensity signal.

  The correction value and each related value will be described. The hemoglobin concentration is calculated based on the value of the second light intensity signal, but the value of the second light intensity signal is measured using the second sample containing the immunoreagent, and is affected by the immune reagent. End up. Therefore, the value of the second light intensity signal is corrected by subtracting a correction value, which is a value indicating the magnitude of the influence of the immunoreagent, from the value of the second light intensity signal. The correction value is the sum of a first correction value indicating the magnitude of the influence of the immune reagent itself and a second correction value indicating the magnitude of the immune reaction between the immune reagent and the CRP in the second sample. .

  The first correction value is a value calculated based on a predetermined first related value, and here is equal to the first related value. Prior to measurement of hemoglobin concentration or the like, the first related value is generated at a predetermined magnification with the diluent (here, diluted to approximately the same predetermined magnification as the second sample), and generates the immune reagent, This is a value related to the transmitted light intensity when light is irradiated from the second light source 70 to the immunoreagent contained in the cell 10 (here, a value indicating the transmitted light intensity).

  On the other hand, the present inventors have found that the second correction value depends on the CRP concentration in whole blood, and the inventors have found that the second correction value depends on the CRP concentration in whole blood. Calculated by substituting the concentration. The second related value is a value indicating the calibration curve (here, the coefficient of the calibration curve which is a polynomial). More specifically, the second related value is obtained by supplying a hemolytic reagent and an immunological reagent to a plurality of types of whole blood whose blood concentrations are different from each other, in which the CRP concentration in the whole blood is known prior to measurement of the hemoglobin concentration or the like. It is a value related to a plurality of transmitted light intensities when a plurality of types of reference samples are generated and each reference sample accommodated in the cell 10 is irradiated with light from the second light source. It is a value indicating a calibration curve indicating the relationship between the transmitted light intensity and the CRP concentration in whole blood, calculated based on the value indicating the transmitted light intensity.

  In addition, the second related value is not limited to this. For another example in which the second related value is a value indicating a calibration curve, the second related value storage unit 55 includes the plurality of transmitted lights. The value indicating the intensity is stored as a second related value, and the correction value calculation unit main body 56 selects one value from the plurality of values according to the CRP concentration in the whole blood, and calculates the value as the second correction value. You can list what you do.

  The Hgb calculation unit main body 53 calculates the difference between the value of the second light intensity signal received from the second light detection means 80 and the correction value, and corrects the value of the second light intensity signal. In addition, the Hgb calculation unit main body 53 stores a calibration curve indicating the relationship between the hemoglobin concentration and the difference, which has been calculated in advance using whole blood having a known hemoglobin concentration, and the calibration curve is included in the calibration curve. The calculated difference is substituted to calculate the hemoglobin concentration.

  The Hct conversion unit 57 converts the hemoglobin concentration calculated by the Hgb calculation unit 51 into a hematocrit value using a predetermined conversion formula.

  Next, the operation procedure of the blood analyzer 100 will be described with reference to the flowchart of FIG. First, when the operator turns on the measurement start switch with the blood collection container approaching so that the whole blood in the blood collection container is immersed in the tip of the whole blood supply nozzle (step S1), a command from the control unit In response, the whole blood supply nozzle supplies a predetermined amount of whole blood to the cell 10 (step S2). Next, the reagent supply means 20 sequentially supplies a hemolysis reagent, a buffer reagent, and an immune reagent to the whole blood stored in the cell 10 to generate a first sample (step S3). Further, the first light source 30 irradiates the first sample with light (step S4), and the first light detection means 40 measures and outputs a first light intensity signal indicating the intensity of the light transmitted through the first sample. (Step S5).

  Further, according to a command from the control unit, a part of the first sample is discharged from the discharge port of the cell 10 to leave a predetermined amount of the first sample in the cell 10 (step S6). The diluting means 60 supplies a predetermined amount of diluent to the first sample remaining in the cell 10, dilutes the first sample at a predetermined magnification, and generates a second sample (step S7).

  In response to a command from the control unit, the second light source 70 irradiates the second sample with light (step S8), and the second light detection means 80 indicates the second light intensity indicating the intensity of the light transmitted through the second sample. The signal is measured and output (step S9).

  The CRP calculating unit 50 calculates the CRP concentration in whole blood by substituting the time change amount of the value of the first light intensity signal into a previously calculated calibration curve (step S10). The correction value calculation unit main body 56 of the correction value calculation unit 52 substitutes the CRP concentration in whole blood into a calibration curve having the second related value stored in the second related value storage unit 55 as a coefficient, and While calculating the second correction value, the first related value stored in the first related value storage unit 54 is accepted as the first correction value, and the correction is the sum of the first correction value and the second correction value. A value is calculated (step S11). The Hgb calculation unit main body 53 calculates a difference between the value of the second light intensity signal received from the second light detection means 80 and the correction value, and substitutes the difference into a previously calculated calibration curve. Then, the hemoglobin concentration is calculated (step S12).

  The Hct conversion unit 57 converts the hemoglobin concentration calculated by the Hgb calculation unit 51 into a hematocrit value using a predetermined conversion formula (step S13). The CRP calculating unit 50 calculates the CRP concentration in plasma based on the CRP concentration and hematocrit value in the whole blood (step S14). An output means such as a printer outputs the calculated hemoglobin concentration and plasma CRP concentration (step S15).

  A graph showing the correlation between the absorbance calculated using the value of the second light intensity signal corrected by the blood analysis method according to the present embodiment (the difference) and the hemoglobin concentration is shown in FIG. The average value of the correlation coefficient is 0.988, the correlation is sufficiently high, and it can be seen that the hemoglobin concentration measuring method according to the present embodiment is sufficiently accurate.

  According to the present embodiment, the second sample is generated by diluting the first sample used for measuring the CRP concentration, and the hemoglobin concentration is measured using the second sample. The number of times of supply and the number of times of cleaning the nozzle used for supply can be reduced, the measurement time can be shortened, and labor can be reduced. In addition, since it is not necessary to secure a certain amount or more separately for the hemoglobin measurement sample and the CRP measurement sample, it is possible to reduce the amount of reagent used and reduce the running cost while ensuring the measurement accuracy. It is also possible to reduce the burden on the subject who collects blood by reducing the amount of blood collected.

  Further, when an immunoreagent is supplied to whole blood, for example, CRP in whole blood and an immune component in the immunoreagent undergo an immunoreaction, and the CRP concentration is measured using this reaction product. On the other hand, there is a problem that the reaction product hinders measurement in measuring hemoglobin concentration. On the other hand, since the second sample is produced by diluting the first sample at a predetermined magnification, for example, the influence of an immune reagent such as the reaction product is reduced as much as possible to accurately measure the hemoglobin concentration. can do.

  Moreover, since the same cell 10 is used for Hgb measurement and CRP measurement, it is not necessary to provide different cells for each type of measurement, and the manufacturing cost can be suppressed. Further, when whole blood is supplied to the cell 10, the whole blood in the blood collection container only needs to be brought into contact with the whole blood supply nozzle for a short time, so that a holder or the like for holding the blood collection container is omitted. can do.

  In the measurement using whole blood, it is necessary to use a hematocrit value in order to calculate the CRP concentration in plasma. Conventionally, since the hematocrit value has been calculated by the electric resistance method, it is necessary to provide an electrode or the like, which increases manufacturing costs. On the other hand, the inventors of the present invention have found that hematocrit values can be accurately converted from the hemoglobin concentration by intensive studies. Since this conversion is used in the blood analyzer 100 of the present embodiment, electrodes and the like can be omitted, and the manufacturing cost can be reduced.

  In addition, not all of the first sample used for CRP measurement is diluted, but a part of the first sample is diluted to generate the second sample, so that consumption of the diluent is suppressed. Running costs can be reduced.

  The present invention is not limited to these embodiments. For example, all the first samples used for CRP measurement may be diluted to generate the second sample.

  Further, the hematocrit value is calculated from the hemoglobin concentration, and the CRP concentration in the plasma is calculated based on the hematocrit value and the CRP concentration in the whole blood. However, without the step of calculating the hematocrit value, the hemoglobin is calculated. The CRP concentration in plasma may be calculated based on the concentration and the CRP concentration in whole blood. Alternatively, the CRP concentration in plasma may be calculated from the value of the first light intensity signal and the value of the second light intensity signal without calculating the hemoglobin concentration.

  Further, the CRP concentration in the whole blood is calculated from the time change amount of the value of the first light intensity signal, but it may be calculated from the value of the first light intensity signal. Similarly, the hemoglobin concentration is calculated from the value of the second light intensity signal, but may be calculated from the amount of time change of the value of the second light intensity signal.

  Further, regarding reagent supply means, each reagent may be supplied to the first cell by one reagent supply nozzle, or a plurality of reagent supply nozzles corresponding to each reagent are provided to supply each reagent. You may make it do. In addition, the hemolytic reagent supply unit, the buffer reagent supply unit, and the immunoreagent supply unit are provided integrally, but they may be provided separately. Similarly, the reagent supply unit and the diluting unit may be provided integrally or separately.

  The first light source and the second light source are single-wavelength light sources that emit light having a peak such as an LED, but only a continuous spectrum light source that emits continuous spectrum light such as an Xe lamp and light in a predetermined wavelength range. And a light source device including an optical filter that blocks light in other wavelength ranges. Moreover, you may comprise a 1st light source and a 2nd light source by using a different optical filter with respect to the same continuous spectrum light source.

  Moreover, although the 1st light detection means and the 2nd light detection means shall be provided separately, you may provide integrally.

  The first related value includes an immunoreagent diluted to the same dilution factor as the second sample (hereinafter also referred to as a reference magnification) and a cell used for hemoglobin measurement (hereinafter, the cell length of this cell is also referred to as a reference cell length). A value indicating the transmitted light intensity measured using the immunoreagent diluted to a dilution ratio different from the reference magnification or a cell having a cell length different from the reference cell length. It is good. In that case, the first correction value may be a value obtained by multiplying the first related value by a predetermined value α, and the predetermined value α is a ratio of the dilution ratio to the reference magnification or a ratio of the cell length to the reference cell length. A value determined accordingly (for example, α = 1 when each ratio is 1) may be used.

  Furthermore, when multiple dilution ratios and cell lengths can be selected, the transmitted light intensity is measured using immunoreagents diluted to multiple dilution ratios and cells with multiple cell lengths, and the measured multiple transmitted light intensities are measured. May be stored as a first related value, and one of them may be selected according to the selection, and used as the first correction value.

  For example, it is desirable to use a calibration curve when an arbitrary dilution rate and cell length within a predetermined range can be selected instead of selecting a dilution rate and cell length from a plurality of options. Specifically, each of the transmitted light intensity is measured using an immunoreagent diluted to a plurality of dilution ratios and a cell having a plurality of cell lengths, and a calibration curve showing the relationship between the transmitted light intensity and the cell length or the dilution ratio. And a value indicating the calibration curve (for example, a coefficient of the calibration curve which is a polynomial) is set as the first related value. Then, the first correction value may be calculated by substituting the cell length and the dilution factor into a calibration curve having the first related value as a coefficient.

  Similarly to the first related value, the second related value may be a value in consideration of the dilution rate and the cell length. For example, a calibration curve (specifically, a coefficient of a calibration curve that is a polynomial) showing the relationship between the transmitted light intensity and the CRP concentration in whole blood can be cited according to the dilution factor and the cell length. More specifically, similarly to the first related value described above, a plurality of sets of coefficients are stored as second related values in the second related value storage unit, and the dilution factor and cell length are determined from the plurality of sets of coefficients. One set may be selected according to the selection and used as the coefficient of the calibration curve. Further, a relational expression between the dilution factor or cell length and the coefficient of the calibration curve may be calculated, and the coefficient of the relational expression may be stored in the second related value storage unit as the second related value.

  In addition, each related value or each correction value is calculated based not only on the dilution factor and cell length, but also on the type of each reagent and diluent, the amount of each reagent and diluent supplied, the ratio between each reagent and diluent, etc. It is good also as what is done.

  On the other hand, when the influence of the CRP concentration in the whole blood on the second correction value does not substantially change, such as when the CRP concentration in the whole blood is expected not to fluctuate so much, the second correction value is set. For example, transmission when light is irradiated from the second light source to a reference sample generated by supplying a hemolyzing reagent and an immune reagent to whole blood in which the CRP concentration in the whole blood is a predetermined value (for example, an average value) A value indicating the light intensity may be set as the second related value.

  Each of the related values is a value related to the transmitted light intensity obtained by using the second light source. For example, the second light source such as a light source that emits light including a wavelength range of light from the second light source. It is good also as a value relevant to the transmitted-light intensity | strength obtained using the light source equivalent to. Further, each related value may be a value indicating transmitted light intensity, light transmittance, or absorbance.

  The control unit outputs a command so that each unit of the blood analyzer 100 operates after a predetermined time has elapsed from the start of measurement. However, the control unit outputs a command for a predetermined time from a predetermined operation such as supply of an immune reagent or a diluent. It is good also as what outputs a command so that each above-mentioned part may operate after progress. In addition, the present invention can be variously modified without departing from the spirit of the present invention.

DESCRIPTION OF SYMBOLS 100 ... Blood analyzer 10 ... Cell 20 ... Reagent supply means 30 ... 1st light source 40 ... 1st light detection means 50 ... CRP calculation part 51 ... Hgb calculation part 60 ... Dilution means 70 ... Second light source 80 ... Second light detection means

Claims (5)

A reagent supply means for generating a first sample by supplying a hemolysis reagent and an immune reagent to whole blood to be measured;
A first light source for irradiating the first sample with light;
First light detection means for receiving light emitted from the first light source and transmitted through the first sample, and outputting a first light intensity signal indicating the intensity;
Dilution means for supplying a diluent to the first sample, diluting the first sample at a predetermined magnification, and generating a second sample;
A second light source for irradiating the second sample with light;
Second light detection means for receiving light emitted from the second light source and transmitted through the second sample, and outputting a second light intensity signal indicating the intensity;
An Hgb calculator that calculates a hemoglobin concentration based on a correction value that is a value indicating the magnitude of the influence of the second light intensity signal and the immunoreagent ;
A blood analyzer comprising: a CRP calculating unit that calculates a C-reactive protein concentration in plasma of the whole blood based on the value of the first light intensity signal and the hemoglobin concentration. Related to the transmitted light intensity when the immunoreagent diluted at a predetermined magnification with the diluent is irradiated with light from the second light source or a light source that emits light including a wavelength range of light from the second light source. A first related value storage unit that stores a first related value that is a value;
The blood analyzer according to claim 1, wherein the Hgb calculation unit calculates a hemoglobin concentration based on the first related value and the value of the second light intensity signal. The wavelength range of light from the second light source or the second light source with respect to a reference sample generated by supplying a hemolysis reagent and an immunoreagent to whole blood with a known C-reactive protein concentration in the whole blood. A second related value storage unit that stores a second related value that is a value related to the transmitted light intensity when light is emitted from a light source that emits light,
The blood analysis according to claim 1, wherein the Hgb calculation unit calculates a hemoglobin concentration based on a second related value, a value of the first light intensity signal, and a value of the second light intensity signal. apparatus. The correction value is calculated from the second related value and the C-reactive protein concentration in whole blood calculated from the value of the first light intensity signal,
The blood analyzer according to claim 3, wherein the Hgb calculating unit calculates a hemoglobin concentration based on the correction value and the value of the second light intensity signal. A reagent supplying step of supplying a hemolysis reagent and an immune reagent to whole blood to generate a first sample;
A first light intensity measuring step of irradiating the first sample with light, receiving light transmitted through the first sample, and measuring a first light intensity indicating the intensity;
A dilution step of supplying a diluent to the first sample, diluting the first sample at a predetermined magnification, and generating a second sample;
A second light intensity measuring step of irradiating the second sample with light, receiving the light transmitted through the second sample, and measuring a second light intensity indicating the intensity;
An Hgb calculating step of calculating a hemoglobin concentration in whole blood based on a correction value which is a value indicating the magnitude of the influence of the second light intensity and the immune reagent ;
A blood analysis method comprising: a CRP calculating step of calculating a C-reactive protein concentration in plasma based on the first light intensity and the hemoglobin concentration.