CN116046620A

CN116046620A - Blood sedimentation measurement apparatus, method and sample analyzer

Info

Publication number: CN116046620A
Application number: CN202111262797.9A
Authority: CN
Inventors: 刘斌; 梁家伟; 寻文鹏
Original assignee: Shenzhen Mindray Bio Medical Electronics Co Ltd
Current assignee: Shenzhen Mindray Bio Medical Electronics Co Ltd
Priority date: 2021-10-28
Filing date: 2021-10-28
Publication date: 2023-05-02

Abstract

Embodiments of the present application relate to blood sedimentation measurement apparatus, methods, and sample analyzers. The method comprises the steps of obtaining parameters representing the aggregation degree of red blood cells of a blood sample to be measured by blood sedimentation measurement equipment; acquiring the temperature of the blood sample to be measured when performing blood sedimentation measurement by blood sedimentation measurement equipment; calculating, by a blood sedimentation measurement device, a corrected erythrocyte sedimentation rate of the blood sample from the temperature and the parameter indicative of the extent of erythrocyte aggregation. Therefore, the parameter representing the aggregation degree of the red blood cells is corrected by utilizing the temperature of the blood sample to be measured when the blood sedimentation measurement is carried out, so that the more accurate sedimentation rate of the red blood cells can be obtained rapidly.

Description

Blood sedimentation measurement apparatus, method and sample analyzer

Technical Field

The present application relates to the technical field of medical devices, and in particular to blood sedimentation measurement devices, methods and sample analyzers.

Background

The erythrocyte sedimentation rate (Erythrocyte sedimentation rate, ESR) is abbreviated as blood sedimentation and refers to the rate at which erythrocytes naturally sediment in ex-vivo anticoagulation under prescribed conditions. ESR is a common index reflecting the aggregation degree of red blood cells and has a distinguishing significance for stationary phase, stable and recurrent state of illness and benign and malignant tumor.

The current common method for measuring ESR is the weissel method, which is a method of observing and recording the erythrocyte sedimentation rate of blood contained in a weissel tube. Typically, in the Wittig method, the ESR is measured by counting from the time after the injection of the blood sample and observing the distance between the interface between the clustered cells and the plasma from the top surface of the tube (the suspension medium height) after one hour.

However, the measurement of ESR by the weskii method (also referred to as reference method) has the following drawbacks: 1) The measurement speed is slow, the sedimentation time is required to be 1 hour, and the detection efficiency of the measurement result in one hour can not meet the daily detection requirement along with the great increase of patients in hospitals. 2) The blood consumption is large, and a blood sample is usually filled in a sedimentation tube, and a blood volume of about 1mL is required, which is not available for a patient who collects peripheral blood of a finger.

Therefore, in order to overcome the above-described drawbacks of the weisse method, a rapid ESR measurement method (hereinafter also referred to as a red blood cell aggregation method), i.e., a method of predicting the erythrocyte sedimentation rate by measuring the erythrocyte aggregation index, has been developed in the industry on the basis of the study of hemorheology. The ESR measurements were converted by measuring the change in scattering/transmittance of light by the blood cells during rouleaux erythropoiesis. This measurement can be done in a short time (about 20 s) and the blood consumption is only around 100 uL. These methods indicate that there is a correlation between the erythrocyte aggregation index and the erythrocyte sedimentation rate.

However, although the ESR value can be obtained rapidly by the erythrocyte aggregation method, the accuracy of the ESR value measured by the erythrocyte aggregation method is not high.

In addition, it is often necessary to preheat the portion of the blood sample being tested prior to testing the erythrocyte sedimentation rate by the erythrocyte aggregation method to obtain a more accurate test result. However, such preheating increases the volume of the blood sedimentation measurement apparatus, and also increases the blood sedimentation detection time, reducing the blood sedimentation detection efficiency.

Disclosure of Invention

It is therefore an object of the present application to provide a blood sedimentation measurement apparatus, a blood sedimentation measurement method and a sample analyzer, which enable a more accurate erythrocyte sedimentation rate to be obtained rapidly.

Another object of the present application is to increase the blood sedimentation detection speed without increasing the volume of the blood sedimentation detection device, in particular to reduce the volume of the blood sedimentation measurement device.

To achieve the object of the present application, a first aspect of the present application provides a sample blood sedimentation measurement apparatus, including a sampling and dispensing device, a blood sedimentation detection device, a temperature acquisition device, and a data processing device;

the sample distribution device is arranged for collecting a blood sample and for at least partially distributing the blood sample to the blood sedimentation detection device;

The blood sedimentation detection device comprises a detection pipeline, an optical detection assembly and a power assembly connected with the detection pipeline, wherein the power assembly is used for conveying the distributed blood sample part into the detection pipeline, the detection pipeline is used for providing a detection place for the distributed blood sample part, and the optical detection assembly is used for detecting the blood sample part in the detection pipeline so as to obtain a parameter of the blood sample, wherein the parameter is used for representing the aggregation degree of red blood cells;

the temperature acquisition device is used for acquiring the temperature of a blood sample part in the blood sedimentation detection device; and is also provided with

The data processing device is configured to obtain the temperature of the blood sample portion and the parameter indicative of the extent of red blood cell aggregation, and calculate a corrected erythrocyte sedimentation rate of the blood sample from the temperature of the blood sample portion and the parameter indicative of the extent of red blood cell aggregation.

In the blood sedimentation measurement device provided in the first aspect of the application, the parameter representing the aggregation degree of the red blood cells of the blood sample is rapidly obtained based on the red blood cell aggregation method through the blood sedimentation detection device, and then the parameter representing the aggregation degree of the red blood cells is corrected according to the temperature of the blood sample part, so that the accurate sedimentation rate of the red blood cells can be obtained.

A second aspect of the present application provides a blood sedimentation measurement method applied to a blood sedimentation measurement apparatus, including;

obtaining parameters representing the aggregation degree of red blood cells of a blood sample to be measured by blood sedimentation measurement equipment;

acquiring the temperature of the blood sample to be measured when performing blood sedimentation measurement by blood sedimentation measurement equipment;

calculating, by a blood sedimentation measurement device, a corrected erythrocyte sedimentation rate of the blood sample from the temperature and the parameter indicative of the extent of erythrocyte aggregation.

In the blood sedimentation measurement method provided by the second aspect of the invention, the accurate erythrocyte sedimentation rate can be rapidly obtained according to the acquired parameters representing the erythrocyte aggregation degree and the temperature of the blood sample to be measured when the blood sedimentation measurement is performed.

A third aspect of the present application provides a sample analyzer comprising a blood sedimentation detection device, a blood routine detection device, a sample distribution device, and a controller;

the sampling and dispensing device is used for collecting a blood sample and is used for at least partially dispensing the blood sample to the blood routine detection device and the blood sedimentation detection device respectively, wherein the sampling and dispensing device comprises a sampling needle, a power supply pipeline and a sampling power assembly, the power supply pipeline is respectively connected with the sampling power assembly and the sampling needle at two ends, and the sampling power assembly is used for driving the sampling needle to suck or discharge the blood sample through the power supply pipeline;

The blood routine detection device comprises a blood routine reaction tank and a blood routine detection assembly, wherein the blood routine reaction tank is used for receiving a processing reagent and a blood sample part distributed by the sampling and distribution device, and the blood routine detection assembly is used for detecting blood routine parameters of a sample liquid to be detected, which is obtained by mixing and reacting the blood sample part in the blood routine reaction tank with the processing reagent;

the blood sedimentation detection device comprises a blood sedimentation detection pipeline, a blood sedimentation optical detection assembly and a heating assembly, wherein the blood sedimentation detection pipeline is arranged as a part of the power supply pipeline, the sampling power assembly is further arranged for conveying a blood sample into the blood sedimentation detection pipeline, the blood sedimentation optical detection assembly is arranged beside the blood sedimentation detection pipeline and is used for detecting parameters representing the aggregation degree of red blood cells of the blood sample part in the blood sedimentation detection pipeline, and the heating assembly is arranged for keeping the temperature of the blood sedimentation detection device within a preset range; and is also provided with

The controller is in communication with the blood sedimentation detection device, the blood routine detection device, the sample distribution device and is configured to:

Causing the sample distribution device to collect a predetermined amount of blood sample such that after collection is complete and prior to at least partially distributing the blood sample to the blood sedimentation detection device, there is a blood sample in the blood sedimentation detection line such that the heating assembly can preheat the blood sample in the blood sedimentation detection line;

causing the sample distribution device to distribute a portion of the collected blood sample to a blood routine reaction cell of the blood routine detection device;

after the blood sample distribution to the blood sedimentation detection device is completed, the blood sedimentation optical detection assembly and the blood sedimentation detection assembly are made to detect the blood sample portion in the blood sedimentation detection line and the blood sample portion in the blood sedimentation reaction tank in parallel.

In the sample analyzer provided in the third aspect of the present application, in which the blood sedimentation detection device and the blood routine detection device are integrated, a part of the power supply line is set as the blood sedimentation detection line, and the blood sedimentation detection line is made to hold the blood sample after the blood sample is collected and before the blood sample is dispensed, so that the blood sample portion for blood sedimentation detection after the completion of sample suction, that is, the blood sample portion for blood sedimentation detection is heated by the heating assembly in the blood sedimentation detection device, the warm-up time of the blood sample portion for blood sedimentation detection alone can be effectively saved, so that the blood sedimentation detection speed can be matched with the blood routine detection speed.

Drawings

The advantages and features of the foregoing and/or additional aspects of the present application will become apparent and readily appreciated from the description of the embodiments, taken in conjunction with the following drawings, wherein:

FIG. 1 is a schematic block diagram of an blood sedimentation measurement device according to some embodiments of the present application;

FIG. 2 is a schematic flow chart of a blood sedimentation measurement method according to some embodiments of the present application;

FIG. 3 is a schematic diagram of a blood sedimentation measurement device according to some embodiments of the present application;

FIG. 4 is a schematic dimensional view of an optical detection assembly according to some embodiments of the present application;

FIG. 5 is a schematic diagram of a blood sedimentation measurement device according to further embodiments of the present application;

FIG. 6 is a graph of the aggregation of red blood cells measured by the erythrocyte aggregation method by the blood sedimentation detection device according to the present application;

FIG. 7 is a calibration curve for calculating the erythrocyte sedimentation rate prior to correction;

FIG. 8 is a fitted curve of temperature versus blood sedimentation measurement bias;

FIG. 9 is a fitted curve of temperature-blood sedimentation measurement deviation based on the blood self temperature characteristic;

FIG. 10 is a fitted curve of temperature-blood sedimentation measurement bias based on light emitter temperature characteristics;

FIG. 11 is a schematic diagram of a sample analyzer according to some embodiments of the present application;

Fig. 12 is a schematic view of the blood sedimentation detection device after the sample distribution device collects the blood sample and after the blood sample is distributed.

Detailed Description

For the purposes of making the objects, technical solutions and advantages of the embodiments of the present application more clear, the technical solutions of the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application, and it is apparent that the described embodiments are some embodiments of the present application, but not all embodiments. All other embodiments, which can be made by one of ordinary skill in the art without undue burden from the present disclosure, are within the scope of the present application based on the embodiments herein.

Currently, ESR values of blood samples are increasingly used clinically to aid in diagnosing disease. The inventors of the present application noted that the ESR values currently detected using the erythrocyte aggregation method do not accurately reflect the natural sedimentation rate of erythrocytes.

By analysis, the inventors have realized that in the application of the erythrocyte aggregation method, since both the speed of the erythrocyte aggregation and the measurement of the absorbance of the blood sedimentation measurement assembly are affected by the temperature, a separate thermostat (or heating device) is usually provided in the existing blood sedimentation measurement apparatus to keep the temperature of the blood sample and the temperature of the blood sedimentation measurement assembly within a range. However, the provision of the thermostat device may cause uneven temperature distribution of the blood sedimentation measurement assembly and the blood sample, deteriorating ESR measurement accuracy. Furthermore, even if a thermostat is provided, the blood sample often needs to be preheated before it enters the blood sedimentation measurement assembly, which results in a slow blood sedimentation detection speed.

Based on this, in order to rapidly obtain ESR values capable of more accurately reflecting the natural sedimentation rate of erythrocytes, the present application first proposes a technical solution for correcting parameters characterizing the degree of erythrocyte aggregation of a blood sample using temperature.

Referring to fig. 1, an embodiment of the present application provides an apparatus 100 for measuring blood sedimentation, including a sampling and dispensing device 10, a blood sedimentation detecting device 20, a temperature acquiring device 30 and a data processing device 40.

The sample distribution device 10 is arranged for collecting a blood sample and for at least partially distributing the blood sample to the blood sedimentation detection device 20.

The blood sedimentation detection device 20 comprises a detection pipeline, an optical detection component and a power component connected with the detection pipeline. The power assembly is arranged to transport the dispensed blood sample portion into the detection circuit, the detection circuit is arranged to provide a detection site for the dispensed blood sample portion, and the optical detection assembly is arranged to detect the blood sample portion in the detection circuit in order to obtain a parameter of the blood sample indicative of the extent of red blood cell aggregation.

The temperature acquisition device 30 is arranged to acquire the temperature of the blood sample portion in the blood sedimentation detection device 20.

The data processing device 40 is arranged to obtain the temperature of the blood sample part and parameters characterizing the extent of aggregation of the red blood cells, and to calculate the corrected erythrocyte sedimentation rate of the blood sample from the temperature of the blood sample part and the parameters characterizing the extent of aggregation of the red blood cells.

Accordingly, referring to fig. 2, the embodiment of the present application further provides a blood sedimentation measurement method applied to a blood sedimentation measurement device, including the following steps:

s201: obtaining parameters representing the aggregation degree of red blood cells of a blood sample to be measured by blood sedimentation measurement equipment;

s202: acquiring the temperature of the blood sample to be measured when performing blood sedimentation measurement by blood sedimentation measurement equipment;

s203: calculating, by a blood sedimentation measurement device, a corrected erythrocyte sedimentation rate of the blood sample from the temperature and the parameter indicative of the extent of erythrocyte aggregation.

The blood sedimentation measurement method provided by the embodiment of the present application is implemented in particular by the blood sedimentation measurement apparatus 100 provided by the embodiment of the present application.

Compared with the existing blood sedimentation measurement equipment, the blood sedimentation measurement equipment provided by the embodiment of the application can correct parameters representing the aggregation degree of the red blood cells according to the temperature of the blood sample, so that the more accurate sedimentation rate of the red blood cells can be obtained. Furthermore, since the influence of temperature on blood sedimentation detection is compensated, a heating assembly for bringing the blood sedimentation measurement device to a constant temperature state can be eliminated. Even in the case where such a heating element is provided, the target heating temperature (i.e., constant temperature) of the heating element can be reduced due to the temperature compensation design proposed by the present invention, and thus a heating element having a smaller heating power can be used.

The blood sedimentation measurement apparatus and the blood sedimentation measurement method provided in the present application are further described below with reference to fig. 3 to 10.

In some embodiments, data processing device 40 may include a processor including, but not limited to, a central processing unit (Central Processing Unit, CPU), a micro control unit (Micro Controller Unit, MCU), a Field programmable gate array (Field-Programmable Gate Array, FPGA), a Digital Signal Processor (DSP), etc., for interpreting computer instructions and processing data in computer software.

Referring to fig. 3, in some embodiments, the sample dispensing device 10 may include a sample needle 11, a power supply line 12, and a sample power assembly 13. The power supply line 12 is connected at both ends 121, 122 to a sampling power assembly 13 and a sampling needle 11, respectively, the sampling power assembly 13 being arranged for driving the sampling needle 11 through the power supply line 12 to aspirate or discharge a blood sample. For example, sampling power assembly 13 provides negative pressure to the sampling needle through power supply line 12 to aspirate the blood sample and positive pressure to discharge the blood sample. The sampling power assembly 13 may be a pump or syringe or other source of power, such as a positive and negative air pressure source.

Blood sedimentation detection device 20 may include a detection circuit 21, a power assembly 22, and an optical detection assembly having a light emitter 231 and a light receiver 232. In the embodiment shown in fig. 3, the detection line 21 is part of the power supply line 12 and the power assembly 22 is the sampling power assembly 13. In other embodiments, the detection line 21 may be a line branching from the power supply line 12, with the power assembly 22 being a different component than the sampling power assembly 13.

The test line 21 is used to provide a test site for the dispensed portion of the blood sample to be tested. The power assembly 22 (currently configured as a syringe) is configured to transport the dispensed blood sample portion into the test line 21. For example, the power assembly 22 may draw a blood sample collected by the sample distribution device 10 into the test tubing 21. The light emitter 231 and the light receiver 232 are respectively located at both sides of the detection pipe 21. The light emitter 231 is used to illuminate the blood sample in the test line. The light receiver 232 is used to detect the amount of change in the light emitted by the light emitter 231 after irradiating the blood sample (e.g., receiving the light transmitted and/or scattered by the blood sample), and to detect the extent of absorption or scattering of the light by the blood sample in the detection line 21 by detecting how much light is received. Since the scattering or transmission of the light irradiated on the blood sample is changed during the aggregation (rouleaux formation) of the red blood cells in the blood sample, the degree of scattering or absorption of the light by the blood sample can be detected by detecting the amount of the transmitted or scattered light after receiving the irradiated blood sample, thereby measuring the sedimentation rate of the red blood cells.

Upon activation of the blood sedimentation testing device 20 for testing, the power assembly 22 drives the dispensed blood sample portion into the testing line 21 and stops the movement of the blood sample portion after it has flowed into the testing line 21, and then holds the blood sample portion stationary. The light emitter 231 irradiates the blood sample portion in the detection circuit 21, and the light receiver 232 detects the degree to which the light emitted from the light emitter 231 is backscattered or transmitted from the blood sample portion in the irradiation detection circuit 21, so as to detect the degree of red blood cell aggregation, such as the red blood cell aggregation speed, of the blood sample to be measured.

In some embodiments, the power assembly 22 is further configured to flow the blood sample portion back and forth in the detection line 21 after the blood sample portion is conveyed into the detection line 21 and before the optical detection assembly detects the blood sample portion, so as to deagglomerate red blood cells in the blood sample portion. Thereby enabling the red blood cells in the blood sample portion in the detection circuit 21 to be in a dispersed state as much as possible before the optical detection assembly having the light emitter 231 and the light receiver 232 detects the degree of red blood cell aggregation, so that the degree of red blood cell aggregation can be measured more accurately.

In particular, in the case where the power unit 22 is configured as a syringe, since the movement speed and movement direction of the syringe can be flexibly set, the blood sample can be flexibly disaggregated, and the blood volume can be saved.

In some embodiments, the power assembly 22 is further configured to stop driving immediately after the blood sample portion is caused to flow back and forth in the detection circuit 21 a predetermined number of times, thereby holding the blood sample portion stationary in the detection circuit 21 so that the optical detection assembly detects transmitted light transmitted through or scattered light scattered by the blood sample portion. At this time, the parameter characterizing the degree of aggregation of red blood cells includes a parameter related to the transmitted light or scattered light.

In some embodiments, the optical detection assembly has a height of no greater than 50 mm; and/or the optical detection assembly has a length of no more than 20 mm; and/or the optical detection assembly has a width of no more than 15 mm.

In some embodiments, the optical detection assembly has a volume of no greater than 50mm x 20mm x 15 mm. For example, as shown in FIG. 4, the optical detection assembly has a volume of 50mm 17mm 15 mm.

In some embodiments, the detection line 21 is made of a hose. Therefore, the detection pipe 21 may be flexibly arranged, for example, may be vertically, horizontally or obliquely arranged, or may be bent, which is not limited. Preferably, the detection line 21 is formed as a capillary tube.

In some embodiments, the blood sedimentation detection device 20 may also include a heating assembly. The heating assembly is provided for maintaining the temperature of the blood sedimentation detection device 20 within a preset range. Referring to fig. 3 and 5, the heating assembly may include, for example, a heater 241 and a first temperature sensor 242. The first temperature sensor 242 is disposed beside the optical detection assembly and is used to detect a first temperature of the optical detection assembly. The heater 241 is provided for being manipulated according to a set target temperature and a first temperature of the optical detection assembly to maintain the temperature of the blood sedimentation detection device 20 within a preset range.

Here, the heater 241 may be, for example, a resistance wire, a heating rod, a heating film, or the like. The first temperature sensor 242 may be, for example, a thermocouple, a thermistor, an NTC, or the like.

In some embodiments, the set target temperature may be predetermined in relation to an ambient temperature of the environment in which the blood sedimentation measurement device 100 is located.

In some embodiments, the temperature acquisition device 30 may include a first temperature sensor 242. Accordingly, the temperature for correction may include the first temperature. The temperature detected by the first temperature sensor 242 can reflect the temperature of the blood sample portion in the detection circuit 21.

In some embodiments, referring to fig. 5, the blood sedimentation measurement apparatus 100 may further include a second temperature sensor 25 disposed outside the blood sedimentation detection device 20, and the temperature acquisition device 30 may include the second temperature sensor 25. The temperature detected by the second temperature sensor 25 can also reflect the temperature of the blood sample portion in the detection line 21.

In some embodiments, the temperature acquisition device 30 may be configured to obtain an ambient temperature of the environment in which the blood sedimentation measurement apparatus 100 is located. The ambient temperature can also reflect the temperature of the blood sample portion in the test line 21.

In some embodiments, the data processing device 40 may use one or more of the temperature detected by the first temperature sensor 242, the temperature detected by the second temperature sensor 25, and the ambient temperature to modify a parameter indicative of the extent of red blood cell aggregation to calculate ESR1 of the blood sample.

In some embodiments, the data processing device 40 is further configured to modify a parameter indicative of the extent of red blood cell aggregation based on the temperature of the blood sample portion and the pre-stored mapping model, and to calculate the modified erythrocyte sedimentation rate ESR1 based on the modified parameter indicative of the extent of red blood cell aggregation. Wherein the pre-stored mapping model describes the correspondence between the temperature of the blood sample portion, the parameter indicative of the extent of red blood cell aggregation and the modified parameter indicative of the extent of red blood cell aggregation.

In other embodiments, the data processing device 40 is further configured to input the temperature of the blood sample portion and the parameter indicative of the extent of red blood cell aggregation into a pre-stored mapping model describing the correspondence between the temperature of the blood sample portion, the parameter indicative of the extent of red blood cell aggregation and the corrected sedimentation rate of red blood cells to obtain an output of the pre-stored mapping model as ESR1. For example, the temperature of the blood sample portion and the parameter characterizing the degree of erythrocyte aggregation are taken as two variables of a binary function, and the function value of the binary function is ESR1.

In some embodiments, the pre-stored mapping model may be a polynomial fit function or a lookup table. The pre-stored mapping model is stored, for example, in the data processing device 40.

In some embodiments, the parameter indicative of the extent of red blood cell aggregation may include a parameter related to transmitted light transmitted through or scattered light scattered by the blood sample portion. In particular, the parameters characterizing the extent of red blood cell aggregation include parameters related to the red blood cell aggregation curve of the light intensity of transmitted or scattered light over time.

Fig. 6 shows a red blood cell aggregation curve C measured by a blood sedimentation detection device 20 provided in accordance with an embodiment of the present application, wherein the transmittance (which may also be referred to as transmissivity) is a relative light intensity, equal to the ratio of the transmitted light intensity to the background light intensity. Wherein parameters characterizing the extent of red blood cell aggregation can be extracted from the red blood cell aggregation curve C.

In some embodiments, the parameter characterizing the extent of red blood cell aggregation comprises at least one of the following parameters:

an area AUC (Area Under Curve) surrounded by the red blood cell aggregation curve C and the time axis in a period from the measurement start time point T1 to the measurement end time point T2;

calculating the corrected erythrocyte sedimentation rate ESR2 based on the area AUC and a prestored calibration curve;

a minimum value of the transmitted light intensity in a period between the measurement start time point T1 and the measurement end time point T2;

the difference d=l2-L1 between the transmitted light intensity L1 at the measurement start time point T1 and the transmitted light intensity L2 at the measurement end time point T2;

a time point T3 corresponding to 1/2 (l3=l2/2) of the transmitted light intensity L2 at the measurement end time point T2.

In some embodiments, the pre-stored calibration curve is stored, for example, in the data processing device 40.

Fig. 7 shows a calibration curve (which may also be referred to as a calibration curve) for calculating the erythrocyte sedimentation rate ESR2 before correction, wherein the abscissa is AUC and the ordinate is erythrocyte sedimentation rate ESR2 before correction. Therefore, as long as the red blood cell aggregation curve of the blood sample to be measured is obtained, and the area AUC surrounded by the red blood cell aggregation curve and the time axis in the period from the measurement start time point t1 to the measurement end time point t2 is obtained by the red blood cell aggregation curve, ESR2 can be obtained by the calibration curve.

Through research, the red blood cell aggregation curve AUC of a blood sample has a correlation with the weissel ESR, and therefore, the calibration curve can be fitted through the red blood cell aggregation curve AUC and the weissel ESR statistics of a large number of blood samples. That is, a large number of blood samples are simultaneously examined with the blood sedimentation measuring apparatus and the welt method measuring apparatus (including a sedimentation tube) provided in accordance with the present application to obtain the erythrocyte aggregation curve AUC and the welt method ESR of these blood samples, and then a calibration curve is obtained based on these data.

In some embodiments, the calibration curve is stored in the data processing device 40 in the form of a series of discrete points, so that the ESR2 can be obtained based on AUC in the calibration curve by means of a look-up table and interpolation.

Of course, in other embodiments, the calibration curve is stored in the data processing means 40 in the form of a fitting function, so that the fitting function can be used to calculate ESR2 based on AUC.

In other embodiments, the temperature of the blood sample portion may also be used to compensate for any intermediate values in the calculation of the erythrocyte sedimentation rate by the blood sedimentation detection device 20, such as gain values in an analog circuit or the like.

In some embodiments, the parameter characterizing the extent of erythrocyte aggregation may include the area AUC. Accordingly, the data processing device 40 is arranged to modify the AUC according to the temperature of the blood sample part to obtain a modified AUC, and calculate ESR1 based on the modified AUC and a pre-stored calibration curve.

In other embodiments, the parameter indicative of the extent of erythrocyte aggregation may include erythrocyte sedimentation rate ESR2 prior to correction. Accordingly, the data processing device 40 is arranged to obtain a correction amount from a pre-stored fitted curve of temperature-blood sedimentation measurement deviations from the temperature of the blood sample portion and calculate ESR1 from the correction amount and ESR2.

Fig. 8 shows a fitted curve of temperature-blood sedimentation measurement deviation, wherein the abscissa is the temperature of the blood sample portion and the ordinate is the blood sedimentation measurement deviation. For example, when the temperature of the blood sample portion is 5 degrees celsius and ESR2 is a, the blood sedimentation measurement deviation (correction amount) is 28% by interpolation from the fitted curve shown in fig. 8, and the data processing device 40 can calculate esr1=a/(1 to 0.28) from the correction amount and ESR2.

In addition, factors that cause the aggregation curve of red blood cells, such as AUC, to change with temperature include the change in light intensity of the light emitter 231 with temperature in addition to the change in ESR value with temperature due to the temperature characteristics of the blood itself. Thus, in some embodiments, the temperature of the optical detection assembly may additionally be used to modify a parameter indicative of the extent of red blood cell aggregation, i.e., the data processing device 40 may modify a parameter indicative of the extent of red blood cell aggregation (e.g., ESR 2) based on the temperature of the blood sample portion in the blood sedimentation detection device 20 acquired by the temperature acquisition device 30 and the first temperature of the optical detection assembly to calculate a modified erythrocyte sedimentation rate ESR1. Thus, a more accurate erythrocyte sedimentation rate can be obtained.

For example, fig. 9 shows a fitted curve of temperature-blood sedimentation measurement deviation based on the temperature characteristic of blood itself, wherein the abscissa is the temperature of the blood sample and the ordinate is the blood sedimentation measurement deviation. Fig. 10 shows a fitted curve of temperature-blood sedimentation measurement deviation based on the temperature characteristic of the light emitter 231, wherein the abscissa is the temperature of the optical detection assembly and the ordinate is the blood sedimentation measurement deviation. The data processing means 40 may be arranged to calculate the function ess1=ess2+f _b (T _b )+f _l (T _l ) To calculate the corrected erythrocyte sedimentation rate ESR1, wherein f _b (T _b ) Representing the temperature T in terms of the blood sample portion _b Correction amount, f, determined from fitted curve of temperature-blood sedimentation measurement deviation shown in FIG. 9 _l (T _l ) Indicating a first temperature T according to the optical detection assembly _l Correction amounts determined from the fitted curve of the temperature-blood sedimentation measurement deviation shown in fig. 10.

The embodiment of the application also provides a sample analyzer. Referring to fig. 11, a sample analyzer provided in an embodiment of the present application includes: the sample distribution device 10, the blood sedimentation detection device 20, the blood routine detection device 50, and a controller (not shown in the figure).

The sample distribution device 10 is arranged for collecting a blood sample and for distributing the blood sample at least partly to the blood conventional detection device 50 and the blood sedimentation detection device 20, respectively. Wherein the sampling and dispensing device 10 comprises a sampling needle 11, a power supply line 12 and a sampling power assembly 13, the power supply line 12 is connected with the sampling power assembly 13 and the sampling needle 11 at both ends respectively, and the sampling power assembly 13 is provided for driving the sampling needle 11 to suck or discharge a blood sample through the power supply line 12.

The blood sedimentation detection device 20 includes a blood sedimentation detection line 21, a blood sedimentation optical detection assembly 23, and a heating assembly 24. The blood sedimentation detection line 21 is provided as a part of the power supply line 12, the sampling power assembly 13 is further provided for transporting the blood sample into the blood sedimentation detection line 21, the blood sedimentation optical detection assembly 23 is provided beside the blood sedimentation detection line 21 and for detecting a parameter characterizing the extent of aggregation of red blood cells of the blood sample portion in the blood sedimentation detection line 21, and the heating assembly 24 is provided for maintaining the temperature of the blood sedimentation detection device 20 within a preset range.

The blood routine detecting device 50 includes a blood routine reaction tank 51 and a blood routine detecting member (not shown in the drawing), the blood routine reaction tank 51 being provided for receiving a processing reagent and a blood sample portion dispensed by the sample dispensing device 10, the blood routine detecting member being provided for performing blood routine parameter detection on a sample liquid to be measured obtained by mixing the blood sample portion in the blood routine reaction tank 51 with the processing reagent.

The controller is communicatively connected to the blood sedimentation detection device 20, the blood routine detection device 50, the sample distribution device 10 and is arranged for:

causing the sample distribution device 10 to collect a predetermined amount of blood sample such that after collection is completed and before the blood sample is at least partially distributed to the blood sedimentation detection device 50, the blood sample is present in the blood sedimentation detection line 21, as shown in the left-hand diagram of fig. 12, so that the heating assembly 24 can preheat the blood sample present in the blood sedimentation detection line 21;

causing the sample distribution device 10 to distribute a part of the collected blood sample to the blood routine reaction cell 51 of the blood routine detection device 50;

after the distribution of the blood sample to the blood sedimentation testing device 50 is completed, the blood sample portion in the blood sedimentation testing line 21 and the blood sample portion in the blood sedimentation reaction tank 51 are tested in parallel by the blood sedimentation optical testing assembly 23 and the blood sedimentation testing assembly.

Thus, by disposing the blood sedimentation detection device 20 at the rear of the sampling needle so that the blood sample portion for blood sedimentation detection after the completion of sample suction, i.e., the blood sample portion for blood sedimentation detection enters the blood sedimentation detection line 21 to be heated, the warm-up time of the blood sample portion for blood sedimentation detection alone can be effectively saved, so that the blood sedimentation detection speed can be matched with the blood conventional detection speed.

Those skilled in the art will appreciate that the blood routine testing components of the blood routine testing device 50 may include at least one of an optical testing unit, an impedance testing unit, and a hemoglobin testing unit. Accordingly, the blood conventional reaction cell 51 may include at least one of an optical detection reaction cell, an impedance detection reaction cell, and a hemoglobin detection reaction cell. When the blood sample is subjected to routine blood testing by the blood cell testing device 30, the blood sample and corresponding reagents (e.g., diluents and/or hemolysis agents and/or staining agents, etc.) may be added to the reaction cell 51, and the blood sample in the reaction cell 51 may be measured by the testing component to obtain at least one blood cell parameter, which may include at least one or more of WBC (White blood cell) classification parameters, WBC count and morphology parameters, HGB (Hemoglobin) parameters, RBC (Red blood cell) and PLT (blood platelet) count and morphology parameters.

Here, the controller may include a processor including, but not limited to, a central processing unit (Central Processing Unit, CPU), a micro control unit (Micro Controller Unit, MCU), a Field programmable gate array (Field-Programmable Gate Array, FPGA), a Digital Signal Processor (DSP), etc. for interpreting computer instructions and processing data in computer software.

In some embodiments, the controller is further configured to control the sample distribution device to maintain a blood sample in the blood sedimentation testing line after completion of distribution of the blood sample to the blood routine testing device, as shown in the right-hand side view of fig. 12. It can thereby be ensured that the blood sample portion for blood sedimentation detection is still located in the blood sedimentation detection line 21 after completion of the blood regular blood separation. That is, the blood sample portion for blood sedimentation detection is in the blood sedimentation detection device 20 from after the blood sample is collected by the sample distribution device 10 until the conventional blood separation of the blood is completed, whereby the warm-up time of the blood sample portion for blood sedimentation detection alone can be further saved.

In some embodiments, the length between the end of the blood sedimentation detection line 21 proximate to the sampling power assembly 13 and the end of the power supply line 12 connected to the sampling needle 11 is less than a predetermined length, wherein the predetermined length is defined as the length of the blood sample portion in the power supply line 13 after the blood sample required by the blood sedimentation detection device 20 and the blood routine detection device 50 is drawn into the sampling needle 11 and the power supply line 13 by the sampling power assembly 13. This can avoid waste of blood caused by the presence of a blood sample in the blood sedimentation detection line 21 after blood collection.

In some embodiments, the controller is further configured to obtain a temperature of a portion of the blood sample in the blood sedimentation detection device 20 and to obtain a parameter indicative of a degree of red blood cell aggregation, and to calculate a corrected erythrocyte sedimentation rate of the blood sample from the temperature of the portion of the blood sample and the parameter indicative of the degree of red blood cell aggregation.

In some embodiments, the controller is further configured to: correcting parameters representing the aggregation degree of the red blood cells according to the temperature of the blood sample part and a prestored mapping model, and calculating the corrected sedimentation rate of the red blood cells according to the corrected parameters representing the aggregation degree of the red blood cells. Wherein the pre-stored map describes a correspondence between the temperature of the blood sample portion, a parameter indicative of the extent of red blood cell aggregation, and a modified parameter indicative of the extent of red blood cell aggregation.

In some embodiments, the sampling dynamics assembly 13 is further configured to flow the blood sample portion back and forth in the blood sedimentation detection line 21 after the blood sample portion is conveyed into the blood sedimentation detection line 21 and before the blood sample portion is detected by the blood sedimentation optical detection assembly 23, so as to subject the blood sample portion to a deagglomeration process of red blood cells. The sampling power assembly 13 is further configured to stop driving immediately after the blood sample portion is caused to flow back and forth in the blood sedimentation detection line 21 a predetermined number of times, thereby keeping the blood sample portion stationary in the blood sedimentation detection line 21 so that the blood sedimentation optical detection assembly 23 detects the transmitted light transmitted through the blood sample portion or the scattered light scattered through the blood sample portion.

In a specific example, the working procedure of the sample analyzer provided in the embodiment of the present application is as follows: first, the sampling power assembly 13 drives the sampling needle 11 to draw a predetermined amount of blood sample so that the blood sample is filled from the sampling needle into the blood sedimentation detection line 21, as shown on the left side of fig. 12. Next, the sampling power assembly 13 drives the sampling needle 11 to dispense a portion of the blood sample to the blood conventional reaction cell 51, and after the blood sample is dispensed to the blood conventional reaction cell 51, the blood sedimentation detection line 21 is still filled with the blood sample, as shown on the right side of fig. 12. Next, the blood sample portion in the blood sedimentation detecting reservoir 51 is detected by the blood sedimentation detecting assembly, and at the same time, the blood sample portion in the blood sedimentation detecting line 21 is driven by the sampling power assembly 13 to flow back and forth in the blood sedimentation detecting line 21 a predetermined number of times, and then immediately the driving is stopped, so that the blood sample portion is held stationary in the blood sedimentation detecting line 21, so that the transmitted light transmitted through the blood sample portion or the scattered light scattered through the blood sample portion is detected by the blood sedimentation optical detecting assembly 23, thereby obtaining the red blood cell aggregation curve.

In some embodiments, the parameter indicative of the extent of red blood cell aggregation comprises a parameter related to a red blood cell aggregation curve of the light intensity of the transmitted or scattered light over time. In particular, the parameters characterizing the extent of erythrocyte aggregation include at least one of the following parameters:

For example, in case the parameter characterizing the extent of aggregation of erythrocytes comprises the area AUC, the controller is further arranged to: the AUC is corrected based on the temperature of the blood sample portion to obtain a corrected AUC, and the corrected erythrocyte sedimentation rate is calculated based on the corrected AUC and a pre-stored calibration curve (e.g., stored in a controller).

In another example, where the parameter indicative of the extent of red blood cell aggregation includes a pre-correction erythrocyte sedimentation rate ESR2, the controller is further configured to: the correction is obtained from a pre-stored fitted curve of temperature-blood sedimentation measurement deviation (stored, for example, in a controller) based on the temperature of the blood sample portion, and the corrected erythrocyte sedimentation rate ESR1 is calculated from the correction and the erythrocyte sedimentation rate ESR2 before correction.

Other features and advantages of the sample analyzer provided in the embodiments of the present application may refer to the above description of the blood sedimentation measurement device and the blood sedimentation measurement method provided in the embodiments of the present application, and are not described herein again.

It should be noted that in this document, relational terms such as "first" and "second" and the like are used solely to distinguish one entity or action from another entity or action without necessarily requiring or implying any actual such relationship or order between such entities or actions. Moreover, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or apparatus. Without further limitation, an element defined by the phrase "comprising one … …" does not exclude the presence of other like elements in a process, method, article, or apparatus that comprises an element.

The features mentioned above in the description, in the drawings and in the claims may be combined with one another at will as far as they are relevant in the present application. The features and advantages described for the blood sedimentation measurement system according to the present application apply in a corresponding manner to the blood sedimentation measurement method and the sample analyzer according to the present application and vice versa.

The foregoing is merely a specific embodiment of the application to enable one skilled in the art to understand or practice the application. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other embodiments without departing from the spirit or scope of the application. Thus, the present application is not intended to be limited to the embodiments shown herein but is to be accorded the widest scope consistent with the principles and novel features disclosed herein.

Claims

1. A blood sedimentation measurement device comprises a sampling and distribution device, a blood sedimentation detection device, a temperature acquisition device and a data processing device;

2. The blood sedimentation measurement device of claim 1, wherein the blood sedimentation detection arrangement further comprises a heating assembly arranged to maintain the temperature of the blood sedimentation detection arrangement within a preset range.

3. The blood sedimentation measurement device of claim 1 or 2, wherein the data processing means is further arranged to:

correcting the parameter representing the aggregation degree of the red blood cells according to the temperature of the blood sample part and a prestored mapping model, wherein the prestored mapping model describes the corresponding relation among the temperature of the blood sample part, the parameter representing the aggregation degree of the red blood cells and the corrected parameter representing the aggregation degree of the red blood cells; and is also provided with

Calculating the corrected erythrocyte sedimentation rate according to the corrected parameters representing the erythrocyte aggregation degree.

4. The blood sedimentation measurement device of claim 1 or 2, wherein the data processing means is further arranged to:

inputting the temperature of the blood sample portion and the parameter representing the degree of aggregation of the red blood cells into a pre-stored mapping model to obtain an output of the pre-stored mapping model as the corrected sedimentation rate of the red blood cells, wherein the pre-stored mapping model describes a correspondence between the temperature of the blood sample portion, the parameter representing the degree of aggregation of the red blood cells and the corrected sedimentation rate of the red blood cells.

5. The blood sedimentation measurement device of claim 3 or 4, wherein the pre-stored mapping model is a polynomial fitting function or a look-up table.

6. The blood sedimentation measurement device of any one of claims 1 to 5, wherein the power assembly is further configured to:

flowing the blood sample portion back and forth in the test line after the blood sample portion is conveyed into the test line and before the optical test assembly tests the blood sample portion so as to deagglomerate red blood cells in the blood sample portion; and is also provided with

Immediately after the blood sample part is caused to flow back and forth in the detection line a predetermined number of times, the driving is stopped so that the blood sample part remains stationary in the detection line so that the optical detection assembly detects the transmitted light transmitted through the blood sample part or the scattered light scattered by the blood sample part, and the parameter indicative of the degree of aggregation of red blood cells includes a parameter related to the transmitted light or the scattered light.

7. The blood sedimentation measurement device of claim 6, wherein the parameter characterizing the extent of red blood cell aggregation comprises a parameter related to a red blood cell aggregation curve of the light intensity of the transmitted or scattered light over time.

8. The blood sedimentation measurement device of claim 7, wherein the parameter characterizing the extent of red blood cell aggregation comprises at least one of the following parameters:

the area surrounded by the red blood cell aggregation curve and the time axis in the time period from the measurement starting time point to the measurement ending time point;

calculating the erythrocyte sedimentation rate before correction based on the area and a prestored calibration curve;

a minimum value of transmitted light intensity in a period between a measurement start time point and a measurement end time point;

A difference between the transmitted light intensity at the measurement start time point and the transmitted light intensity at the measurement end time point;

at the time point corresponding to 1/2 of the transmitted light intensity at the measurement end time point.

9. The blood sedimentation measurement device of claim 8, wherein the parameter characterizing the extent of red blood cell aggregation comprises the area;

the data processing device is further configured to modify the area according to the temperature of the blood sample portion to obtain a modified area, and calculate the modified erythrocyte sedimentation rate based on the modified area and a pre-stored calibration curve.

10. The blood sedimentation measurement device of claim 8, wherein the parameter indicative of the extent of red blood cell aggregation comprises the pre-correction erythrocyte sedimentation rate;

the data processing device is further configured to obtain a correction amount from a pre-stored fitted curve of temperature-blood sedimentation measurement deviation according to the temperature of the blood sample portion, and calculate the corrected erythrocyte sedimentation rate according to the correction amount and the erythrocyte sedimentation rate before correction.

11. The blood sedimentation measurement device of claim 2, wherein the heating assembly comprises a heater and a first temperature sensor disposed alongside the optical detection assembly and configured to detect a first temperature of the optical detection assembly, the heater being operable to maintain the temperature of the blood sedimentation detection arrangement within the preset range in accordance with a set target temperature and the first temperature;

The temperature acquisition device includes the first temperature sensor.

12. The blood sedimentation measurement device of any one of claims 1 to 11, further comprising a second temperature sensor provided outside the blood sedimentation detection arrangement, the temperature acquisition arrangement comprising the second temperature sensor.

13. A blood sedimentation measurement device according to any one of claims 1 to 10, wherein the temperature acquisition means is arranged to obtain an ambient temperature of an environment in which the blood sedimentation measurement device is located, the temperature of the blood sample portion comprising the ambient temperature.

14. The blood sedimentation measurement device of claim 11, wherein the target temperature is predetermined in relation to an ambient temperature of an environment in which the blood sedimentation measurement device is located.

15. The blood sedimentation measurement device of any one of claims 1 to 14, wherein the optical detection assembly has a height of no more than 50 mm; and/or

The optical detection assembly has a length of no more than 20 mm; and/or

The optical detection assembly has a width of no greater than 15 mm; and/or

The optical detection assembly has a volume of no greater than 50mm x 20mm x 15 mm.

16. A blood sedimentation measurement method applied to blood sedimentation measurement equipment, comprising;

17. The method of claim 16, wherein calculating a corrected erythrocyte sedimentation rate for the blood sample based on the temperature and the parameter indicative of the extent of erythrocyte aggregation comprises:

correcting the parameter representing the aggregation degree of the red blood cells according to the temperature and a prestored mapping model, wherein the prestored mapping describes the corresponding relation among the temperature, the parameter representing the aggregation degree of the red blood cells and the corrected parameter representing the aggregation degree of the red blood cells; and is also provided with

18. The method of claim 16, wherein calculating a corrected erythrocyte sedimentation rate for the blood sample based on the temperature and the parameter indicative of the extent of erythrocyte aggregation comprises:

Inputting the temperature and the parameter representing the aggregation degree of the red blood cells into a prestored mapping model to obtain output of the prestored mapping model as the corrected sedimentation rate of the red blood cells, wherein the prestored mapping model describes the corresponding relation among the temperature of the blood sample part, the parameter representing the aggregation degree of the red blood cells and the corrected sedimentation rate of the red blood cells.

19. The blood sedimentation measurement method of claim 17 or 18, wherein the pre-stored mapping model is a polynomial fitting function or a look-up table.

20. A method of blood sedimentation measurement according to any one of claims 16 to 19 in which the parameter characterising the extent of erythrocyte aggregation comprises: parameters related to the red blood cell aggregation curve of the light intensity of the transmitted light transmitted through or scattered light scattered by the blood sample to be measured over time.

21. The method of claim 20, wherein the parameter indicative of the extent of erythrocyte aggregation comprises at least one of the following:

22. The method of claim 21, wherein the parameter indicative of the extent of red blood cell aggregation comprises the area;

calculating a corrected erythrocyte sedimentation rate of the blood sample from the temperature and the parameter indicative of the extent of erythrocyte aggregation, comprising: and correcting the area according to the temperature to obtain a corrected area, and calculating the corrected erythrocyte sedimentation rate based on the corrected area and a pre-stored calibration curve.

23. The method of claim 21, wherein the parameter indicative of the extent of red blood cell aggregation comprises the pre-correction erythrocyte sedimentation rate;

calculating a corrected erythrocyte sedimentation rate of the blood sample from the temperature and the parameter indicative of the extent of erythrocyte aggregation, comprising: and obtaining a correction amount from a prestored fitting curve of temperature-blood sedimentation measurement deviation according to the temperature, and calculating the corrected erythrocyte sedimentation rate according to the correction amount and the erythrocyte sedimentation rate before correction.

24. A sample analyzer comprises a blood sedimentation detection device, a blood routine detection device, a sampling and distributing device and a controller;

25. The sample analyzer of claim 24, wherein the controller is further configured to control the sample distribution device to maintain a blood sample in the blood sedimentation testing line after the completion of the distribution of the blood sample to the blood routine testing device.

26. The sample analyzer of claim 24 or 25, wherein a length between an end of the blood sedimentation detection line proximate the sampling power assembly and an end of the power supply line connected to the sampling needle is less than a predetermined length, wherein the predetermined length is defined as a length of a portion of the blood sample in the power supply line after a blood sample required by the blood sedimentation detection device and the blood routine detection device is drawn into the sampling needle and the power supply line by the sampling power assembly.

27. The sample analyzer of any one of claims 24 to 26, wherein the controller is further configured to obtain a temperature of a blood sample portion in the blood sedimentation detection device and to obtain the parameter indicative of the extent of red blood cell aggregation, and to calculate a corrected erythrocyte sedimentation rate of the blood sample from the temperature of the blood sample portion and the parameter indicative of the extent of red blood cell aggregation.

28. The sample analyzer of claim 27, wherein the controller is further configured to:

correcting the parameter representing the aggregation degree of the red blood cells according to the temperature of the blood sample part and a prestored mapping model, wherein the prestored mapping describes the corresponding relation among the temperature of the blood sample part, the parameter representing the aggregation degree of the red blood cells and the corrected parameter representing the aggregation degree of the red blood cells; and is also provided with

29. The sample analyzer of claim 27 or 28, wherein the sampling power assembly is further configured to:

flowing the blood sample portion back and forth in the blood sedimentation testing line after the blood sample portion is conveyed into the blood sedimentation testing line and before the blood sample portion is tested by the blood sedimentation optical testing assembly so as to depolymerize red blood cells in the blood sample portion;

immediately after the blood sample portion is caused to flow back and forth in the blood sedimentation detection line a predetermined number of times, the driving is stopped so that the blood sample portion remains stationary in the blood sedimentation detection line so that the blood sedimentation optical detection assembly detects the transmitted light transmitted through the blood sample portion or the scattered light scattered through the blood sample portion, and the parameter indicative of the degree of aggregation of red blood cells includes a parameter related to a red blood cell aggregation curve in which the light intensity of the transmitted light or the scattered light varies with time.

30. The sample analyzer of claim 29, wherein the parameter indicative of the extent of red blood cell aggregation comprises at least one of the following:

calculating the corrected red blood cell sedimentation rate based on the area and a prestored calibration curve;

31. The sample analyzer of claim 30, wherein the parameter indicative of the extent of red blood cell aggregation comprises the area;

the controller is further configured to: and correcting the area according to the temperature of the blood sample part to obtain a corrected area, and calculating the corrected erythrocyte sedimentation rate based on the corrected area and a prestored calibration curve.

32. The sample analyzer of claim 30, wherein the parameter indicative of the extent of red blood cell aggregation comprises the pre-correction erythrocyte sedimentation rate;

The controller is further configured to: and obtaining a correction amount from a prestored fitting curve of temperature-blood sedimentation measurement deviation according to the temperature of the blood sample part, and calculating the corrected erythrocyte sedimentation rate according to the correction amount and the erythrocyte sedimentation rate before correction.