CN112798769B - Cell analysis method and device of cell analyzer and cell analyzer - Google Patents
Cell analysis method and device of cell analyzer and cell analyzer Download PDFInfo
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- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/483—Physical analysis of biological material
- G01N33/487—Physical analysis of biological material of liquid biological material
- G01N33/49—Blood
Abstract
A cell analysis method of cell analyzer includes such steps as outputting voltage signal to obtain electric pulse signal data according to the blood sample detected by cell analyzer, and detectingSequentially acquiring the pulse width W of each pulse signal in the electric pulse signal datan. Then the pulse width W of each pulse signal is obtainednAnd compensating, and counting the pulse signals of which the compensated pulse width W accords with a preset value. And then obtaining the detection result of the cell analyzer according to the counting result. Due to the pulse width WnThe compensation coefficient for compensation is related to the rotating speed of the motor for driving the blood sample to flow when the cell analyzer detects, so that a correct detection result can be output according to detection data when the rotating speed of the motor is not a fixed value, the detection speed of a project is further improved, the detection quantity of samples in unit time is increased, and the product performance of the cell analyzer is improved.
Description
Technical Field
The invention relates to the technical field of cell analyzers, in particular to a cell analysis method and device of a cell analyzer and the cell analyzer.
Background
A blood cell analyzer is an instrument that can detect cells in blood, and can count and classify cells such as White Blood Cells (WBCs), red blood cells, platelets, nucleated red blood cells, reticulocytes, and the like. For example, a blood cell analyzer is most commonly used for detecting leukocytes, and the laser scattering method is used for classifying and counting leukocytes by irradiating cells flowing through a detection area with laser light and collecting light signals reflected or scattered by the cells. The optical signals include forward scattered light, side scattered light, fluorescence, and the like. The forward scattering light signal reflects the size information of the cell, the side scattering light signal reflects the complexity of the internal structure of the cell, and the fluorescence signal reflects the content of substances such as DNA and RNA which can be stained by fluorescent dye in the cell. After the scattered light signals are converted into electric pulse signals, the white blood cells can be classified, and the count value of the white blood cells can be obtained. In the prior art, in order to obtain stable detection data, a blood cell analyzer does not detect the time of the front segment of a sample detection period or discards the data of the initial detection period, because the flow rate of the initial sample flowing through a detection region is unstable, so that the electric pulse signal caused by white blood cells is uncertain, and the detection data is inaccurate. Discarding the detection data or not performing data collection at the initial stage of the time sequence leads to prolonged detection time of the detection items and waste of samples.
Disclosure of Invention
The invention mainly solves the technical problem of how to improve the detection speed of a cell analyzer and reduce the waste of samples.
According to a first aspect, there is provided in one embodiment a cell analysis method of a cell analyzer, comprising:
acquiring electric pulse signal data according to a voltage signal output when the cell analyzer detects the blood sample; the electrical pulse signal data is related to cells in the blood sample detected by the cell analyzer;
sequentially acquiring the pulse width W of each pulse signal in the electric pulse signal data according to the detected time sequencen；
For the pulse width W of each obtained pulse signalnCompensating to obtain compensated pulse width W; wherein the pulse width W and the pulse width W are compensatednIn a direct proportional relationship, a compensation factor is related to the rotation speed of a motor driving the blood sample to flow when the cell analyzer detects the blood sample;
counting the pulse signals of which the compensation pulse width W accords with a preset value in the electric pulse signals to obtain a counting result;
and acquiring and outputting the detection result of the cell analyzer according to the counting result.
In one embodiment, the formula for obtaining the compensated pulse width W includes:
when 0 is present<t<At T, W = (W)n*fmax)/{fmin+[(fmax-fmin)/e(3-T/t) ]}；
Wherein T is the time for the cell analyzer to detect the blood sample, T is the time for the motor to accelerate from rest to a preset rotation speed, W is the compensation pulse widthnFor the pulse width value of the detected pulse signal, fmaxFor a predetermined rotational speed, f, of the motorminThe starting point rotating speed when the motor is accelerated.
In one embodiment, the obtaining the detection result of the cell analyzer according to the counting result includes:
compensating the counting result, wherein the compensation formula comprises:
when 0 is present<t<At T, Num = (N)n*fmax)/{fmin+[(fmax-fmin)/e(3-T/t) ]}；
Wherein T is the time for detecting the blood sample by the cell analyzer, T is the time for accelerating the motor from rest to a preset rotating speed, Num is a compensated counting result, and N isnTotal number of cells detected for current minimum time period, fmaxFor a predetermined rotational speed, f, of the motorminThe starting point rotating speed when the motor is accelerated.
In one embodiment, the method further comprises:
when T is<t, stopping pulse width W of each obtained pulse signalnCompensation is performed.
In one embodiment, the method further comprises:
and when T < T, stopping compensating the counting result, and taking the counting result as the detection result of the cell analyzer.
According to a second aspect, there is provided in one embodiment a cell analysis apparatus of a cell analyzer, comprising:
the data acquisition module is used for detecting a voltage signal of the blood sample according to the cell analyzer and acquiring electric pulse signal data; the electrical pulse signal data is related to cells in the blood sample detected by the cell analyzer;
a pulse width acquisition module for sequentially acquiring the pulse width W of each pulse signal in the electric pulse signal data according to the detected time sequencen；
A pulse width compensation module for obtaining the pulse width W of each pulse signalnCompensating to obtain compensated pulse width W; wherein the pulse width W and the pulse width W are compensatednIn a direct proportional relationship, a compensation factor is related to the rotation speed of a motor driving the blood sample to flow when the cell analyzer detects the blood sample;
the result output module is used for counting the pulse signals of which the compensation pulse width W accords with a preset value in the electric pulse signals so as to obtain counting results; and the result output module is also used for acquiring and outputting the detection result of the cell analyzer according to the counting result.
In one embodiment, the formula for obtaining the compensated pulse width W includes:
when 0 is present<t<At T, W = (W)n*fmax)/{fmin+[(fmax-fmin)/e(3-T/t) ]}；
Wherein T is the time for the cell analyzer to detect the blood sample, T is the time for the motor to accelerate from rest to a preset rotation speed, W is the compensation pulse widthnFor the pulse width value of the detected pulse signal, fmaxFor a predetermined rotational speed, f, of the motorminThe starting point rotating speed when the motor is accelerated is set;
the result output module is further configured to obtain a detection result of the cell analyzer according to the counting result, and includes:
compensating the counting result, wherein the compensation formula comprises:
when 0 is present<t<At T, Num = (N)n*fmax)/{fmin+[(fmax-fmin)/e(3-T/t) ]}；
Wherein T is the time for detecting the blood sample by the cell analyzer, T is the time for accelerating the motor from rest to a preset rotating speed, Num is a compensated counting result, and N isnTotal number of cells detected for current minimum time period, fmaxFor a predetermined rotational speed, f, of the motorminThe starting point rotating speed when the motor is accelerated.
In one embodiment, the pulse width compensation module is further configured to determine the time T<t, stopping pulse width W of each obtained pulse signalnPerforming compensation;
and the result output module is also used for stopping compensating the counting result when T < T and taking the counting result as the detection result of the cell analyzer.
According to a third aspect, there is provided in an embodiment a cell analyzer comprising the cell analysis device of the second aspect.
According to the cell analysis method of the above embodiment, firstly, the electric pulse signal data is obtained according to the voltage signal outputted when the cell analyzer detects the blood sample, and the pulse width W of each pulse signal in the electric pulse signal data is sequentially obtained according to the time sequence of detectionn. Then the pulse width W of each pulse signal is obtainednAnd compensating, and counting the pulse signals of which the compensated pulse width W accords with a preset value. And then obtaining the detection result of the cell analyzer according to the counting result. Due to the pulse width WnThe compensation coefficient for compensation is related to the rotating speed of the motor for driving the blood sample to flow when the cell analyzer detects, so that a correct detection result can be output according to detection data when the rotating speed of the motor is not a fixed value, the detection speed of a project is further improved, the detection quantity of samples in unit time is increased, and the product performance of the cell analyzer is improved.
Drawings
FIG. 1 is a schematic diagram of a blood cell analyzer;
FIG. 2 is a schematic structural view of a conveying apparatus in one embodiment;
FIG. 3 is a schematic diagram illustrating the detection of a sample flowing through the detection device according to one embodiment;
FIG. 4 is a graph showing voltage signals generated by cells according to an embodiment;
FIG. 5 is a method for analyzing cells in the cell analyzer according to an embodiment;
FIG. 6 is a view showing a cell analysis apparatus according to another embodiment;
FIG. 7 is a graph showing the number of leukocytes obtained by the cell analyzer in one embodiment;
FIG. 8 is a graph showing the number of leukocytes obtained after compensation by the cell analyzer in one example.
Detailed Description
The present invention will be described in further detail with reference to the following detailed description and accompanying drawings. Wherein like elements in different embodiments are numbered with like associated elements. In the following description, numerous details are set forth in order to provide a better understanding of the present application. However, those skilled in the art will readily recognize that some of the features may be omitted or replaced with other elements, materials, methods in different instances. In some instances, certain operations related to the present application have not been shown or described in detail in order to avoid obscuring the core of the present application from excessive description, and it is not necessary for those skilled in the art to describe these operations in detail, so that they may be fully understood from the description in the specification and the general knowledge in the art.
Furthermore, the features, operations, or characteristics described in the specification may be combined in any suitable manner to form various embodiments. Also, the various steps or actions in the method descriptions may be transposed or transposed in order, as will be apparent to one of ordinary skill in the art. Thus, the various sequences in the specification and drawings are for the purpose of describing certain embodiments only and are not intended to imply a required sequence unless otherwise indicated where such sequence must be followed.
The numbering of the components as such, e.g., "first", "second", etc., is used herein only to distinguish the objects as described, and does not have any sequential or technical meaning. The term "connected" and "coupled" when used in this application, unless otherwise indicated, includes both direct and indirect connections (couplings).
Referring to fig. 1, a schematic diagram of a blood cell analyzer is shown, the blood cell analyzer includes an optical detection device 20, a conveying device 30, a data processing device 40 and a display device 50. The transport device 30 is used for transporting the sample liquid (e.g. the blood sample to be tested) reacted with the reagent to the optical detection device 20. The transport device 30 typically comprises transport lines and control valves through which the sample fluid is transported into the optical detection device 20.
The optical detection device 20 is used for irradiating the sample liquid flowing through the detection area thereof with light, collecting various optical signals (such as scattered light signals and/or fluorescent signals) generated by the cells due to the light irradiation, and converting the optical signals and the corresponding electrical signals into corresponding electrical signals, wherein the information carried by the optical signals and the corresponding electrical signals corresponds to the characteristics of the cell particles, and can be used as cell particle characteristic data, the forward scattered light signals reflect the size information of the cells, the side scattered light signals reflect the complexity of the internal structure of the cells, and the fluorescent signals reflect the content of substances, such as DNA and RNA, which can be stained by fluorescent dyes in the cells. In the schematic illustration shown in fig. 1, optical inspection apparatus 20 may include a light source 1025, a flow cell 1022 as an inspection area, a forward scattered light signal collection device 1023 disposed on the optical axis, a side scattered light signal collection device 1026 disposed to the side of the optical axis, and a fluorescent signal collection device 1027. The blood sample is divided according to the need, the sample liquid of the first white blood cell measuring system and the second white blood cell measuring system after reacting with different reagents passes through a flowing chamber 1022 for providing a detection area under the wrapping of sheath liquid, the light beam emitted by a light source 1025 irradiates the detection area 1021, each cell particle in the sample liquid emits scattered light after being irradiated by the light beam, a light collecting device collects the scattered light, for example, when the sample liquid of the DIFF channel passes through the detection region 1021, the forward scattered light signal collection means 1023, the side scattered light signal collection means 1026 and the fluorescence signal collection means 1027 collect forward scattered light, side scattered light and fluorescence signals respectively, forward scattered light signal collection apparatus 1023 and side scattered light signal collection apparatus 1026 collect forward scattered light and side scattered light signals, respectively, as the BASO channel sample fluid passes through detection region 1021. The collected and shaped light is irradiated to the photoelectric sensor, and the photoelectric sensor converts the light signal into a corresponding electrical signal and outputs the electrical signal to the data processing device 40. The data processing device 40 performs analysis processing on the received particle characteristic data to realize analysis of the blood sample to be tested.
Referring to fig. 2, which is a schematic structural diagram of a conveying apparatus in an embodiment, the conveying apparatus 30 includes a sheath fluid injector 31, a sample injector 32, a sheath fluid conveying pipeline 33, and a detection device 34. The sheath fluid injector 31 and the sample injector 32 push the fluid to flow, the fluid to be detected is injected into the detection device 34, the particle or signal detection is performed, and the injector is pushed by a motor. The detecting device 34 is a detecting area 1021 of the optical detecting device 20.
Referring to fig. 3, which is a schematic diagram illustrating the detection of a sample flowing through the detection device in an embodiment, when the sample enters the flow chamber under the pushing of the injector, and the cell passes through the laser detection region, the light beam is scattered, the intensity of the light beam obtained by the photoelectric sensor is changed, and a corresponding electrical signal is generated according to the intensity of the light beam.
Referring to fig. 4, which is a schematic diagram of voltage signals generated by cells in an embodiment, the photo sensor converts the optical signals into corresponding voltage signals, wherein one pulse width signal corresponds to one cell. After the voltage signal is denoised by hardware, pulse amplitude is counted by software digital signal filtering processing, software pulse identification processing and software, the distribution proportion of particles with different sizes in the detection process is obtained, and the output of the detection result is realized.
In the prior art, because the rotating speed of a motor for pushing the injector has an acceleration process from electrifying to rotating at a fixed rotating speed, the liquid pushing speed of the injector is derived from the speed of the motor of the injector, and when the counting of the instrument is started, the acceleration and the deceleration can be carried out for a long time in order to ensure that the motor moves stably and reaches a certain speed. The cell speed in the sample flowing through the flow chamber at the initial stage is changed from slow to fast, the pulse width of the formed pulse signal is also a variable value, the obtained detection result is incorrect, and further the sample data at the initial stage of detection is not required to be sampled or deleted, so that the detection time is increased, and the sample is wasted.
In the embodiment of the invention, the pulse width W is adjustednThe compensation coefficient for compensation is related to the rotating speed of the motor for driving the blood sample to flow when the cell analyzer detects, so that a correct detection result can be output according to detection data when the rotating speed of the motor is not a fixed value, the detection speed of a project is further improved, the detection quantity of samples in unit time is increased, and the product performance of the cell analyzer is improved.
The first embodiment is as follows:
referring to fig. 5, a method for analyzing cells in the cell analyzer according to an embodiment of the present invention includes:
The method comprises the steps of obtaining electric pulse signal data according to a voltage signal output when a cell analyzer detects a blood sample, and converting a received optical signal into a voltage signal by a photoelectric sensor when cells in the sample flow through a flow chamber of the cell analyzer. The cell is one that flows through the flow cell, so the voltage signal is a pulse signal from which electrical pulse signal data is obtained, so the pulse signal data is related to the cells in the blood sample detected by the cell analyzer.
Sequentially acquiring the pulse width W of each pulse signal in the electric pulse signal data according to the detected time sequencen. Wherein, the time sequence of detection is the sequence of the cells passing through the flow chamber, and the sequence of the formed pulse signals corresponds to the sequence of the cells passing through the flow chamber.
And step 130, compensating the pulse width.
For the pulse width W of each obtained pulse signalnAnd compensating to obtain the compensated pulse width W. Wherein the pulse width W and the pulse width W are compensatednIn direct proportion, the compensation factor is related to the rotation speed of the motor driving the blood sample to flow when the cell analyzer detects the blood sample. In one embodiment, the formula for obtaining the compensated pulse width W includes:
when 0 is present<t<At T, W = (W)n*fmax)/{fmin+[(fmax-fmin)/e(3-T/t) ]}；
Wherein T is the time for detecting the blood sample by the cell analyzer, T is the time for accelerating the motor from rest to a preset rotating speed, W is the compensation pulse width, and W isnFor the pulse width value of the detected pulse signal, fmaxFor a predetermined rotational speed of the motor, fminThe starting rotation speed when the motor is accelerated. f. ofminThe starting speed for motor acceleration, the speed at which the motor torque is maximum, is related to the motor torque frequency curve, which is the motor constant. f. ofmaxThe maximum value of the motor acceleration and the final speed of the injector operation.
When the motor accelerates and decelerates, the pulse width becomes too large, and the pulse width W needs to be compensated, so that the pulse signal with too long pulse width caused by the slowing of the speed is prevented from being filtered out during the later data processing. When the motor speed is stable, the pulse width of the electric pulse signal formed by normal cells is between 2us and 15us, which is us-level, and the motor speed is s. The pulse width of the particles when the system is stable is as follows:
W=（10^6）*（fmax K）-1；
wherein K is the mechanical transformation coefficient of the injector, which is a constant.
And step 140, counting.
And counting the pulse signals of which the compensation pulse width W in the electric pulse signals accords with a preset value so as to obtain a counting result. And filtering the pulse signals which do not meet the requirements according to the preset requirements. In one embodiment, the preset value is an interval threshold set between 2us and 15 us.
And 150, acquiring a detection result.
And obtaining and outputting the detection result of the cell analyzer according to the counting result. Compensating the counting result, wherein the compensation formula comprises:
when 0 is present<t<At T, Num = (N)n*fmax)/{fmin+[(fmax-fmin)/e(3-T/t) ]}；
Wherein T is the time for detecting the blood sample by the cell analyzer, T is the time for accelerating the motor from rest to a preset rotating speed, Num is a compensated counting result, and N isnTotal number of cells detected for current minimum time period, fmaxFor a predetermined rotational speed of the motor, fminThe starting rotation speed when the motor is accelerated. And outputting Num as a detection result. In one embodiment, Nn is the number of cells detected in the current time unit, and since the system steady state cellular analyzer pulse signal width ranges from 2us to 40us, Nn may be the total number of cells in 1 ms.
In one embodiment, the cell analysis method further comprises:
when T is<At time t, stopping pulse width W of each pulse signalnCompensating, stopping compensating the counting result, and taking the counting result as a cell scoreAnd (5) detecting results of the analyzer.
The embodiment of the application discloses a cell analysis method of a cell analyzer, which comprises the steps of firstly obtaining electric pulse signal data according to voltage signals output when the cell analyzer detects a blood sample, and sequentially obtaining the pulse width W of each pulse signal in the electric pulse signal data according to the detection time sequencen. Then the pulse width W of each pulse signal is obtainednAnd compensating, and counting the pulse signals of which the compensated pulse width W accords with a preset value. And then obtaining the detection result of the cell analyzer according to the counting result. Due to the pulse width WnThe compensation coefficient for compensation is related to the rotating speed of the motor for driving the blood sample to flow when the cell analyzer detects, so that a correct detection result can be output according to detection data when the rotating speed of the motor is not a fixed value, the detection speed of a project is further improved, the detection quantity of samples in unit time is increased, and the product performance of the cell analyzer is improved.
Example two:
referring to fig. 6, the cell analysis apparatus in another embodiment includes a data acquisition module 100, a pulse width acquisition module 200, a pulse width compensation module 300, and a result output module 400. The data acquisition module 100 is configured to acquire electrical pulse signal data according to a voltage signal of a blood sample detected by the cell analyzer. The electrical pulse signal data is related to cells in the blood sample detected by the cell analyzer. The pulse width obtaining module 200 is used for sequentially obtaining the pulse width W of each pulse signal in the electrical pulse signal data according to the detected time sequencen. The pulse width compensation module 300 is used for obtaining the pulse width W of each pulse signalnAnd compensating to obtain the compensated pulse width W. Wherein the pulse width W and the pulse width W are compensatednIn direct proportion, the compensation factor is related to the rotation speed of the motor driving the blood sample to flow when the cell analyzer detects the blood sample. The result output module 400 is configured to count the pulse signals whose compensated pulse width W in the electrical pulse signals meets a preset value, so as to obtain a counting result. And the result output module is also used for acquiring and outputting the detection result of the cell analyzer according to the counting result.
In one embodiment, the formula for obtaining the compensated pulse width W includes:
when 0 is present<t<At T, W = (W)n*fmax)/{fmin+[(fmax-fmin)/e(3-T/t) ]}；
Wherein T is the time for detecting the blood sample by the cell analyzer, T is the time for accelerating the motor from rest to a preset rotating speed, W is the compensation pulse width, and W isnFor the pulse width value of the detected pulse signal, fmaxFor a predetermined rotational speed of the motor, fminThe starting rotation speed when the motor is accelerated.
The result output module 400 is further configured to obtain a detection result of the cell analyzer according to the counting result, and includes:
compensating the counting result, wherein the compensation formula comprises:
when 0 is present<t<At T, Num = (N)n*fmax)/{fmin+[(fmax-fmin)/e(3-T/t) ]}；
Wherein T is the time for detecting the blood sample by the cell analyzer, T is the time for accelerating the motor from rest to a preset rotating speed, Num is a compensated counting result, and N isnTotal number of cells detected for current minimum time period, fmaxFor a predetermined rotational speed of the motor, fminThe starting rotation speed when the motor is accelerated.
In one embodiment, the pulse width compensation module 300 is further configured to determine the time T<At time t, stopping pulse width W of each pulse signalnAnd compensating, stopping compensating the counting result by the result output module 400, and taking the counting result as the detection result of the cell analyzer.
In an embodiment of the present application, a cell analyzer including the cell analysis device in the embodiment is also disclosed.
Referring to fig. 7 and 8, graphs of the number of leukocytes obtained by the cell analyzer are shown, in which fig. 7 is a graph without pulse width compensation, and fig. 8 is a graph after pulse width compensation. As can be seen from fig. 7 and 8, there is a difference between the curves before and after compensation at the front end of the data (i.e., at the early stage of the start of detection by the cell analyzer), and the initial stage of the detection data obtained after compensation is a steady state.
Those skilled in the art will appreciate that all or part of the functions of the various methods in the above embodiments may be implemented by hardware, or may be implemented by computer programs. When all or part of the functions of the above embodiments are implemented by a computer program, the program may be stored in a computer-readable storage medium, and the storage medium may include: a read only memory, a random access memory, a magnetic disk, an optical disk, a hard disk, etc., and the program is executed by a computer to realize the above functions. For example, the program may be stored in a memory of the device, and when the program in the memory is executed by the processor, all or part of the functions described above may be implemented. In addition, when all or part of the functions in the above embodiments are implemented by a computer program, the program may be stored in a storage medium such as a server, another computer, a magnetic disk, an optical disk, a flash disk, or a removable hard disk, and may be downloaded or copied to a memory of a local device, or may be version-updated in a system of the local device, and when the program in the memory is executed by a processor, all or part of the functions in the above embodiments may be implemented.
The present invention has been described in terms of specific examples, which are provided to aid understanding of the invention and are not intended to be limiting. For a person skilled in the art to which the invention pertains, several simple deductions, modifications or substitutions may be made according to the idea of the invention.
Claims (8)
1. A cell analysis method of a cell analyzer, comprising:
acquiring electric pulse signal data according to a voltage signal output when the cell analyzer detects the blood sample; the electrical pulse signal data is related to cells in the blood sample detected by the cell analyzer;
sequentially acquiring the pulse width W of each pulse signal in the electric pulse signal data according to the detected time sequencen；
For the pulse width W of each obtained pulse signalnCompensating to obtain compensated pulse width W; wherein the pulse width W and the pulse width W are compensatednIn a direct proportional relationship, a compensation factor is related to the rotation speed of a motor driving the blood sample to flow when the cell analyzer detects the blood sample;
counting the pulse signals of which the compensation pulse width W accords with a preset value in the electric pulse signals to obtain a counting result;
obtaining a detection result of the cell analyzer according to the counting result and outputting the detection result;
the obtaining formula of the compensation pulse width W comprises the following steps:
when 0 is present<t<At T, W = (W)n*fmax)/{fmin+[(fmax-fmin)/e(3-T/t)]}；
Wherein T is the time for the cell analyzer to detect the blood sample, T is the time for the motor to accelerate from rest to a preset rotation speed, W is the compensation pulse widthnFor the pulse width value of the detected pulse signal, fmaxFor a predetermined rotational speed, f, of the motorminThe starting point rotating speed when the motor is accelerated.
2. The method of claim 1, wherein said obtaining a test result of said cell analyzer based on said counting result comprises:
compensating the counting result, wherein the compensation formula comprises:
when 0 is present<t<At T, Num = (N)n*fmax)/{fmin+[(fmax-fmin)/e(3-T/t)]}；
Wherein T is the time for detecting the blood sample by the cell analyzer, T is the time for accelerating the motor from rest to a preset rotating speed, Num is a compensated counting result, and N isnTotal number of cells detected for current minimum time period, fmaxFor a predetermined rotational speed, f, of the motorminThe starting point rotating speed when the motor is accelerated.
3. The method of claim 2, further comprising:
when T is<t, stopping pulse width W of each obtained pulse signalnCompensation is performed.
4. The method of claim 2, further comprising:
and when T < T, stopping compensating the counting result, and taking the counting result as the detection result of the cell analyzer.
5. A cell analysis device of a cell analyzer, comprising:
the data acquisition module is used for detecting a voltage signal of the blood sample according to the cell analyzer and acquiring electric pulse signal data; the electrical pulse signal data is related to cells in the blood sample detected by the cell analyzer;
a pulse width acquisition module for sequentially acquiring the pulse width W of each pulse signal in the electric pulse signal data according to the detected time sequencen；
A pulse width compensation module for obtaining the pulse width W of each pulse signalnCompensating to obtain compensated pulse width W; wherein the pulse width W and the pulse width W are compensatednIn a direct proportional relationship, a compensation factor is related to the rotation speed of a motor driving the blood sample to flow when the cell analyzer detects the blood sample;
the result output module is used for counting the pulse signals of which the compensation pulse width W accords with a preset value in the electric pulse signals so as to obtain counting results; the result output module is also used for acquiring the detection result of the cell analyzer according to the counting result and outputting the detection result;
the obtaining formula of the compensation pulse width W comprises the following steps:
when 0 is present<t<At T, W = (W)n*fmax)/{fmin+[(fmax-fmin)/e(3-T/t)]}；
Wherein T is the time for the cell analyzer to detect the blood sample, and T is the electricityTime from rest to acceleration to a predetermined speed, W being the compensating pulse width, WnFor the pulse width value of the detected pulse signal, fmaxFor a predetermined rotational speed, f, of the motorminThe starting point rotating speed when the motor is accelerated is set;
the result output module is further configured to obtain a detection result of the cell analyzer according to the counting result, and includes:
compensating the counting result, wherein the compensation formula comprises:
when 0 is present<t<At T, Num = (N)n*fmax)/{fmin+[(fmax-fmin)/e(3-T/t)]}；
Wherein T is the time for detecting the blood sample by the cell analyzer, T is the time for accelerating the motor from rest to a preset rotating speed, Num is a compensated counting result, and N isnTotal number of cells detected for current minimum time period, fmaxFor a predetermined rotational speed, f, of the motorminThe starting point rotating speed when the motor is accelerated.
6. The apparatus of claim 5, wherein the pulse width compensation module is further configured to compensate for the pulse width difference when T is greater than T<t, stopping pulse width W of each obtained pulse signalnPerforming compensation;
and the result output module is also used for stopping compensating the counting result when T < T and taking the counting result as the detection result of the cell analyzer.
7. A cell analyzer comprising the cell analysis device according to any one of claims 5 or 6.
8. A computer-readable storage medium, characterized in that the medium has stored thereon a program which is executable by a processor to implement the method according to any one of claims 1 to 4.
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| CN202110118229.5A CN112798769B (en) | 2021-01-28 | 2021-01-28 | Cell analysis method and device of cell analyzer and cell analyzer |
| PCT/CN2021/092456 WO2022160500A1 (en) | 2021-01-28 | 2021-05-08 | Cell analysis method and apparatus of cell analyzer, and cell analyzer |
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| CN202110118229.5A CN112798769B (en) | 2021-01-28 | 2021-01-28 | Cell analysis method and device of cell analyzer and cell analyzer |
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| CN106662572B (en) * | 2015-02-12 | 2019-07-05 | 深圳迈瑞生物医疗电子股份有限公司 | Cytoanalyze, method for classifying particles and device |
| CN106383082B (en) * | 2015-10-14 | 2018-10-19 | 北京信息科技大学 | A kind of optical path adjustment device and method of the flow cytometer without fluid path situation |
| CN107988042B (en) * | 2017-11-27 | 2021-03-09 | 长春理工大学 | Circulating tumor cell separation device and detection method thereof |
| CN108441474B (en) * | 2018-03-23 | 2021-10-08 | 天晴干细胞股份有限公司 | Method for separating and purifying hematopoietic stem cells from umbilical cord blood and placenta |
| CN109580459A (en) * | 2019-01-08 | 2019-04-05 | 广西师范大学 | A kind of Flow cytometry data acquisition system |
| CN110031386B (en) * | 2019-05-16 | 2023-12-26 | 重庆博奥新景医学科技有限公司 | Flow cytometer liquid path system and detection method thereof |
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