Blood cell analyzer and detection method for hole blockage of flow chamber

Abstract

The invention discloses a hematology analyzer and a detection method for hole blockage of a flow chamber, in the hematology analyzer provided by the invention, in the process that sample liquid enters the flow chamber for sample detection, a control unit can also obtain signal parameters based on optical signals of the sample liquid flowing through the flow chamber; whether the flow chamber is blocked or not is judged, the safety of the flow chamber is improved, and the detection efficiency of an optical detection system on sample liquid is improved. Meanwhile, in the process of detecting the sample liquid, whether the flow chamber has the hole blocking problem or not can be judged, the step of judging the hole blocking of the flow chamber does not need to be additionally set, the operation efficiency of the hematology analyzer is improved, and the use experience of a user on the hematology analyzer is improved.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of sample analysis, in particular to a blood cell analyzer and a method for detecting a flow chamber blockage. BACKGROUND

[0002] A blood cell analyzer is an instrument for counting and classifying blood cells of a human body, which is widely used in clinics and laboratories. The blood cell analyzer generally classifies and counts blood cells in a blood sample by using an electrical impedance method or an optical detection method. The general principle of the optical detection method is as follows: a certain amount of diluted blood sample is reacted with a reagent to obtain a sample liquid, and the sample liquid is transported to a flow chamber. The flow chamber provides an optical detection area, and the sample liquid forms a stable sheath flow under the wrapping of sheath liquid. The sheath flow enables the cells in the sample liquid to flow through the optical detection area one by one for detection. A light beam generated by an optical system irradiates on the optical detection area. When a particle flows through the optical detection area, the light beam irradiates on the particle to cause light scattering. A detector can collect the scattered light, and the optical system can convert the scattered light into an electrical pulse output. By analyzing the information contained in the electrical pulse, the detection result of the blood sample can be obtained.

[0003] However, when the blood sample liquid passes through the flow chamber, if substances other than cells are mixed into the blood sample, the optical detection area of the flow chamber may be reduced, resulting in a flow chamber blockage problem, and further affecting the detection result of the blood sample. SUMMARY

[0004] To solve the above technical problems, the present application provides a sample analyzer. The sample analyzer comprises an optical detection system,

[0005] The optical detection system comprises a sample liquid supply assembly, a flow chamber, a laser, a photoelectric detection assembly, and an optical information processing assembly,

[0006] The sample liquid supply assembly is connected with the flow chamber and is used for supplying the flow chamber with sample liquid. The laser is arranged at a position spaced apart from the flow chamber. The photoelectric detection assembly is arranged on a side of the flow chamber away from the laser and is arranged correspondingly to the laser.

[0007] During the process in which the sample liquid supply assembly transports sample liquid to the flow chamber, a light beam generated by the laser enters the photoelectric detection assembly after passing through the sample liquid in the flow chamber. The photoelectric detection assembly receives an optical signal carrying information of the sample liquid and transmits the optical signal to the optical information processing assembly. The optical information processing assembly processes the optical signal to obtain a pulse digital signal of the sample liquid flowing through the flow chamber.

[0008] The blood cell analyzer further comprises a control unit connected with the optical information processing assembly, configured to receive the pulse digital signal and process the pulse digital signal to obtain a signal parameter of the sample liquid flowing through the flow chamber, and determine whether the flow chamber has a hole blocking problem based on the signal parameter.

[0009] The signal parameter comprises particle flow jump degree of the sample liquid, and the control unit is configured to determine that the flow chamber has a hole blocking problem and send an alarm signal in response to the particle flow jump degree being greater than a preset particle flow jump degree;

[0010] The signal parameter comprises particle flow inclination degree of the sample liquid, and the control unit is configured to determine that the flow chamber has a hole blocking problem and send an alarm signal in response to the particle flow inclination degree being greater than a preset particle flow inclination degree;

[0011] The signal parameter comprises voltage characteristic value of the sample liquid, and the control unit is configured to determine that the flow chamber has a hole blocking problem and send an alarm signal in response to the voltage characteristic value being greater than a preset voltage characteristic value;

[0012] The signal parameter comprises pulse width characteristic of the sample liquid, and the control unit is configured to determine that the flow chamber has a hole blocking problem and send an alarm signal in response to the pulse width characteristic being greater than a preset pulse width characteristic.

[0013] The optical information processing assembly comprises:

[0014] A beam splitter configured to separate an effective optical signal in the optical signal;

[0015] A photoelectric converter configured to receive the effective optical signal separated by the beam splitter and convert the effective optical signal into an analog signal;

[0016] An A / D converter configured to convert the analog signal into the pulse digital signal;

[0017] The control unit is configured to receive the pulse digital signal transmitted by the A / D converter and process the pulse digital signal to obtain the signal parameter of the sample liquid flowing through the flow chamber.

[0018] The control unit is further configured to:

[0019] Obtain a first pulse digital signal of the sample liquid flowing through the flow chamber, and obtain a first analog baseline signal of the sample liquid flowing through the flow chamber and a first median value of the first analog baseline signal based on the first pulse digital signal;

[0020] acquire a second pulse digital signal after the sample liquid flows through the flow chamber, and acquire a second analog baseline signal based on the second pulse digital signal, and a second median value of the second analog baseline signal;

[0021] acquire the voltage characteristic value of the sample liquid based on the first median value and the second median value.

[0022] The control unit is further configured to,

[0023] acquire a plurality of pulse width values in succession during the process of the sample liquid flowing through the flow chamber based on the pulse digital signal, and acquire an average value and a standard value of the plurality of pulse width values;

[0024] acquire the pulse width characteristic of the sample liquid based on the average value and the standard value of the plurality of pulse width values.

[0025] The control unit is further configured to,

[0026] acquire a plurality of time points and a plurality of particle numbers in succession during the process of the sample liquid flowing through the flow chamber based on the pulse digital signal, wherein the particle numbers correspond to the time points one by one;

[0027] acquire a correlation coefficient of the time points and the particle numbers corresponding to the time points based on the plurality of time points and the plurality of particle numbers corresponding to the time points, and acquire a slope of a fitting straight line formed by the plurality of time points and the plurality of particle numbers;

[0028] acquire the particle flow inclination of the sample liquid based on the correlation coefficient and the slope.

[0029] The control unit is further configured to,

[0030] acquire a plurality of particle numbers in a continuous time period during the process of the sample liquid flowing through the flow chamber based on the pulse digital signal;

[0031] acquire an average value of the plurality of particle numbers, a maximum particle number in the plurality of particle numbers, and a minimum particle number in the plurality of particle numbers;

[0032] acquire the particle flow jump degree of the sample liquid based on the average value, the maximum particle number, and the minimum particle number.

[0033] The optical information processing assembly comprises a beam splitter, a photoelectric converter, a baseline amplifier, and an A / D converter,

[0034] The beamsplitter separates the forward scattering light in the optical signal; the photoelectric converter receives the forward scattering light and converts the forward scattering light into an analog signal; the baseline amplifier receives the analog signal and amplifies the baseline voltage of the analog signal; the A / D converter converts the processed analog signal into a pulse digital signal, and the control unit receives the pulse digital signal and obtains the voltage characteristic value of the sample liquid based on the pulse digital signal.

[0035] The optical information processing assembly includes a beamsplitter, a photoelectric converter, a pulse amplifier, and an A / D converter.

[0036] The beamsplitter separates the effective optical signal in the optical signal; the photoelectric converter receives the effective optical signal and converts the effective optical signal into an analog signal; the pulse amplifier receives the analog signal and amplifies the pulse signal of the analog signal; the A / D converter converts the processed analog signal into a pulse digital signal, and the control unit receives the pulse digital signal and obtains the pulse width characteristic of the sample liquid based on the pulse digital signal.

[0037] The control unit is further configured to obtain a particle flow pattern of the particle number of the sample liquid flowing through the flow chamber changing with time based on the pulse digital signal, and obtain the particle flow jump degree and the particle flow inclination degree of the sample liquid based on the particle flow pattern.

[0038] To solve the above technical problems, the application also provides a detection method for a flow chamber hole blockage, applied to the blood cell analyzer described above, and the detection method comprises the following steps:

[0039] Obtaining an optical signal generated during the detection process of the sample liquid flowing through the flow chamber;

[0040] Obtaining a signal parameter of the sample liquid flowing through the flow chamber based on the optical signal;

[0041] In response to the signal parameter not belonging to the standard range, it is determined that the flow chamber has a hole blockage problem, and an alarm is issued.

[0042] The step of obtaining a signal parameter of the sample liquid flowing through the flow chamber based on the optical signal, and in response to the signal parameter not belonging to the standard range, determining that the flow chamber has a hole blockage problem and issuing an alarm, comprises the following steps:

[0043] Obtaining a particle flow jump degree of the sample liquid flowing through the flow chamber based on the optical signal, and in response to the particle flow jump degree being greater than a preset particle flow jump degree, determining that the flow chamber has a hole blockage problem and issuing an alarm.

[0044] and / or, based on the optical signal, obtaining a particle flow inclination when the sample liquid flows through the flow chamber; in response to the particle flow inclination being greater than a preset particle flow inclination, determining that the flow chamber has a hole blocking problem, and issuing an alarm;

[0045] and / or, based on the optical signal, obtaining a voltage characteristic value when the sample liquid flows through the flow chamber; in response to the voltage characteristic value being greater than a preset voltage characteristic value, determining that the flow chamber has a hole blocking problem, and issuing an alarm;

[0046] and / or, based on the optical signal, obtaining a pulse width characteristic when the sample liquid flows through the flow chamber; in response to the pulse width characteristic being greater than a preset pulse width characteristic, determining that the flow chamber has a hole blocking problem, and issuing an alarm.

[0047] The blood cell analyzer provided by the application has the following beneficial effects: different from the prior art, in the process that the sample liquid supply assembly delivers sample liquid to the flow chamber, the light beam generated by the laser passes through the sample liquid and enters the photoelectric detection assembly, the photoelectric detection assembly receives the optical signal of the sample liquid flowing through the flow chamber, and the optical signal is transmitted to the optical information processing assembly. The optical information processing assembly processes the optical signal to obtain a pulse digital signal of the sample liquid flowing through the flow chamber. The control unit is connected with the optical information processing assembly, is used for receiving the pulse digital signal, processing the pulse digital signal to obtain a signal parameter of the sample liquid flowing through the flow chamber, and judging whether the flow chamber has a hole blocking problem based on the signal parameter. In the process that the sample liquid enters the flow chamber for sample detection, the control unit can also obtain the signal parameter based on the optical signal of the sample liquid flowing through the flow chamber to judge whether the flow chamber has a hole blocking problem, improve the safety of the flow chamber, and improve the detection efficiency of the optical detection system on the sample liquid. At the same time, the judgment of whether the flow chamber has a hole blocking problem can be completed in the process that the sample liquid is detected, without the need to additionally set a step of judging the hole blocking of the flow chamber, thereby improving the running efficiency of the blood cell analyzer and improving the user experience of the blood cell analyzer. BRIEF DESCRIPTION OF DRAWINGS

[0048] In order to more clearly illustrate the technical solutions in the embodiments of the application, the following will briefly introduce the drawings needed to be used in the embodiment description. Obviously, the drawings in the following description are only some embodiments of the application, and other drawings can be obtained by those skilled in the art without any creative effort on the basis of these drawings.

[0049] Wherein:

[0050] Figure 1 is a structural schematic diagram of an embodiment of the optical detection device of the application;

[0051] Figure 2 is a structural schematic diagram of an embodiment of the optical information processing assembly of the present application;

[0052] Figure 3 is a structural schematic diagram of an embodiment of the baseline voltage curve of the sample liquid flowing through the flow chamber of the present application;

[0053] Figure 4 is a structural schematic diagram of an embodiment of the pulse width distribution of the sample liquid flowing through the flow chamber of the present application;

[0054] Figure 5 is a structural schematic diagram of a first embodiment of the particle flow of the sample liquid flowing through the flow chamber of the present application;

[0055] Figure 6 is a structural schematic diagram of a second embodiment of the particle flow of the sample liquid flowing through the flow chamber of the present application;

[0056] Figure 7 is a flow schematic diagram of a first embodiment of the detection method of the present application;

[0057] Figure 8 is a flow schematic diagram of a second embodiment of the detection method of the present application;

[0058] Figure 9 is a flow schematic diagram of a third embodiment of the detection method of the present application;

[0059] Figure 10 is a flow schematic diagram of a fourth embodiment of the detection method of the present application;

[0060] Figure 11 is a flow schematic diagram of a fifth embodiment of the detection method of the present application.

[0061] Reference signs: optical detection system 1; sample liquid supply assembly 11; flow chamber 12; laser 13; photoelectric detection assembly 14; optical information processing assembly 15; beam splitter 151; photoelectric converter 152; A / D converter 153; baseline amplifier 154; pulse amplifier 155. DETAILED DESCRIPTION

[0062] The scheme of the embodiments of the present application will be described in detail below in conjunction with the drawings of the specification.

[0063] In the following description, specific details are set forth in order to provide a thorough understanding of the present application. The present application may, however, be practiced without these details. In other instances, well-known methods, structures and techniques have not been described in detail in order to avoid obscuring the present application.

[0064] Reference to an "embodiment" in this application means that a particular feature, structure, or characteristic described in connection with the embodiment can be included in at least one embodiment of the application. The appearances of the phrase in various places in the specification are not necessarily all referring to the same embodiment, nor are they necessarily mutually exclusive of one another. As will be apparent to those of ordinary skill in the art, embodiments described herein can be combined with other embodiments.

[0065] The term "and / or" in this application is only a description of the association relationship of the associated objects, which means that there can be three relationships, for example, A and / or B can represent the existence of A alone, the existence of A and B at the same time, and the existence of B alone. In addition, the character " / " in this application generally represents that the front and rear associated objects are in an "or" relationship. In addition, "multiple" in this application means two or more than two. In addition, the term "at least one" in this application means any one of multiple or any combination of at least two of multiple, for example, including at least one of A, B and C can mean including any one or more elements selected from the set consisting of A, B and C. In addition, the terms "first", "second", "third" in this application are only for description purposes, and cannot be understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features.

[0066] In the existing blood cell analyzer, if there is a hole blocking problem in the flow chamber during the optical detection of the sample liquid, the flow rate and flow volume of the sample liquid flowing through the flow chamber will be affected, and then the detection result of the sample liquid by the blood cell analyzer will be affected. Therefore, it is necessary to detect and judge whether there is a hole blocking problem in the flow chamber to ensure the detection efficiency of the sample liquid. The application provides a blood cell analyzer which can judge whether there is a hole blocking problem in the flow chamber during the optical detection of the sample liquid, and improve the detection efficiency of the sample liquid by the blood cell analyzer.

[0067] The blood cell analyzer provided by the embodiments of the application includes an optical detection system, as shown in Figure 1 Figure 1 is a structural schematic diagram of an embodiment of the optical detection system of the application. The optical detection system 1 includes a sample liquid supply assembly 11, a flow chamber 12, a laser 13, a photoelectric detection assembly 14 and an optical information processing assembly 15.

[0068] The sample liquid supply assembly 11 is connected with the flow chamber 12, and is used to supply sample liquid for the flow chamber 12. The laser 13 is arranged in a spaced manner with the flow chamber 12. The photoelectric detection assembly 14 is arranged on the side of the flow chamber 12 away from the laser 13, and is arranged in a position corresponding to the position of the laser 13, so that the photoelectric detection assembly 14 can receive the light beam emitted by the laser 13 and passing through the flow chamber 12.

[0069] ​The sample liquid supply assembly 11 can include various optical channel reaction cells, such as a WNR (white blood cell count, classification count of basophilic granulocytes and nucleated red blood cells) channel reaction cell, a DIFF (five classification examination of white blood cells) channel reaction cell, a RET (reticulocyte detection) channel reaction cell, and a PLTF channel (low value platelet channel) reaction cell, etc.

[0070] During the process of the sample liquid supply assembly 11 delivering the sample liquid to the flow chamber 12, the sample liquid can form a stable sheath flow under the wrapping of the sheath liquid, and then the cells in the sample liquid can flow through the optical detection area of the flow chamber 12 in turn. Meanwhile, the light beam generated by the laser 13 irradiates the sample liquid flowing through the optical detection area of the flow chamber 12, and then enters the photoelectric detection assembly 14. The photoelectric detection assembly 14 receives the optical signal carrying the information of the sample liquid flowing through the optical detection area, and transmits the optical signal to the optical information processing assembly 15. The optical information processing assembly 15 processes the optical signal to obtain the pulse digital signal of the sample liquid flowing through the flow chamber.

[0071] Further, the blood cell analyzer further includes a control module (not shown in the figure), which is connected with the optical information processing assembly 15, used to receive the pulse digital signal obtained after the processing of the optical information processing assembly 15, and process the pulse digital signal to obtain the signal parameter of the sample liquid flowing through the flow chamber, and judge whether there is a clogging problem of the flow chamber 12 based on the obtained signal parameter.

[0072] In an embodiment, if the control unit judges that there is no clogging problem of the flow chamber 12, the blood cell analyzer can obtain the detection result of the sample liquid based on the optical signal obtained by the photoelectric detection assembly 14; if the control unit judges that there is a clogging problem of the flow chamber 12, the control unit can further send an alarm signal to remind the user to maintain the flow chamber 12, or the control unit can control the blood cell analyzer to call the clogging solving sequence to solve the clogging problem of the flow chamber 12, and recheck the sample liquid after the clogging problem of the flow chamber 12 is solved to obtain the detection result of the sample liquid.

[0073] In summary, in the blood cell analyzer provided in this application embodiment, during the sample fluid testing process, the control unit can process the optical signal of the sample fluid flowing through the flow chamber 12 collected by the photoelectric detection component 14 to obtain the signal parameters of the sample fluid flowing through the flow chamber 12, and determine whether there is a blockage problem in the flow chamber 12. The determination of whether the flow chamber 12 is blocked can be completed during the sample testing process, and an alarm signal is generated in a timely manner when a blockage problem is found, improving the efficiency of the blood cell analyzer in sample testing. Furthermore, no additional judgment steps are required; the determination can be completed during the sample fluid testing process, further improving the operating efficiency of the blood cell analyzer and enhancing the user experience.

[0074] In one embodiment, the signal parameters may include at least one of the following: particle flow jump degree, particle flow tilt degree, voltage characteristic value, and pulse characteristic width.

[0075] Specifically, if the signal parameters include the particle flow jump degree of the sample liquid, the control unit is used to determine that there is a blockage problem in the flow chamber and issue an alarm signal in response to the particle flow jump degree of the sample liquid being greater than a preset particle flow jump degree.

[0076] If the signal parameters include the particle flow inclination of the sample liquid, the control unit is used to determine that there is a blockage problem in the flow chamber 12 in response to the particle flow inclination of the sample liquid being greater than the preset particle flow inclination, and to issue an alarm signal.

[0077] If the signal parameters include the voltage characteristic value of the sample liquid, the control unit is used to determine that there is a blockage problem in the flow chamber 12 in response to the voltage characteristic value of the sample liquid being less than the preset voltage characteristic value, and to issue an alarm signal.

[0078] If the signal parameters include the pulse width characteristics of the sample liquid, the control unit is also used to determine that there is a blockage problem in the flow chamber 12 in response to the pulse width characteristics being greater than the preset pulse width characteristics, and to issue an alarm signal.

[0079] Optionally, such as Figure 2 As shown, Figure 2 This is a schematic diagram of the structure of an embodiment of the optical information processing component of this application. In one embodiment, the optical information processing component 15 includes a beam splitter 151, a photoelectric converter 152, and an A / D converter 153.

[0080] Beam splitter 151 is used to separate effective optical signals from optical signals, such as forward scattered light (hereinafter referred to as forward astigmatism), side scattered light (hereinafter referred to as side astigmatism), fluorescence signals, etc.; photoelectric converter 152 is used to receive the effective optical signals separated by beam splitter 151 and convert the effective optical signals into analog signals; A / D converter 153 is used to convert analog signals into pulse digital signals.

[0081] Wherein, after the optical signal is converted into pulse digital signal by the beam splitter 151, the photoelectric converter 152 and the A / D converter 153, the control unit is configured to receive the pulse digital signal transmitted by the A / D converter 153, and process the pulse digital signal to obtain the signal parameter of the sample liquid flowing through the flow chamber 12.

[0082] In an embodiment, the control unit is further configured to obtain a first pulse digital signal of the sample liquid flowing through the flow chamber 12, and obtain a first analog baseline signal of the sample liquid flowing through the flow chamber 12 based on the first pulse digital signal, and a first median value of the first analog baseline signal.

[0083] Further, the control unit is further configured to obtain a second pulse digital signal of the sample liquid flowing through the flow chamber 12, and obtain a second analog baseline signal of the flow chamber 12 without the sample liquid based on the second pulse digital signal, and a second median value of the second analog baseline signal.

[0084] And based on the first median value and the second median value, obtain the voltage characteristic value of the sample liquid.

[0085] Wherein, please refer to Figure 3 , Figure 3 is a structural schematic diagram of an embodiment of the baseline voltage curve of the sample liquid flowing through the flow chamber of the present application. Wherein, Figure 3 (a) is the baseline voltage curve obtained by processing the optical signal generated by the light beam through the sample liquid flowing in the flow chamber 12 without the problem of blocked holes in the flow chamber 12; Figure 3 (b) is the baseline voltage curve obtained by processing the optical signal generated by the light beam through the sample liquid in the flow chamber 12, wherein the abscissa of the baseline voltage curve is time, and the ordinate is voltage value. As can be seen, Figure 3 In (a), the stability of the voltage is higher, while in Figure 3 In (b), the voltage will appear mutation, and abnormal decline.

[0086] Wherein, the baseline voltage curve can represent the stability of the sample liquid in the flow chamber 12, when the flow chamber 12 has the problem of blocked holes, it will affect the stability of the sample liquid, the stability of the sample liquid will decrease, and then the baseline voltage will also decrease, which will present the curve change as Figure 3 (b) shows.

[0087] Further, the control unit can calculate the curve to accurately determine whether the flow chamber 12 has the problem of blocked holes. For example, Figure 3As shown, the baseline voltage curve includes two parts, the first part is PD1 (the first analog baseline signal described above) during the sample liquid flowing through the flow chamber 12, and the second part is PD2 (the second analog baseline signal described above) after the sample liquid flowing through the flow chamber 12 and the sample liquid is blocked, and PD1 is greater than PD2 because there is no sample liquid in the flow chamber 12 during PD2.

[0088] The control unit can obtain the voltage characteristic value of the sample liquid using PD1 and PD2.

[0089] Specifically, the control unit can obtain the baseline voltage curve of the sample liquid through the first pulse digital signal and the second pulse digital signal, calculate the median value PM1 (the first median value described above) of PD1, and calculate the median value PM2 (the second median value described above) of PD2. In actual application, because the voltage will fluctuate within a certain range, the median values PM1 and PM2 are used in the embodiment of the application to avoid the judgment error caused by voltage fluctuation and improve the accuracy of calculation of the control unit.

[0090] Further, the voltage characteristic value Pm of the sample liquid can be represented as:

[0091]

[0092] Wherein, D and E are preset adjustment parameters (D>1, E>1) to adjust the range of Pm to be mostly distributed within the range of 0-100.

[0093] In the case where there is no blockage problem in the flow chamber 12, Pm≈0; and in the case where the voltage jumps or drops as shown in (b), Pm>1. Figure 3

[0094] In actual application, the control unit can preset a preset voltage characteristic value Pth, and when the calculated voltage characteristic value Pm is greater than the preset voltage characteristic value Pth, it can be considered that there is a blockage problem in the flow chamber 12 at this time, and the cells in the sample liquid have not completely passed through the flow chamber 12, which will affect the detection result of the sample liquid, and the control unit will immediately issue an alarm signal; and when the calculated voltage characteristic value Pm of the control unit is greater than 1 but less than the preset voltage characteristic value Pth, it can be considered that there is a small degree of blockage problem in the flow chamber 12 at this time, but it does not affect the detection result of the sample liquid, and then the control unit can not issue an alarm signal, or the control unit can issue a warning signal to remind the user that the flow chamber 12 may have a blockage problem that affects the detection efficiency of the sample liquid in the future, and remind the user to pay attention.

[0095] ​Optionally, the preset voltage characteristic value Pth has a specific setting value of 0-100, such as 10, 20, 25, 30, 40, 60, 80, etc., preferably 40, which can be set by the user according to the demand, and the application does not limit the specific setting value of the preset voltage characteristic value Pth.

[0096] In another embodiment, the control unit is also used to obtain a plurality of pulse width values during the flow of the sample liquid through the flow chamber 12 based on the pulse digital signal, and obtain the average value and the standard value of the plurality of pulse width values, and obtain the pulse width characteristic of the sample liquid based on the average value and the standard value of the plurality of pulse width values.

[0097] Wherein, please refer to Figure 4 , Figure 4 is a structural schematic diagram of an embodiment of the pulse width distribution of the sample liquid flowing through the flow chamber of the application. Wherein, Figure 4 (a) is the optical signal generated by the light beam passing through the sample liquid flowing in the flow chamber 12, and the pulse width distribution diagram obtained by processing; Figure 4 (b) is the optical signal generated by the light beam passing through the sample liquid in the flow chamber 12, and the pulse width distribution diagram obtained by processing, wherein the abscissa of the pulse width distribution diagram is the pulse width, and the ordinate is the particle number. As can be seen, Figure 4 In (a), each pulse width corresponds to a larger number of particles, while in Figure 4 In (b), each pulse width corresponds to a smaller number of particles.

[0098] Wherein, the pulse width distribution diagram can represent the flow rate of the sample liquid in the flow chamber 12, such as Figure 4 As shown in (a), the flow rate of the sample liquid in the flow chamber 12 is faster, so the pulse width distribution diagram presents a smaller number of pulse width distribution values, and each pulse width corresponds to a larger number of particles. While in Figure 4 (b), due to the clogging problem of the flow chamber 12, the flow rate of the sample liquid in the flow chamber 12 is slowed down, and the pulse width distribution diagram presents a larger number of pulse width distribution values, the distribution is wider, and each pulse width corresponds to a smaller number of particles (it can be understood that the number of cells of the sample liquid passing in each fixed time period is smaller).

[0099] Further, the control unit can accurately determine whether the flow chamber 12 has a clogging problem by processing the pulse width distribution diagram of the sample liquid.

[0100] Specifically, the control unit can first obtain the pulse width distribution diagram of the sample liquid based on the pulse digital signal, obtain a plurality of pulse width values on the pulse width distribution diagram, and obtain the average value and the standard value of the plurality of pulse width values. and a standard value Wsd, the expression formula of the standard value Wsd is:

[0101]

[0102] Further, the control unit can calculate the pulse width feature Wd based on the average value of the plurality of pulse width values and the standard value Wsd, the calculation formula is:

[0103]

[0104] Wherein, F, G, H are preset adjustment parameters (F>1, G>1, H>1) to adjust the range of Wd to mostly distribute in the range of 0~100; W i is the i-th pulse width value.

[0105] In the case that there is no clogging problem in the flow chamber 12, max(Wsd-F, 0)=0, Therefore, Wd=0; while in the case that the pulse width distribution graph produces changes as shown in Figure 4 (b), Wd>1.

[0106] In practical application, the control unit can preset a preset pulse width feature Wth, when the calculated pulse width feature Wd is greater than the preset pulse width feature Wth, it can be considered that at this time the flow chamber 12 has a clogging problem, the sample liquid flow rate in the flow chamber 12 is abnormal, which will affect the detection result of the sample liquid, and the control unit will immediately issue an alarm signal; while the calculated pulse width feature Wd of the control unit is greater than 1 but less than the preset pulse width feature Wth, it can be considered that at this time the flow chamber 12 may have a small degree of clogging problem, but it does not affect the detection result of the sample liquid, then the control unit can not issue an alarm signal, or the control unit can issue a pre-warning signal to remind the user that the flow chamber 12 may subsequently have a clogging problem that affects the detection efficiency of the sample liquid, reminding the user to pay attention continuously.

[0107] Optionally, the specific setting value of the preset pulse width feature Wth is 0~100, for example, 10, 20, 25, 30, 40, 60, 80, etc., preferably 40, which can be set by the user according to the demand, and the application does not limit the specific setting value of the preset pulse width feature Wth.

[0108] In another embodiment, the control unit is further configured to obtain a plurality of time points and a plurality of particle numbers corresponding to the plurality of time points based on the pulsed digital signal, wherein the particle numbers correspond to the time points one by one; obtain a correlation coefficient of the time points and the particle numbers corresponding to the time points based on the plurality of time points and the plurality of particle numbers; obtain a slope of a fitting straight line formed by the plurality of time points and the plurality of particle numbers; and obtain a particle flow inclination of the sample liquid based on the correlation coefficient and the slope.

[0109] Wherein, please refer to Figure 5 , Figure 5 is a structural schematic diagram of a first embodiment of a particle flow of a sample liquid flowing through a flow chamber of the present application. Wherein, Figure 5 (a) is a particle flow pattern obtained by processing an optical signal generated by a light beam passing through the sample liquid flowing in the flow chamber 12 in the case where there is no hole blocking problem in the flow chamber 12; Figure 5 (b) is a particle flow pattern obtained by processing an optical signal generated by a light beam passing through the sample liquid flowing in the flow chamber 12 in the case where there is a hole blocking problem in the flow chamber 12, wherein the abscissa of the particle flow pattern is time and the ordinate is particle number. As can be seen, Figure 5 In (a), the particle flow curve is relatively stable, while in Figure 5 In (b), the particle flow gradually decreases over time.

[0110] Wherein, the particle flow pattern can represent the number of particles flowing through the flow chamber 12 in each fixed time period, that is, the flow rate of the sample liquid in the flow chamber 12, as shown in Figure 5 (a), the sample liquid flows uniformly in the flow chamber 12, so that the number of particles in the particle flow pattern tends to be stable and equal at each time. While in Figure 5 (b), due to the hole blocking problem in the flow chamber 12, the flow rate of the sample liquid in the flow chamber 12 is reduced, and thus the number of particles in the particle flow pattern gradually decreases over time.

[0111] Further, the control unit can accurately determine whether the flow chamber 12 has a hole blocking problem by processing the particle flow pattern of the sample liquid.

[0112] Specifically, the control unit can first obtain a particle flow pattern of the sample liquid based on the pulsed digital signal, wherein each particle number in the particle flow pattern is the number of particles flowing through the flow chamber 12 detected by the photoelectric detection assembly in a predetermined time period, then obtain a plurality of time points and a plurality of particle numbers corresponding to the plurality of time points based on the particle flow pattern of the sample liquid, wherein the particle numbers correspond to the time points one by one, and obtain a correlation coefficient of the time points and the particle numbers based on the plurality of time points and the plurality of particle numbers corresponding to the time points. The control unit can calculate the correlation coefficient Tr of the time points and the particle numbers using the absolute value of the Pearson correlation coefficient:

[0113]

[0114] wherein, Tx i represents the i-th time point, Ty i represents the i-th particle number, wherein the i-th time point corresponds to the i-th particle number, is the average of the plurality of time points, is the average of the plurality of particle numbers.

[0115] Further, the control unit can use linear regression to fit the slope of the fitting straight line formed by the plurality of time points and the plurality of particle numbers (the slope of the fitting straight line of the particle flow pattern), wherein since the slope has a positive slope and a negative slope, in order to improve the subsequent calculation efficiency, the absolute value Tk of the slope is used to represent, and the specific calculation formula is:

[0116]

[0117] wherein, Tx i represents the i-th time point, Ty i represents the i-th particle number, wherein the i-th time point corresponds to the i-th particle number, is the average of the plurality of time points, is the average of the plurality of particle numbers.

[0118] And based on the correlation coefficient Tr and the absolute value Tk of the slope obtained by calculation, the particle flow inclination Ts of the sample liquid is obtained, and the specific calculation formula is:

[0119] Ts = Tr x Tk x A (6)

[0120] Wherein, A is a preset adjustment parameter (A>1), to adjust the range of particle flow inclination Ts mostly distributed in the range of 0~100.

[0121] In the case that the flow chamber 12 does not have the problem of hole blockage, Tr≈0, Tk≈0, so Ts≈0; while in the case that the particle flow pattern produces changes as shown in Figure 5 (b), Tr>0.8, Tk>1, Ts>1.

[0122] In actual application, the control unit can be preset with a preset particle flow inclination Tth. When the calculated particle flow inclination Ts is greater than the preset particle flow inclination Tth, it can be considered that the flow chamber 12 has a hole blocking problem at this time, the number of cells of the sample liquid flowing through the flow chamber 12 is abnormal at this time, which will affect the detection result of the sample liquid, and the control unit will immediately issue an alarm signal. When the calculated particle flow inclination Ts of the control unit is greater than 1 and less than the preset particle flow inclination Tth, it can be considered that the flow chamber 12 may have a small degree of hole blocking problem at this time, but it does not affect the detection result of the sample liquid, and the control unit can not issue an alarm signal, or the control unit can issue a warning signal to remind the user that the flow chamber 12 may have a hole blocking problem affecting the detection efficiency of the sample liquid in the future, and remind the user to pay attention.

[0123] Optionally, the specific setting value of the preset particle flow inclination Tth is 0-100, for example, 10, 20, 25, 30, 40, 60, 80, etc., preferably 40, which can be set by the user according to the needs, and the specific setting value of the preset particle flow inclination Tth is not limited in the present application.

[0124] In other embodiments, the control unit is also used to obtain a plurality of particle numbers in a continuous time period in the particle flow pattern of the sample liquid based on the pulse digital signal, and then the control unit can further obtain the average value of the plurality of particle numbers, the maximum particle number in the plurality of particle numbers and the minimum particle number in the plurality of particle numbers, and obtain the particle flow jump degree of the sample liquid based on the average value of the plurality of particle numbers, the maximum particle number in the plurality of particle numbers and the minimum particle number in the plurality of particle numbers.

[0125] Wherein, please refer to Figure 6 , Figure 6 is a structural schematic diagram of the second embodiment of the particle flow of the sample liquid flowing through the flow chamber of the present application. Wherein, Figure 6 (a) is the optical signal generated by the light beam passing through the sample liquid flowing in the flow chamber 12 when the flow chamber 12 has no hole blocking problem, and the particle flow pattern obtained by processing; Figure 6 (b) is the optical signal generated by the light beam passing through the sample liquid in the flow chamber 12 when the flow chamber 12 has a hole blocking problem, and the particle flow pattern obtained by processing, wherein the abscissa of the particle flow pattern is time, and the ordinate is the number of particles. It can be seen that, Figure 6 In (a), the particle flow curve is relatively stable, while in Figure 6 In (b), the particle flow gradually decreases with time and has a relatively obvious jump.

[0126] Wherein, the particle flow pattern can represent the number of particles flowing through every fixed time period in the flow chamber 12, that is, the flow amount of the sample liquid in the flow chamber 12, such as Figure 6(a) as shown, if the sample liquid flows uniformly in the flow chamber 12, the number of particles in the particle flow pattern tends to be stable at each time. However, in Figure 6 (b), due to the hole blocking problem of the flow chamber 12, the flow of the sample liquid is interrupted, and the number of particles in the particle flow pattern changes with time.

[0127] Specifically, the control unit can calculate the particle flow jump degree Jp of the sample liquid by using the following formula:

[0128]

[0129] wherein max(Ty) is the maximum number of particles in the plurality of particle numbers, min(Ty) is the minimum number of particles in the plurality of particle numbers, is the average value of the plurality of particle numbers, and B and C are preset adjustment parameters (B>1, C>1) for adjusting the range of the particle flow jump degree Jp of the sample liquid to be mostly distributed in the range of 0-100.

[0130] In the case where the flow chamber 12 does not have the hole blocking problem, Jp≈0; and in the case where the particle flow pattern changes as shown in Figure 6 (b), Jp>1.

[0131] In practical applications, the control unit can preset a preset particle flow jump degree Jth. When the calculated particle flow jump degree Jp is greater than the preset particle flow jump degree Jth, it can be considered that the flow chamber 12 has a hole blocking problem at this time, and the number of cells of the sample liquid flowing through the flow chamber 12 is abnormal, which will affect the detection result of the sample liquid, and the control unit will immediately issue an alarm signal. When the calculated particle flow jump degree Jp of the control unit is greater than 1 but less than the preset particle flow jump degree Jth, it can be considered that the flow chamber 12 may have a small degree of hole blocking problem, but it does not affect the detection result of the sample liquid, so the control unit can not issue an alarm signal, or the control unit can issue a warning signal to remind the user that the flow chamber 12 may have a hole blocking problem that affects the detection efficiency of the sample liquid in the future, reminding the user to pay attention.

[0132] Optionally, the preset particle flow jump degree Jth has a specific set value of 0-100, such as 10, 20, 25, 30, 40, 60, 80, etc., preferably 40, which can be set by the user according to the demand, and the specific set value of the preset particle flow jump degree Jth is not limited in the present application.

[0133] In summary, the control unit can calculate the particle flow jump degree Jp, the particle flow tilt degree Ts, the voltage characteristic value Pm and the pulse width characteristic Wd of the sample liquid based on the above calculation method, so as to accurately determine whether the flow chamber 12 has the hole blocking problem, and improve the detection efficiency of the blood cell analyzer on the sample liquid.

[0134] In an embodiment, please continue to refer to Figure 2 , the optical information processing assembly 15 further comprises a baseline amplifier 154, that is, the optical information processing assembly 15 can comprise a beam splitter 151, a photoelectric converter 152, a baseline amplifier 154 and an A / D converter 153.

[0135] Wherein, the beam splitter 151 separates the front light scattering in the optical signal, the photoelectric converter 152 receives the front light scattering and converts the front light scattering into an analog signal, the baseline amplifier 154 receives the analog signal transmitted by the photoelectric converter 152 and amplifies the baseline voltage of the analog signal, and the A / D converter 153 converts the processed analog signal into a pulse digital signal, and the control unit receives the pulse digital signal and obtains the voltage characteristic value of the sample liquid based on the pulse digital signal.

[0136] Wherein, as can be seen from the foregoing, the voltage characteristic value is obtained by the control unit generating a baseline voltage curve based on the pulse digital signal and then processing the baseline voltage curve, therefore, in the embodiment of the application, a baseline amplifier 154 is added to amplify the baseline voltage, thereby improving the processing efficiency of the subsequent control unit.

[0137] After obtaining the pulse digital signal, the control unit can obtain the voltage characteristic value based on formula (1), which has been described in detail in the foregoing and will not be repeated here.

[0138] Wherein, in order to reduce operating costs in the embodiment, the front light scattering is used to obtain the baseline voltage curve, which does not mean that the calculation of the voltage characteristic value of the sample liquid can only use the front light scattering in the optical signal, in other embodiments, the side light scattering or fluorescence signal in the optical signal can also be used for processing, which is not limited in the application.

[0139] In another embodiment, please continue to refer to Figure 2 , the optical information processing assembly 15 further comprises a pulse amplifier 155, that is, the optical information processing assembly 15 comprises a beam splitter 151, a photoelectric converter 152, a pulse amplifier 155 and an A / D converter 153.

[0140] The beam splitter 151 separates the effective optical signal in the optical signal, the photoelectric converter 152 receives the effective optical signal and converts the effective optical signal into an analog signal, the pulse amplifier 155 receives the analog signal and amplifies the pulse signal of the analog signal, the A / D converter converts the processed analog signal into a pulse digital signal, and the control unit receives the pulse digital signal and obtains the pulse width characteristic of the sample liquid based on the pulse digital signal.

[0141] According to the foregoing, the pulse width characteristic is obtained by processing the pulse width distribution map generated by the control unit based on the pulse digital signal. Therefore, in the embodiment of the application, the pulse amplifier 155 is added to amplify the pulse signal, thereby improving the processing efficiency of the subsequent control unit.

[0142] After obtaining the pulse digital signal, the control unit can obtain the pulse width characteristic based on formula (2) and formula (3). The foregoing has been described in detail, and thus will not be described here.

[0143] Further, the control unit can also obtain the particle flow pattern of the particle number of the sample liquid flowing through the flow chamber 12 with time based on the pulse digital signal processed by the pulse amplifier 155, and obtain the particle flow jump degree and the particle flow inclination degree of the sample liquid based on the particle flow pattern.

[0144] Specifically, the control unit can calculate the particle flow inclination degree of the sample liquid based on formula (4), formula (5) and formula (6), and calculate the particle flow jump degree of the sample liquid based on formula (7).

[0145] In summary, in the blood cell analyzer provided by the embodiment of the application, in the process of detecting the sample liquid, the control unit can process the optical signal collected by the photoelectric detection assembly 14 to obtain the signal parameter of the sample liquid flowing through the flow chamber 12, and determine whether the flow chamber 12 has a hole blocking problem. The determination of whether the flow chamber 12 has a hole blocking problem can be completed during the sample detection process, and an alarm signal can be generated in time when the flow chamber 12 has a hole blocking problem, thereby improving the efficiency of the blood cell analyzer in detecting the sample. Moreover, no additional determination step is needed, and the determination can be completed during the detection of the sample liquid, thereby further improving the operation efficiency of the blood cell analyzer and enhancing the user experience of the blood cell analyzer.

[0146] The application also provides a detection method for a hole blocking problem of a flow chamber, which is applied to the blood cell analyzer as described above. Please refer to Figure 7 , Figure 7 which is a flowchart of the first embodiment of the detection method of the application. The detection method provided by the embodiment of the application specifically includes the following steps:

[0147] S1: obtaining an optical signal generated in the process of the sample liquid flowing through the flow chamber 12.

[0148] In the process of the sample liquid supplied by the sample liquid supply assembly 11 flowing through the flow chamber 12, the light beam emitted by the laser 13 passes through the sample liquid in the flow chamber 12, and then is collected by the photoelectric detection assembly 14. The photoelectric detection assembly 14 processes the received optical signal parameters into the optical information processing assembly 15, and then the optical information processing assembly 15 processes the obtained pulse digital signal into the control unit.

[0149] S2: obtaining a signal parameter of the sample liquid flowing through the flow chamber 12 based on the optical signal.

[0150] After the control unit receives the pulse digital signal obtained by the optical information processing assembly 15 based on the optical signal, the control unit can process the pulse digital signal (the specific processing process is described above, and will not be described here) to obtain at least one signal parameter of the sample liquid flowing through the flow chamber 12, such as the sample liquid inclination, the sample liquid jump degree, the voltage characteristic value, and the pulse width characteristic.

[0151] S3: in response to the signal parameter not belonging to the standard range, determining that the flow chamber 12 has a hole blocking problem and issuing an alarm.

[0152] After obtaining the signal parameter, the control unit can further compare the signal parameter with the standard range, and in response to the signal parameter not belonging to the standard range, determine that the flow chamber 12 has a hole blocking problem and issue an alarm.

[0153] In an embodiment, after the hole blocking problem of the flow chamber 12 is excluded, the sample liquid can be rechecked to improve the detection accuracy of the blood cell analyzer on the sample liquid.

[0154] And in response to the signal parameter belonging to the standard range, that is, the flow chamber 12 does not have a hole blocking problem, the blood cell analyzer can output the detection result of the sample liquid.

[0155] In summary, in the detection method provided by the present application, the control unit of the blood cell analyzer can process the optical signal generated in the process of the sample liquid flowing through the flow chamber 12, obtain the signal parameter of the sample liquid flowing through the flow chamber 12, and determine whether the flow chamber 12 has a hole blocking problem based on the signal parameter, thereby reducing the occurrence of sample liquid detection errors and improving the detection efficiency of the blood cell analyzer on the sample liquid. At the same time, without the need to additionally set up a judgment process to determine the hole blocking problem of the flow chamber 12, the blood cell analyzer can achieve the determination in the process of detecting the sample liquid, thereby improving the operation efficiency of the blood cell analyzer.

[0156] Optionally, please refer to Figure 8 ,Figure 8 is a flowchart of a second embodiment of the detection method of the present application. In the case where the signal parameter comprises the particle flow jump degree of the sample liquid, the detection method provided by the embodiment of the present application specifically comprises the following steps:

[0157] S81: Based on the optical signal, the particle flow jump degree of the sample liquid flowing through the flow chamber 12 is obtained. In response to the particle flow jump degree being greater than the preset particle flow jump degree, it is determined that the flow chamber 12 has a clogging problem, and an alarm is issued.

[0158] In the case where the signal parameter comprises the particle flow jump degree of the sample liquid, the control unit can calculate the particle flow jump degree of the sample liquid by using formula (7), and compare the calculated particle flow jump degree with the preset particle flow jump degree. In response to the particle flow jump degree being greater than the preset particle flow jump degree, that is, the number of cells of the sample liquid flowing through the flow chamber 12 is abnormal at this time, the control unit determines that the flow chamber 12 has a clogging problem, issues an alarm, reminds the user to call the clogging timing sequence, and removes the clogging problem of the flow chamber 12, thereby improving the detection efficiency of the blood cell analyzer on the sample liquid.

[0159] Optionally, please refer to Figure 9 , Figure 9 is a flowchart of a third embodiment of the detection method of the present application. In the case where the signal parameter comprises the particle flow inclination degree of the sample liquid, the detection method provided by the embodiment of the present application specifically comprises the following steps:

[0160] S91: Based on the optical signal, the particle flow inclination degree of the sample liquid flowing through the flow chamber 12 is obtained. In response to the particle flow inclination degree being greater than the preset particle flow inclination degree, it is determined that the flow chamber 12 has a clogging problem, and an alarm is issued.

[0161] In the case where the signal parameter comprises the particle flow inclination degree of the sample liquid, the control unit can calculate the particle flow inclination degree of the sample liquid by using formula (4), formula (5) and formula (6), and compare the calculated particle flow inclination degree with the preset particle flow inclination degree. In response to the particle flow inclination degree being greater than the preset particle flow inclination degree, that is, the flow rate of the sample liquid flowing through the flow chamber 12 is abnormal at this time, the control unit determines that the flow chamber 12 has a clogging problem, issues an alarm, reminds the user to call the clogging timing sequence, and removes the clogging problem of the flow chamber 12, thereby improving the detection efficiency of the blood cell analyzer on the sample liquid.

[0162] Optionally, please refer to Figure 10 , Figure 10 is a flowchart of a fourth embodiment of the detection method of the present application. In the case where the signal parameter comprises the voltage characteristic value of the sample liquid, the detection method provided by the embodiment of the present application specifically comprises the following steps:

[0163] S101: Obtain the voltage characteristic value of the sample liquid flowing through the flow chamber 12 based on the optical signal, and determine that the flow chamber 12 has a hole blocking problem and issue an alarm in response to the voltage characteristic value being greater than the preset voltage characteristic value.

[0164] In the case where the signal parameter includes the voltage characteristic value of the sample liquid, the control unit can calculate the voltage characteristic value of the sample liquid by using formula (1), and compare the calculated voltage characteristic value with the preset voltage characteristic value. In response to the voltage characteristic value being greater than the preset voltage characteristic value, that is, the stability of the sample liquid flowing through the flow chamber 12 is abnormal, the control unit determines that the flow chamber 12 has a hole blocking problem, issues an alarm, reminds the user to call the hole blocking timing, removes the hole blocking problem of the flow chamber 12, and improves the detection efficiency of the blood cell analyzer on the sample liquid.

[0165] Optionally, referring to Figure 11 , Figure 11 is the flowchart of the fifth embodiment of the detection method of the application. In the case where the signal parameter includes the pulse width characteristic of the sample liquid, the detection method provided by the embodiment of the application specifically includes the following steps:

[0166] S111: Obtain the pulse width characteristic of the sample liquid flowing through the flow chamber 12 based on the optical signal, and determine that the flow chamber 12 has a hole blocking problem and issue an alarm in response to the pulse width characteristic being greater than the preset pulse width characteristic.

[0167] In the case where the signal parameter includes the pulse width characteristic of the sample liquid, the control unit can calculate the pulse width characteristic of the sample liquid by using formula (2) and formula (3), and compare the calculated pulse width characteristic with the preset pulse width characteristic. In response to the pulse width characteristic being greater than the preset pulse width characteristic, that is, the flow rate of the sample liquid flowing through the flow chamber 12 is slower, the control unit determines that the flow chamber 12 has a hole blocking problem, issues an alarm, reminds the user to call the hole blocking timing, removes the hole blocking problem of the flow chamber 12, and improves the detection efficiency of the blood cell analyzer on the sample liquid.

[0168] It can be understood that in the process of detecting the sample liquid by the blood cell analyzer, the control unit can determine whether the flow chamber 12 has a hole blocking problem based on one of the particle flow jump degree, the particle flow inclination, the voltage characteristic value, and the pulse width characteristic of the sample liquid obtained based on the optical signal, that is, one of steps S81, S91, S101, and S111 can be performed to determine whether the flow chamber 12 has a hole blocking problem.

[0169] Or, the control unit can determine whether the flow chamber 12 has the clogging problem based on the optical signal, the particle flow jump degree, the particle flow inclination degree, the voltage characteristic value, and the pulse width characteristic of the sample liquid, i.e., can determine whether the flow chamber 12 has the clogging problem based on two of the steps S81, S91, S101, and S111.

[0170] Or, the control unit can determine whether the flow chamber 12 has the clogging problem based on the optical signal, the particle flow jump degree, the particle flow inclination degree, the voltage characteristic value, and the pulse width characteristic of the sample liquid, i.e., can determine whether the flow chamber 12 has the clogging problem based on three of the steps S81, S91, S101, and S111.

[0171] Or, the control unit can determine whether the flow chamber 12 has the clogging problem based on the optical signal, the particle flow jump degree, the particle flow inclination degree, the voltage characteristic value, and the pulse width characteristic of the sample liquid, i.e., can determine whether the flow chamber 12 has the clogging problem based on all of the steps S81, S91, S101, and S111.

[0172] The present application does not limit the specific number and specific parameters of the four parameters of the particle flow jump degree, the particle flow inclination degree, the voltage characteristic value, and the pulse width characteristic of the sample liquid used by the control unit.

[0173] Further, the present application does not limit the order of the judgment steps of the two or more parameters in the process of determining the two or more parameters of the particle flow jump degree, the particle flow inclination degree, the voltage characteristic value, and the pulse width characteristic of the sample liquid by the control unit. For example, when the control unit determines whether the flow chamber 12 has the clogging problem based on the steps S81, S91, and S111, the step S81 can be performed first, then the step S111, and finally the step S81, or the step S81 can be performed first, then the step S91, and finally the step S111, or the step S91 can be performed first, then the step S81, and finally the step S111, or the step S91 can be performed first, then the step S111, and finally the step S81, or the step S111 can be performed first, then the step S81, and finally the step S91, or the step S111 can be performed first, then the step S91, and finally the step S81, or the steps S81, S91, and S111 can be performed simultaneously, etc.

[0174] To sum up, the detection method provided by the embodiments of the present application further proposes that the control unit can judge whether the flow chamber 12 has the hole blocking problem based on the particle flow inclination, the particle flow jump, the voltage characteristic value and the pulse width characteristic of the sample flow, further improves the efficiency of the judgment of the control unit, improves the detection efficiency of the blood cell analyzer on the sample, and improves the operation efficiency of the blood cell analyzer.

[0175] The above merely describes the embodiments of the present application, and does not limit the patent scope of the present application. Any equivalent structure or equivalent process transformation using the content of the specification and drawings, or direct or indirect application in other related technical fields, are also included in the patent protection scope of the present application.

Claims

1. A blood cell analyzer, characterized in that, Including optical inspection systems, The optical detection system includes a sample liquid supply component, a flow chamber, a laser, a photoelectric detection component, and an optical information processing component. The sample solution supply component is connected to the flow chamber and is used to supply sample solution to the flow chamber; the laser is spaced apart from the flow chamber, and the photoelectric detection component is located on the side of the flow chamber away from the laser and is correspondingly arranged to the laser; During the process of the sample liquid supply assembly delivering sample liquid to the flow chamber, the light beam generated by the laser enters the photoelectric detection assembly after passing through the sample liquid in the flow chamber. The photoelectric detection assembly receives the optical signal carrying the information of the sample liquid and transmits the optical signal to the optical information processing assembly. The optical information processing assembly processes the optical signal to obtain the pulse digital signal of the sample liquid flowing through the flow chamber. The blood cell analyzer also includes a control unit connected to the optical information processing component. The control unit receives the pulse digital signal, processes the pulse digital signal to obtain the signal parameters of the sample fluid flowing through the flow chamber, and determines whether there is a blockage problem in the flow chamber based on the signal parameters.

2. The blood cell analyzer according to claim 1, characterized in that, The signal parameters include the particle flow jump degree of the sample liquid. The control unit is used to determine that there is a blockage problem in the flow chamber and issue an alarm signal in response to the particle flow jump degree being greater than a preset particle flow jump degree. And / or, the signal parameters include the particle flow inclination of the sample liquid, and the control unit is configured to, in response to the particle flow inclination being greater than a preset particle flow inclination, determine that there is a blockage problem in the flow chamber and issue an alarm signal; And / or, the signal parameters include the voltage characteristic value of the sample liquid, and the control unit is used to determine that there is a blockage problem in the flow chamber and issue an alarm signal in response to the voltage characteristic value being greater than a preset voltage characteristic value; And / or, the signal parameters include the pulse width characteristics of the sample liquid, and the control unit is configured to, in response to the pulse width characteristics being greater than a preset pulse width characteristics, determine that there is a blockage problem in the flow chamber and issue an alarm signal.

3. The blood cell analyzer according to claim 2, characterized in that, The optical information processing component includes: A beam splitter is used to separate the effective optical signal from the optical signal; A photoelectric converter is used to receive the effective optical signal obtained by the beam splitter and convert the effective optical signal into an analog signal; An A / D converter is used to convert the analog signal into the pulse digital signal; The control unit is configured to receive the pulse digital signal transmitted by the A / D converter and process the pulse digital signal to obtain the signal parameters of the sample liquid flowing through the flow chamber.

4. The blood cell analyzer according to claim 2 or 3, characterized in that, The control unit is also used for, Acquire a first pulse digital signal of the sample fluid flowing through the flow chamber, and based on the first pulse digital signal, acquire a first analog baseline signal of the sample fluid flowing through the flow chamber, and a first median value of the first analog baseline signal; The second pulse digital signal of the sample liquid after it flows through the flow chamber is obtained, and a second analog baseline signal in which the sample liquid does not exist in the flow chamber is obtained based on the second pulse digital signal, as well as a second median value of the second analog baseline signal; The voltage characteristic values ​​of the sample solution are obtained based on the first median value and the second median value.

5. The blood cell analyzer according to claim 2 or 3, characterized in that, The control unit is also used for, Based on the pulsed digital signal, the width values ​​of multiple consecutive pulses are obtained during the flow of the sample liquid through the flow chamber, and the average value and standard value of the multiple pulse width values ​​are obtained. The pulse width characteristics of the sample solution are obtained based on the average value and standard value of the plurality of pulse width values.

6. The blood cell analyzer according to claim 2 or 3, characterized in that, The control unit is also used for, Based on the pulsed digital signal, multiple consecutive time points and multiple particle counts are obtained during the process of the sample liquid flowing through the flow chamber, wherein the particle count corresponds one-to-one with the time point; Based on multiple time points and multiple particle numbers corresponding to the time points, obtain the correlation coefficient between the time points and the particle numbers, and obtain the slope of the fitted straight line formed by the multiple time points and the multiple particle numbers; Based on the correlation coefficient and the slope, the particle flow inclination of the sample liquid is obtained.

7. The blood cell analyzer according to claim 2 or 3, characterized in that, The control unit is also used for, The number of particles in a continuous time period is obtained based on the pulsed digital signal as the sample liquid flows through the flow chamber; Obtain the average value of the plurality of particle counts, the maximum particle count among the plurality of particle counts, and the minimum particle count among the plurality of particle counts; The particle flow hopping degree of the sample solution is obtained based on the average value, the maximum number of particles, and the minimum number of particles.

8. The blood cell analyzer according to claim 2, characterized in that, The optical information processing components include a beam splitter, a photoelectric converter, a baseline amplifier, and an A / D converter. The beam splitter separates the forward-scattered light from the optical signal; the photoelectric converter receives the forward-scattered light and converts it into an analog signal; the baseline amplifier receives the analog signal and amplifies the baseline voltage of the analog signal; the A / D converter converts the processed analog signal into a pulse digital signal; the control unit receives the pulse digital signal and obtains the voltage characteristic value of the sample liquid based on the pulse digital signal.

9. The blood cell analyzer according to claim 2, characterized in that, The optical information processing components include a beam splitter, a photoelectric converter, a pulse amplifier, and an A / D converter. The beam splitter separates the effective light signal from the optical signal; the photoelectric converter receives the effective light signal and converts it into an analog signal; the pulse amplifier receives the analog signal and amplifies the pulse signal of the analog signal; the A / D converter converts the processed analog signal into a pulse digital signal; the control unit receives the pulse digital signal and obtains the pulse width characteristics of the sample liquid based on the pulse digital signal.

10. The blood cell analyzer according to claim 9, characterized in that, The control unit is further configured to: obtain a particle flow pattern of the number of particles flowing through the flow chamber of the sample liquid over time based on the pulse digital signal, and obtain the particle flow jump degree and the particle flow tilt degree of the sample liquid based on the particle flow pattern.

11. A method for detecting blockage in a flow chamber, characterized in that, Applied to the blood cell analyzer as described in any one of claims 1-10, the detection method comprises: Acquire the optical signal generated during the process of sample liquid flowing through the flow chamber for detection; The signal parameters of the sample liquid flowing through the flow chamber are obtained based on the optical signal; If the signal parameters are outside the standard range, it is determined that there is a blockage problem in the flow chamber, and an alarm is issued.

12. The detection method according to claim 11, characterized in that, The steps of acquiring signal parameters of the sample liquid flowing through the flow chamber based on the optical signal, and determining that the flow chamber has a blockage problem and issuing an alarm in response to the signal parameters not being within the standard range, include: The particle flow jump degree when the sample liquid flows through the flow chamber is obtained based on the optical signal; if the particle flow jump degree is greater than the preset particle flow jump degree, it is determined that there is a blockage problem in the flow chamber and an alarm is issued. And / or, based on the optical signal, the particle flow inclination of the sample liquid as it flows through the flow chamber is obtained; in response to the particle flow inclination being greater than a preset particle flow inclination, it is determined that there is a blockage problem in the flow chamber, and an alarm is issued; And / or, based on the optical signal, obtain the voltage characteristic value of the sample liquid flowing through the flow chamber; in response to the voltage characteristic value being greater than a preset voltage characteristic value, determine that there is a blockage problem in the flow chamber and issue an alarm; And / or, based on the optical signal, obtain the pulse width characteristics of the sample liquid flowing through the flow chamber; in response to the pulse width characteristics being greater than a preset pulse width characteristics, determine that there is a blockage problem in the flow chamber and issue an alarm.

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