Cell comparison device for flow cytometry

Abstract

The invention relates to the technical field of flow cytometry analysis, in particular to a cell comparison device for flow cytometry analysis, which comprises a shell and a communication module, a liquid flow assembly and a test assembly are arranged in the shell, the liquid flow assembly comprises a flow chamber, sheath fluid and a driving assembly are arranged in the flow chamber, and the driving assembly is used for driving the sheath fluid to flow; the sheath fluid is used for driving cells in the sample flow to be arranged in sequence, an auxiliary channel is further arranged in the flowing chamber and used for shunting the sample flow, the output end of the auxiliary channel is communicated with the output end of the flowing chamber, and the device is used for reducing errors caused by vibration and the like generated in the working process of the device to data acquisition.

Description

Technical Field

[0001] The present invention relates to the technical field of flow cytometric analysis, and in particular to a cell contrast device for flow cytometric analysis. Background Art

[0002] Flow cytometry (FCM) is a single-cell quantitative analysis and sorting technology using flow cytometer.

[0003] The working principle of flow cytometry is to perform multi-parameter, rapid quantitative analysis of single cells or other biological particles at the cellular molecular level through monoclonal antibodies. It uses a flow cytometer to allow fluorescently labeled cells or particles suspended in a liquid to pass through a sample pool one by one. At the same time, the fluorescence detector captures the fluorescence signal and converts it into electrical pulse signals representing the forward scattering angle, side scattering angle and different fluorescence intensities. After these signals are processed by a computer, corresponding dot plots, histograms and three-dimensional structural images are formed for further analysis.

[0004] The flow cytometer is mainly composed of three parts: first, the liquid flow system, including the flow chamber and the liquid flow drive system, which is used to introduce the cell suspension into the sample pool to form a sample flow; second, the optical system, including the light source and the signal detection and transmission part, which is used to generate fluorescent signals and capture these signals; third, the electronic system, including the photoelectric converter and the data processing system, which is used to convert the captured fluorescent signals into electrical pulse signals, and perform computer processing and analysis.

[0005] In the prior art, due to vibrations generated when the device is working, the air inside the flow cytometer is easily moved, so that the laser emitted to the sample flow in the optical system cannot overlap with the sample flow, thereby reducing the reliability of the data. Summary of the invention

[0006] In order to solve the above problems, the present invention provides a cell comparison device for flow cytometric analysis, which is used to reduce the error in data collection caused by vibration generated during the operation of the device.

[0007] In order to achieve the above-mentioned purpose, the technical scheme of the present invention is as follows: a cell comparison device for flow cytometric analysis, comprising a housing and a communication module, wherein a liquid flow component and a test component are arranged in the housing, wherein the liquid flow component is used to drive cells in a sample flow to sequentially pass through the test component, wherein the test component is used to collect photoelectric information of laser light after the cells are excited, wherein the liquid flow component comprises a flow chamber, wherein a sheath fluid and a drive component are arranged in the flow chamber, wherein the drive component is used to drive the sheath fluid to flow, wherein the sheath fluid is used to drive the cells in the sample flow to be arranged sequentially, wherein a side channel is further arranged in the flow chamber, wherein the side channel is used to divert the sample flow, and wherein the output end of the side channel is connected to the output end of the flow chamber;

[0008] It also includes a control system, which is used to obtain basic information of cells in samples in the flow chamber, at the output end of the flow chamber, and in the side channel according to the photoelectric information, and calculate the similarity between the sum of the basic information of cells in the sample flow in the flow chamber and the sample flow in the side channel and the basic information of cells in the sample at the output end of the flow chamber. When the similarity is lower than a preset value, the data reliability is insufficient, and the control communication module outputs the basic information of cells at the output end of the flow chamber to the user and outputs a prompt message. When the similarity is greater than or equal to the preset value, the data is reliable, and the control communication module outputs the basic information of cells at the output end of the flow chamber to the user.

[0009] Furthermore, two electric fields with opposite electrodes are arranged in the flow chamber, both of which are used to generate electric charges in the cells in the flow chamber, and a deflection plate is arranged in the shell, which is used to drive the charged cells to move.

[0010] Furthermore, the test component includes a laser light source, a lens and a light detector. The laser light source is used to generate laser light, and the light detector is used to receive the laser light beam after cell excitation and generate a corresponding photoelectric signal.

[0011] Furthermore, a shock-absorbing component is provided in the shell, and the shock-absorbing component is used to adjust the relative position of the test component and the output end of the flow chamber. The control system is used to determine whether the sample flow at the output end of the flow chamber intersects with the laser based on the basic cell information, and control the shock-absorbing component to work only when the sample flow does not intersect with the laser.

[0012] Furthermore, a shock-absorbing layer made of elastic material is provided on both the laser light source and the light detector, and the shock-absorbing layer is used to absorb the vibration generated when the laser light source and the light detector are working.

[0013] Furthermore, the control system includes a controller, which is used to obtain basic information of cells in samples in the flow chamber, at the output end of the flow chamber and in the side channel based on the photoelectric signals collected by the light detector, and calculate the similarity between the sum of the basic information of cells in the sample in the flow chamber and the sample flow in the side channel and the basic information of cells in the sample at the output end of the flow chamber. When the similarity is lower than a preset value, the data reliability is insufficient, and the control communication module outputs the basic information of cells at the output end of the flow chamber to the user and outputs a prompt message. When the similarity is greater than or equal to the preset value, the data is reliable, and the control communication module outputs the basic information of cells at the output end of the flow chamber to the user. The controller is also used to determine whether the laser and the sample flow intersect based on the basic cell information, and control the damping component to work only when the sample flow does not intersect with the laser.

[0014] Furthermore, the control system also includes a temperature sensor and a humidity sensor. The temperature sensor is used to collect temperature information inside the shell, and the humidity sensor is used to collect humidity information inside the shell. The controller is also used to control the communication module to alarm the user when the temperature information is not within a preset optimal temperature range, and to control the communication module to alarm the user when the humidity information is greater than a preset maximum humidity.

[0015] Furthermore, the shell is connected to a pump assembly, which is used to drive the gas flow inside the shell, and the controller controls the operation of the pump assembly according to temperature information.

[0016] Furthermore, a heating wire is provided in the shell, and the heating wire is used to heat the gas in the shell. The controller controls the operation of the heating wire and the pump assembly according to the temperature information.

[0017] Furthermore, a dehumidification component is provided at the connection point between the shell and the pump component, and the dehumidification component is used to remove moisture in the gas flowing through.

[0018] Technical principles and beneficial effects of the above scheme:

[0019] The design of the sub-channel in this scheme realizes the testing of cells at different positions after the sample flow is diverted. The reliability of the test results is verified by comparing the two test results. Compared with the existing technology, it can avoid defects such as insufficient data reading time caused by too fast sample flow speed, too short irradiation time and cell loss caused by mechanical vibration, thereby improving the accuracy of the data finally obtained. At the same time, the design of the sub-channel can cause changes in the air pressure in the sub-channel during the movement of the sample flow, so that the sub-channel can give the sample flow a certain thrust, thereby prompting the sample flow to pass through the output end of the flow chamber more quickly, improving the speed of the inspection, and the cells accumulate at the output end of the flow chamber, thereby affecting the accuracy of the data finally obtained.

[0020] Additional aspects and advantages of the present invention will be given in part in the following description and in part will be obvious from the following description, or will be learned through practice of the present invention. BRIEF DESCRIPTION OF THE DRAWINGS

[0021] Figure 1 An axonometric diagram of an embodiment of a cell contrast device for flow cytometric analysis of the present invention;

[0022] Figure 2 A top view of an embodiment of a cell comparison device for flow cytometric analysis of the present invention;

[0023] Figure 3 for Figure 2 Cross-section view in the AA direction;

[0024] Figure 4 for Figure 2 Cross-section along the middle BB direction;

[0025] Figure 5 FIG. 4 is a circuit diagram of an embodiment of a cell comparison device for flow cytometric analysis of the present invention.

[0026] The figure marks in the drawings of the specification include: 1. shell; 2. test component; 21. light detector; 22. lens; 23. laser light source; 24. micro electric cylinder; 25. transmission motor; 3. liquid flow component; 31. deflection plate; 32. flow chamber; 33. side channel; 34. sample tube; 35. sheath fluid. DETAILED DESCRIPTION

[0027] The technical solution of the present invention will be described clearly and completely below in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0028] In the description of the present invention, it should be noted that the terms "center", "upper", "lower", "left", "right", "vertical", "horizontal", "inner", "outer", etc., indicating the orientation or positional relationship, are based on the orientation or positional relationship shown in the drawings, and are only for the convenience of describing the present invention and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore cannot be understood as limiting the present invention. In addition, the terms "first", "second", and "third" are used for descriptive purposes only, and cannot be understood as indicating or implying relative importance.

[0029] In the description of the present invention, it should be noted that, unless otherwise clearly specified and limited, the terms "installed", "connected", and "connected" should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection or an electrical connection; it can be a direct connection, or it can be indirectly connected through an intermediate medium, or it can be the internal communication of two components. For ordinary technicians in this field, the specific meanings of the above terms in the present invention can be understood according to specific circumstances.

[0030] The following is further described in detail through specific implementation methods:

[0031] Embodiment 1:

[0032] As attached Figure 1 -Attached Figure 5 As shown: a cell comparison device for flow cytometric analysis, comprising a housing 1 and a communication module, wherein the communication module is fixedly connected to the outer side wall of the housing 1 by bolts.

[0033] A liquid flow component 3 and a test component 2 are provided in the shell 1. The liquid flow component 3 is used to drive the cells in the sample flow to pass through the test component 2 in sequence. The test component 2 is used to collect basic information of the cells in the sample flow. The test component 2 includes a laser light source 23, a lens 22 and a light detector 21. In this embodiment, the light detector 21 is a photomultiplier tube. The laser light source 23, the lens 22 and the light detector 21 are all fixedly connected to the shell 1 by bolts. The laser light source 23 is used to generate laser, and the light detector 21 is used to receive the laser light beam after cell excitation and produce corresponding photoelectric signals. The test component 2 also includes a dichroic prism (not shown in the figure), a fluorescence signal detector, etc. (not shown in the figure).

[0034] The liquid flow component 3 includes a flow chamber 32, in which a sheath liquid 35 and a driving component are arranged. The driving component is used to drive the sheath liquid 35 to flow. The driving component includes a plurality of sheath tubes (not shown in the figure), which are connected to the flow chamber 32, and a solenoid valve is provided at the connection point between the two. The sheath liquid 35 in the sheath tube is in a high-pressure state. The sheath liquid 35 is used to drive the cells in the sample flow to be arranged in sequence. The flow chamber 32 is provided with a sample tube 34 and a water pump (not shown in the figure). The water pump is used to extract the sample into the sample tube 34. The flow chamber 32 is also provided with a side channel 33, which is used to divert the sample flow, and the output end of the side channel 33 is connected to the output end of the flow chamber 32:

[0035] It also includes a control system, which includes a controller. The fluorescence signal detection, light detector and communication module are all electrically connected to the controller. The controller is used to obtain basic information of cells in the flow chamber 32, the output end of the flow chamber 32 and the sample in the side channel 33 according to the photoelectric signal collected by the light detector, and calculate the similarity between the sum of the basic information of cells in the sample in the flow chamber 32 and the sample flow in the side channel 33 and the basic information of cells in the sample at the output end of the flow chamber 32. When the similarity is lower than a preset value, the data reliability is insufficient, and the control communication module outputs the basic information of cells at the output end of the flow chamber 32 to the user and outputs a prompt message. When the similarity is greater than or equal to the preset value, the data is reliable, and the control communication module outputs the basic information of cells at the output end of the flow chamber 32 to the user.

[0036] The specific implementation process is as follows: when using this device, the processed sample is injected into the sample tube 34 through a water pump. Under the action of fluid pressure, the sample flows downward along the sample tube 34 to form a sample flow. During this process, the solenoid valve is opened to allow high-pressure sheath fluid 35 to be ejected from the sheath tube into the flow chamber 32, wrapping the sample flow, so that the cells in the sample flow are arranged in a single row.

[0037] As the sample flow reaches the input end of the secondary channel 33 , inevitably, a small number of cells enter the secondary channel 33 , and under the action of fluid pressure and gravity, they eventually merge with the cells that have not entered the secondary channel 33 through the output end of the secondary channel 33 .

[0038] During this process, the laser light source 23 emits lasers to the sample flow in the flow chamber 32, the sample flow in the sub-channel 33, and the sample flow at the output end of the flow chamber 32 respectively. After passing through the sample flows at the above-mentioned positions, the laser is excited by the cells in the sample flows. Subsequently, the light detector 21 at the corresponding position receives the excited laser and generates corresponding photoelectric information. The controller obtains the basic information of the cells in the sample flows at each position based on the photoelectric information. The basic information includes cell size and morphology, number of different cells, etc.

[0039] Since both ends of the side channel 33 are connected to the flow chamber 32, theoretically, the basic information of the cells in the sample flow at both ends of the side channel 33 should be roughly the same. Therefore, after the experiment, the sum of the cells in the sample flow in the flow chamber 32 and the sample flow in the side channel 33, as well as the proportion of each type of cell therein should be similar to the sample flow at the output end of the flow chamber 32.

[0040] When the sample flow passes through the output end of the flow chamber 32, that is, the data value obtained by the light detector 21 at the output end of the flow chamber 32 no longer changes significantly, the controller calculates the total number of cells and the proportion of each type of cells in the sample flow in the flow chamber 32 and the sample flow in the side channel 33, and compares it with the cell neutralization and the proportion of each type of cells in the sample flow at the output end of the flow chamber 32. When the similarity between the two is greater than or equal to the preset value, the data error caused by factors such as cell loss, insufficient data reading time, too short irradiation time, and cell accumulation has little effect on data reliability. The data of the sample flow at the output end of the flow chamber 32 obtained at this time can be used for subsequent data analysis, and the controller controls the communication module to output corresponding data to the user; when the similarity between the two is less than the preset value, the data error caused by factors such as cell loss, insufficient data reading time, too short irradiation time, and cell accumulation has a greater impact on data reliability. The controller controls the communication module to work and outputs corresponding data and prompt information to the user, prompting the user to use this group of data with caution.

[0041] At the same time, due to the design of the auxiliary channel 33, when the sample flow passes through the output end of the auxiliary channel 33, due to the high-speed flow of the sample flow, the air flow rate at the output end of the auxiliary channel 33 increases, thereby causing the air pressure at the output end of the auxiliary channel 33 to decrease. Under the action of the air pressure, the gas in the auxiliary channel 33 gives the sample flow a thrust, thereby increasing the flow speed of the sample flow, avoiding cell accumulation at the output end of the flow chamber 32, and helping to improve the accuracy of the data finally obtained.

[0042] Embodiment 2:

[0043] The difference from Example 1 is that a vibration generator (not shown in the figure) and a charging circuit are further provided in the shell 1, and the vibration generator and the charging circuit are both arranged at the output end of the sample tube 34, the vibration generator is used to break the sample flow entering the flow chamber 32 into uniform droplets, the charging circuit is used to make the cells in the sample flow generate electric charges, and a deflection plate 31 is provided on the side of the shell 1 close to the secondary channel 33, and the deflection plate 31 is used to drive the charged cells to move.

[0044] The specific implementation process is as follows: when using this device, when the sample is injected into the flow chamber 32 through the sample tube 34, the vibration generator is started synchronously and the charging circuit is connected. Under the action of the vibration generator, the sample flow is interrupted and becomes droplets. At the same time, the charging circuit makes the droplets carry charges. Due to the existence of charges on the droplets, under the action of the deflection plate 31, part of the charge position is shifted, so that it can smoothly enter the secondary channel 33.

[0045] Due to the design of the vibration generator and the charging circuit, the movement trajectory of some cells in the sample flow is changed, and the amount of cells entering the secondary channel 33 is increased, thereby increasing the reliability of the basic information collected from the abdominal pain to the internal cells, avoiding data mutations caused by the small amount of data, and reducing the reliability of the data finally obtained.

[0046] Embodiment 3:

[0047] As attached Figure 4 As shown, the difference from Example 2 is that a shock-absorbing component is also provided in the shell 1, and the shock-absorbing component is used to adjust the relative position of the test component 2 and the output end of the flow chamber 32. The shock-absorbing component includes a plurality of groups of symmetrically arranged transmission motors 25, and the output ends of the transmission motors 25 are fixedly connected to the micro-electric cylinders 24 by bolts, and the output ends of the micro-electric cylinders 24 are bonded and fixed to the adjacent lenses 22. The micro-electric cylinders 24 and the transmission motors 25 are electrically connected to the controller, and the controller is also used to determine whether the laser and the sample flow intersect according to the basic information of the cells, and control the micro-cylinders and the transmission motors 25 to work only when the sample flow does not intersect with the laser.

[0048] The laser light source 23 and the light detector 21 are both wrapped with a shock-absorbing layer made of elastic material, and the shock-absorbing layer is used to absorb the vibration generated when the laser light source 23 and the light detector 21 are working.

[0049] The specific implementation process is as follows: During the use of the device, the controller determines whether the laser and the sample flow intersect according to the basic information of the cell. Since the basic information of the cells at three positions is obtained in this solution, and the flow speed of the sample flow is known, the time point when the same cell passes the position of the light detector 21 can be calculated. When there is a cell that is collected by the light detector 21 located at the position of the flow chamber 32 or the auxiliary channel 33, but not necessarily by the light detector 21 located at the output end of the flow chamber 32, at this time, the cell may fail to pass the laser located at the output end of the flow chamber 32 due to multiple factors such as air flow and vibration. At this time, the controller sequentially controls the transmission motor 25 and the micro-electric cylinder 24 to work, driving the lens 22 to rotate a unit angle or move a unit distance until the cell is collected by the light detector 21 located at the position of the flow chamber 32 or the auxiliary channel 33 and the light detector 21 at the output end of the flow chamber 32. The design of the shock-absorbing component can determine whether there is a situation where the laser and the sample flow do not converge according to the situation where the basic information of the cell is collected, and when this situation exists, the angle of the lens 22 is adjusted in time to adapt to the laser or sample flow deviation caused by different vibrations during the experiment, thereby improving the accuracy of the data collected by the device.

[0050] At the same time, the design of the shock-absorbing layer in the present solution is such that during use, the laser light source 23 and the light detector 21 will inevitably generate vibrations during operation. After the vibrations are transmitted to the shock-absorbing layer, the shock-absorbing layer is deformed, thereby converting the kinetic energy of the vibrations into the elastic potential energy of the shock-absorbing layer, reducing the influence of the vibrations on the stability of laser emission and reception, thereby further improving the accuracy of the data collected by the device.

[0051] Embodiment 4:

[0052] The difference from Example 3 is that the control system also includes a temperature sensor and a humidity sensor. The temperature sensor is used to collect temperature information inside the shell 1. The temperature sensor and the humidity sensor are both fixedly connected to the inner wall of the shell 1 by bolts. The humidity sensor is used to collect humidity information inside the shell 1. The temperature sensor and the humidity sensor are both electrically connected to the controller. The controller is also used to control the communication module to alarm the user when the temperature information is not within the preset optimal temperature range, and to control the communication module to alarm the user when the humidity information is greater than the preset maximum humidity.

[0053] The shell 1 is connected to a pump assembly (not shown in the figure). In this embodiment, the pump assembly is an air pump. The output end of the pump assembly is bonded and fixed to the top wall of the shell 1 and is connected. The input end of the pump assembly is bonded and fixed to the bottom wall of the shell 1 and is connected. The pump assembly is used to drive the flow of gas inside the shell 1. The controller is electrically connected to the pump assembly, and the controller controls the operation of the pump assembly according to temperature information.

[0054] A heating wire is fixedly connected to the shell 1 by bolts. The heating wire is used to heat the gas in the shell 1. The heating wire is arranged on the top wall of the shell 1 and is electrically connected to the controller. The controller controls the operation of the heating wire and the pump assembly according to temperature information.

[0055] A dehumidification assembly (not shown in the figure) is provided at the connection point between the shell 1 and the pump assembly. The dehumidification assembly includes a dehumidification box. The output end of the dehumidification box is connected to the pump assembly, and the input end of the dehumidification box is connected to the shell 1. A number of silica gel particles are placed in the dehumidification box. The dehumidification assembly is used to remove water vapor in the gas flowing through.

[0056] The specific implementation process is as follows: During the use of this device, the temperature sensor and the humidity sensor continuously collect the temperature information and humidity information inside the shell 1. The temperature of the normal flow cytometry experiment should be maintained at 18 degrees Celsius to 25 degrees Celsius, and the appropriate humidity should be below 64 percent. When the temperature and humidity inside the shell 1 cannot be maintained within the above range, the controller controls the communication module to alarm the user, reminding the user that the experimental environment is not good, prompting the user to adjust the experimental environment, which can improve the accuracy of the experimental data to a certain extent, and can also help users study the impact of the environment on the flow cytometry experimental data.

[0057] When the user does not need to conduct research on the environment and the accuracy of flow cytometry experimental data, the controller continuously evaluates the environment in the shell 1 based on the temperature information. When the temperature information is higher than the preset temperature of 25 degrees Celsius, the controller suspends the entry of the sample and sheath fluid 35, and controls the operation of the pump assembly. The pump assembly drives the gas flow in the shell 1. As the gas flows, the temperature in the shell 1 gradually diffuses to achieve the purpose of lowering the temperature of the experimental area (i.e., the output end of the flow chamber 32 and other positions), thereby reducing the impact of stability on the experiment. At the same time, since the airflow generated by the pump assembly flows from top to bottom, compared with the solution of flowing from bottom to top, it can prevent dust in the shell 1 from following the airflow and adhering to the output end of the flow chamber 32, affecting the flow of the sample, thereby affecting the progress of the experiment.

[0058] When the temperature in the shell 1 is too low, the controller controls the heating wire to work, and the heating wire heats the gas in the shell 1. At the same time, the controller controls the pump assembly to work. As the pump assembly works, the heated gas at the top of the shell 1 passes through the pump assembly to the bottom of the shell 1. Due to the collision of the heated gas volumes, the density of the high-temperature gas is greater than that of the low-temperature gas. The high-temperature gas diffuses upward, accelerating the rise in temperature in the shell 1.

[0059] At the same time, the design of the dehumidification component in the present device is that when the gas flows through the dehumidification box, the water vapor in the gas is absorbed by the silica gel particles, and then the dry gas re-enters the shell 1, thereby achieving the effect of dehumidifying the inside of the shell 1. Compared with the prior art, the present solution can realize the automated processing of the temperature and humidity in the shell 1, so that the inside of the shell 1 is maintained under suitable experimental conditions, thereby improving the accuracy of the data and reducing the work steps of the experimenter.

[0060] Obviously, the above embodiments are merely examples for the purpose of clear explanation, and are not intended to limit the implementation methods. For those skilled in the art, other different forms of changes or modifications can be made based on the above description. It is not necessary and impossible to list all the implementation methods here. The obvious changes or modifications derived therefrom are still within the scope of protection of the invention.

Claims

1. A cell comparison device for flow cytometric analysis, comprising a housing (1) and a communication module, wherein a fluid flow component (3) and a test component (2) are arranged in the housing (1), wherein the fluid flow component (3) is used to drive cells in a sample flow to pass through the test component (2) in sequence, and the test component (2) is used to collect photoelectric information of laser light after the cells are excited, wherein: The liquid flow component (3) comprises a flow chamber (32), wherein a sheath fluid (35) and a driving component are arranged in the flow chamber (32), wherein the driving component is used to drive the sheath fluid (35) to flow, wherein the sheath fluid (35) is used to drive the cells in the sample flow to be arranged in sequence, and wherein a side channel (33) is also arranged in the flow chamber (32), wherein the side channel (33) is used to divert the sample flow, and wherein an output end of the side channel (33) is connected to an output end of the flow chamber (32); The system also includes a control system, which is used to obtain basic information of cells in samples in the flow chamber (32), at the output end of the flow chamber (32) and in the side channel (33) based on the photoelectric information, and calculate the similarity between the sum of the basic information of cells in the sample in the flow chamber (32) and the sample flow in the side channel (33) and the basic information of cells in the sample at the output end of the flow chamber (32). When the similarity is lower than a preset value, the data reliability is insufficient, and the control communication module outputs the basic information of cells at the output end of the flow chamber (32) to the user and outputs a prompt message. When the similarity is greater than or equal to the preset value, the data is reliable, and the control communication module outputs the basic information of cells at the output end of the flow chamber (32) to the user.

2. The cell comparison device for flow cytometric analysis according to claim 1, characterized in that: Two electric fields with opposite electrodes are arranged in the flow chamber (32), and both electric fields are used to generate electric charges in the cells in the flow chamber (32). A deflection plate (31) is arranged in the housing (1), and the deflection plate (31) is used to drive the charged cells to move.

3. The cell comparison device for flow cytometric analysis according to claim 2, characterized in that: The test component (2) comprises a laser light source (23), a lens (22) and a light detector (21), wherein the laser light source (23) is used to generate laser light, and the light detector (21) is used to receive the laser light beam after cell excitation and generate a corresponding photoelectric signal.

4. The cell comparison device for flow cytometric analysis according to claim 3, characterized in that: A shock absorbing component is also provided in the housing (1), and the shock absorbing component is used to adjust the relative position between the test component (2) and the output end of the flow chamber (32). The control system is used to determine whether the sample flow at the output end of the flow chamber (32) intersects with the laser according to the cell basic information, and to control the shock absorbing component to operate only when the sample flow does not intersect with the laser.

5. The cell comparison device for flow cytometric analysis according to claim 4, characterized in that: The laser light source (23) and the light detector (21) are both provided with a shock-absorbing layer made of elastic material, and the shock-absorbing layer is used to absorb vibrations generated when the laser light source (23) and the light detector (21) are working.

6. The cell comparison device for flow cytometric analysis according to claim 5, characterized in that: The control system comprises a controller, which is used to obtain basic information of cells in samples in a flow chamber (32), at an output end of the flow chamber (32) and in a side channel (33) according to photoelectric signals collected by a light detector, and calculate the similarity between the sum of the basic information of cells in the sample in the flow chamber (32) and the sample flow in the side channel (33) and the basic information of cells in the sample at the output end of the flow chamber (32); when the similarity is lower than a preset value, the data reliability is insufficient, and the communication module is controlled to output the basic information of cells at the output end of the flow chamber (32) to the user and output a prompt message; when the similarity is greater than or equal to the preset value, the data is reliable, and the communication module is controlled to output the basic information of cells at the output end of the flow chamber (32) to the user; the controller is also used to determine whether the laser and the sample flow intersect according to the basic information of the cells, and control the damping component to work only when the sample flow does not intersect with the laser.

7. The cell comparison device for flow cytometric analysis according to claim 6, characterized in that: The control system also includes a temperature sensor and a humidity sensor, the temperature sensor being used to collect temperature information within the housing (1), the humidity sensor being used to collect humidity information within the housing (1), and the controller being used to control the communication module to alarm the user when the temperature information is not within a preset optimal temperature range, and to control the communication module to alarm the user when the humidity information is greater than a preset maximum humidity.

8. The cell comparison device for flow cytometric analysis according to claim 7, characterized in that: The housing (1) is connected to a pump assembly, which is used to drive the gas flow inside the housing (1), and the controller controls the operation of the pump assembly according to temperature information.

9. The cell comparison device for flow cytometric analysis according to claim 8, characterized in that: A heating wire is arranged in the shell (1), and the heating wire is used to heat the gas in the shell (1). The controller controls the operation of the heating wire and the pump assembly according to temperature information.

10. The cell comparison device for flow cytometric analysis according to claim 9, characterized in that: A dehumidification component is provided at the connection point between the housing (1) and the pump component, and the dehumidification component is used to remove moisture from the gas flowing through.

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