Multi-channel detection device of flow cytometer

Abstract

The invention provides a flow cytometer multichannel detection device, which comprises a positive lens, a dichroic filter, a plane mirror and a detection assembly, and is characterized in that the positive lens is used for receiving an optical signal generated when laser irradiates on to-be-detected particles or cells, and adjusting the optical signal into a collimated light beam; the dichroic optical filter is arranged on one side of the positive lens in the horizontal direction and is used for separating the collimated light beam into transmission light and reflected light according to the wavelength; the plane mirror is arranged on one side of the dichroic optical filter in the vertical direction and is used for reflecting the reflected light again to enable the reflected light to be parallel to the transmitted light; the detection assembly comprises a first detection module used for receiving the reflected light and a second detection module used for receiving the transmitted light. A collimated light beam is divided into two parts of transmission light and reflected light by using a dichroic optical filter, so that the number of detection channels in a limited collimation distance is doubled, and the optical path design of multiple detection channels is met.

Description

Technical Field

[0001] The present invention relates to the technical field of cell detection, and particularly relates to a multi-channel detection device for a flow cytometer. Background Art

[0002] A flow cytometer is usually configured with one or more lasers, and each laser corresponds to a detection module. The laser beam emitted by the laser is shaped and then used to detect the particles or cells to be measured at the detection position. Among them, the particles or cells to be measured are pre-treated such as immunological reaction and staining, and are provided with fluorescent dyes that can be excited by the laser. When the particles or cells to be measured flow through the detection position, they are irradiated by the laser, generating scattered light signals and fluorescent signals. The scattered light signals and fluorescent signals are collected by the objective lens and directly transmitted to the detection module. In the detection module, generally, a lens is first used to collimate the light beam within a limited distance, and then spectral separation is performed through a series of dichroic filters and band-pass filters, so that the light beam corresponding to the wavelength is focused by the lens and irradiated on the photosensitive area of the corresponding detector.

[0003] Generally, the incident angle of the dichroic filter is 45 degrees, and the incident angle of the band-pass filter is 0 degrees. There are mainly the following two common existing spectral separation methods: The first is that the collimated light beam passes through the dichroic filter multiple times and then passes through the band-pass filter, and is focused on the photosensitive area of the detector through the focusing lens; the second is that the collimated light beam is reflected by the dichroic filter multiple times and then passes through the band-pass filter, and is focused on the photosensitive area of the detector through the focusing lens. However, no matter which method is used, when multiple detection channels are required, such as the detection module corresponding to each laser of a spectral flow cytometer may require 16 - 20 detection channels. No matter which detector is used, within the limited collimation distance, the optical path design of so many detection channels cannot be realized through the existing spectral separation methods. The main reason is that interference may occur in the structure. With the accumulation of optical aberrations, in the detection channels at the back of the optical path, the light beam cannot all be focused within the photosensitive area of the detector, resulting in a sharp decline in the product performance. Summary of the Invention

[0004] Based on this, the purpose of the present invention is to provide a multi-channel detection device for a flow cytometer to solve the technical problems mentioned in the background art.

[0005] The present invention provides a multi-channel detection device for a flow cytometer, including:

[0006] A positive lens, which is used to receive the optical signal generated when the laser irradiates the particles or cells to be measured, and adjust it into a collimated light beam;

[0007] A dichroic filter, the dichroic filter is arranged on one side in the horizontal direction of the positive lens, and the dichroic filter is used to separate the collimated light beam into transmitted light and reflected light according to the wavelength;

[0008] A plane mirror is disposed on one side in the vertical direction of the dichroic filter. The plane mirror is configured to reflect the reflected light again to make it parallel to the transmitted light.

[0009] A detection assembly, the detection assembly includes a first detection module for receiving the reflected light and a second detection module for receiving the transmitted light.

[0010] Furthermore, for the flow cytometer multi-channel detection device, wherein the first detection module includes a plurality of detection channels arranged in parallel. The first detection channel is configured to receive the reflected light from the plane mirror and separate the reflected light according to the wavelength magnitude, so that the reflected light within a preset wavelength range is used for detection, while the reflected light outside the preset wavelength range is reflected into the adjacent next set of detection channels, and so on.

[0011] Furthermore, for the flow cytometer multi-channel detection device, wherein the detection channel includes a concave mirror, and a band-pass filter, a focusing lens and a detector sequentially and spaced apart on one side of the concave mirror.

[0012] Furthermore, for the flow cytometer multi-channel detection device, wherein the optical path from the image-side principal plane of the positive lens to the first concave mirror is the collimation distance. In each detection channel, the optical path from the concave mirror to the band-pass filter is half of the collimation distance, and the optical path from the band-pass filter in one detection channel to the concave mirror in the adjacent next detection channel is also half of the collimation distance.

[0013] Furthermore, for the flow cytometer multi-channel detection device, wherein in each detection channel, the concave curvature radius of the concave mirror is the same, and the size of the concave curvature radius is equal to the collimation distance.

[0014] Furthermore, for the flow cytometer multi-channel detection device, wherein in each detection channel, the concave curvature radius of the concave mirror is different. As the optical path extends backward, the subsequent concave mirrors adaptively increase or decrease their respective concave curvature radii according to aberration.

[0015] Furthermore, for the flow cytometer multi-channel detection device, wherein the first detection module further includes an attenuation sheet, and the attenuation sheet is disposed between the band-pass filter and the focusing lens.

[0016] Furthermore, for the flow cytometer multi-channel detection device, wherein in the first detection channel, the optical path from the band-pass filter to the focusing lens is greater than or equal to half of the collimation distance.

[0017] Further, in the flow cytometer multi-channel detection device, the optical path from the band-pass filter to the focusing lens in one detection channel is greater than the optical path from the band-pass filter to the focusing lens in the next adjacent detection channel, so that the detectors in each detection channel can be aligned on the same plane.

[0018] Further, in the flow cytometer multi-channel detection device, an optical fiber is provided on a side of the positive lens away from the dichroic filter, and the optical fiber is used to transmit the optical signal generated by the particles or cells to be measured to the positive lens.

[0019] Compared with the prior art, the beneficial effects of the present invention are as follows:

[0020] By using a dichroic filter to first divide the collimated light beam into two parts, namely transmitted light and reflected light, and then performing spectral separation on these two parts of the spectrum by the detection component respectively, the number of detection channels is doubled within a limited collimation distance, meeting the optical path design of multiple detection channels. Description of the Drawings

[0021] Figure 1 It is a schematic diagram of the flow cytometer multi-channel detection device in the present invention;

[0022] Description of the Main Element Marks:

[0023] 01, optical fiber; 02, positive lens; 03, dichroic filter; 04, plane mirror; M01-M20, concave mirror; F01-F20, band-pass filter; S01-S20, attenuation sheet; L01-L20, focusing lens; D01-D20, detector.

[0024] The following specific embodiments will further illustrate the present invention in conjunction with the above-mentioned drawings. Specific Embodiments

[0025] To facilitate the understanding of the present invention, the present invention will be described more comprehensively below with reference to the relevant drawings. Several embodiments of the present invention are given in the drawings. However, the present invention can be implemented in many different forms and is not limited to the embodiments described herein. On the contrary, these embodiments are provided to make the disclosure of the present invention more thorough and comprehensive.

[0026] It should be noted that when an element is referred to as being "fixed to" another element, it can be directly on the other element or there can also be an intermediate element. When an element is considered to be "connected" to another element, it can be directly connected to the other element or there may be an intermediate element at the same time. The terms "vertical", "horizontal", "left", "right" and similar expressions used herein are only for the purpose of illustration.

[0027] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the technical field to which this invention belongs. The terms used in the description of this invention herein are for the purpose of describing specific embodiments only and are not intended to limit the invention. The term "and / or" used herein includes any and all combinations of one or more of the related listed items.

[0028] Please refer to Figure 1 , the flow cytometer multi-channel detection device in the present invention includes a positive lens 02, a dichroic filter 03, a plane mirror 04 and a detection component. The positive lens 02 is used to receive the optical signal generated when the laser irradiates the particles or cells to be measured and adjust it into a collimated beam; the dichroic filter 03 is arranged on one side in the horizontal direction of the positive lens 02, and the dichroic filter 03 is used to separate the collimated beam into transmitted light and reflected light according to wavelength; the plane mirror 04 is arranged on one side in the vertical direction of the dichroic filter 03, and the plane mirror 04 is used to reflect the reflected light again to make it parallel to the transmitted light; the detection component includes a first detection module for receiving the reflected light and a second detection module for receiving the transmitted light.

[0029] By using a single dichroic filter 03 to first divide the collimated beam into two parts, transmitted light and reflected light, and then the detection component separately performs spectral separation on these two parts of the spectrum, the number of detection channels is doubled within a limited collimation distance, meeting the optical path design of multiple detection channels.

[0030] In this embodiment, the dichroic filter 03 is placed at a 45° angle, that is, the incident angle of light is 45°, and the included angle between the reflected light reflected by the dichroic filter 03 and the transmitted light is 90°, that is, the beam direction deflects by 90°. Similarly, in this embodiment, the plane mirror 04 is also placed at a 45° angle, and the reflected light reflected by the dichroic filter 03 is reflected again by the plane mirror 04, and the reflected light deflects by 90° again, so as to be parallel to the transmitted light. Among them, regarding the placement angles of the dichroic filter 03 and the plane mirror 04, this embodiment is only an example rather than a limitation, and can be flexibly adjusted in actual applications as long as the beam reflected by the plane mirror 04 is parallel to the beam transmitted through the dichroic filter 03.

[0031] In addition, it should be noted that the dichroic filter 03 in this embodiment includes but is not limited to a long-pass dichroic filter 03, and can also be a short-pass dichroic filter 03. For the long-pass dichroic filter 03, light with a wavelength greater than the starting response wavelength will pass through, and light with a wavelength less than the starting response wavelength will be reflected. On the contrary, for the short-pass dichroic filter 03, light with a wavelength less than the starting response wavelength will pass through, and light with a wavelength greater than the starting response wavelength will be reflected.

[0032] The first detection module includes a plurality of detection channels arranged in parallel. The first detection channel is configured to receive the reflected light from the planar mirror 04 and separate the reflected light according to the wavelength, so that the reflected light within a preset wavelength range is used for detection, while the reflected light outside the preset wavelength range is reflected into the adjacent next set of detection channels, and so on. Specifically, the detection channel includes a concave mirror, and a band-pass filter, a focusing lens and a detector sequentially and spacedly arranged on one side of the concave mirror. In this embodiment, the first detection module includes concave mirrors M01 to M10, band-pass filters F01 to F10, focusing lenses L01 to L10 and detectors D01 to D10. Among them, the concave mirror M01 is located on one side of the planar mirror 04 in the horizontal direction, and is used to reflect all the light rays emitted from the planar mirror 04 onto the band-pass filter F01 for separation. The light with a wavelength within its bandwidth passes through the band-pass filter F01 and the focusing lens L01 and enters the detector D01 for detection. The light with a wavelength outside its bandwidth is reflected by the band-pass filter F01 to the mirror M02, and then is continuously reflected by the mirror M02 into the adjacent next band-pass filter F02. The band-pass filter F02 performs the same steps as the above band-pass filter F01, and so on.

[0033] In this embodiment, the second detection module has the same structure as the first detection module. Specifically, the second detection module includes concave mirrors M11 to M20, band-pass filters F11 to F20, focusing lenses L11 to L20 and detectors D11 to D20. Among them, the concave mirror M11 is located on one side of the dichroic filter 03 in the horizontal direction, and is used to reflect all the light rays emitted from the dichroic filter 03 onto the band-pass filter F11 for separation. The light with a wavelength within its bandwidth passes through the band-pass filter F11 and the focusing lens L11 and enters the detector D11 for detection. The light with a wavelength outside its bandwidth is reflected by the band-pass filter F11 to the mirror M12, and then is continuously reflected by the mirror M12 into the adjacent next band-pass filter F12. The band-pass filter F12 performs the same steps as the above band-pass filter F11, and so on.

[0034] It can be seen that in this embodiment, the spectrum separation method adopts the method of continuous reflection, which reduces the number of times the light passes through the bandpass filter. For each detection channel, the number of times the light passes through the bandpass filter is only once. Compared with two or more transmissions, the light energy loss is greatly reduced and the detection sensitivity of the system is improved. The reasons are as follows: the transmittance within the bandwidth of the bandpass filter can generally be guaranteed to be greater than 95%, the reflectivity outside the bandwidth can generally be guaranteed to be greater than 99.99%, and the reflectivity of the reflector can generally be guaranteed to be greater than 99.5%. Secondly, using a concave reflector for relaying, the limited collimation distance is extended, and in theory it can be extended forever, that is, there is no upper limit to the number of channels. However, with the accumulation of optical aberrations and manufacturing tolerances, the aberrations of the subsequent channels will become larger and larger, which will cause the spot size focused on the photosensitive area of ​​the detector to exceed the range of the photosensitive area, which limits the upper limit of the number of channels.

[0035] Furthermore, in this embodiment, an optical fiber 01 is provided on the side of the positive lens 02 away from the dichroic filter 03, and the optical fiber 01 is used to transmit the optical signal generated by the particles or cells to be detected to the positive lens 02. It can be understood that the use of the optical fiber 01 not only improves the transmission efficiency of the optical signal, but also makes the structure of the entire system more compact, which is convenient for the layout and adjustment of optical components. Transmitting the optical signal through the optical fiber 01 can avoid the loss and interference of the optical signal when it propagates in the air, ensuring the high sensitivity and stability of the detection module.

[0036] It should be noted that, in the present embodiment, the concave reflectors M01 and M11 are located at the primary image plane position, that is, the light emitted from any point within the core diameter of the optical fiber 01 is focused at this position for the first time. Similarly, if the light is focused for the second time, it is the secondary image plane position, and if the light is focused for the third time, it is the tertiary image plane position, and so on. In the present embodiment, the concave reflectors M03 and M13 are located at the secondary image plane position, the concave reflectors M05 and M15 are located at the tertiary image plane position, the concave reflectors M07 and M17 are located at the quaternary image plane position, and the concave reflectors M09 and M19 are located at the quintic image plane position.

[0037] The optical path from the image side principal surface of the positive lens 02 to the primary image plane position is the collimation distance, the optical path from the concave reflector M01 to the bandpass filter F01 is half of the collimation distance, the optical path from the bandpass filter F01 to the next concave reflector M02 is also half of the collimation distance, and so on.

[0038] The function of the concave reflectors M01 to M20 is to extend the collimation distance, and the size of the concave curvature radius will affect the position of the subsequent image plane.

[0039] In one implementation of this embodiment, the concave mirror M01-M20 has the same concave curvature radius, and at this time, the size of the concave curvature radius is equal to the collimation distance or within a certain tolerance range thereof.

[0040] In another implementation of this embodiment, the concave mirror M01-M20 may also have different concave curvature radii. Taking the concave mirrors M01-M10 as an example, as the optical path extends backward, the subsequent concave mirrors increase or decrease their respective concave curvature radii according to the aberration adaptability to compensate for the accumulation of optical aberrations and ensure that the light beam can be accurately focused within the photosensitive area of the detector. This design can effectively improve the detection accuracy and stability of the system.

[0041] Furthermore, in this embodiment, the concave mirrors M01-M20 and the band-pass filters F01-F20 are placed at a certain angle, and the incident angle of light on the concave mirrors and the band-pass filters is within the range of 5-20 degrees. The concave mirrors M01-M10 are arranged in an array, and all the concave centers are located in the same plane. The band-pass filters F01-F10 are arranged in an array and are located in the same plane. The concave mirrors M11-M20 are arranged in an array, and all the concave centers are located in the same plane. The band-pass filters F11-F20 are arranged in an array and are located in the same plane.

[0042] Optionally, the first detection module further includes an attenuation sheet, and the attenuation sheet is disposed between the band-pass filter and the focusing lens. The main function of the attenuation sheet is to reduce the light intensity when the light intensity is high and the detector is saturated and cannot work normally. There is also a related setting of the attenuation sheet in the second detection module. Specifically, the first detection module includes attenuation sheets S01-S10, and the second detection module includes attenuation sheets S11-S20.

[0043] Specifically, in this embodiment, the light beam passing through the band-pass filter F01 is focused by the focusing lens L01 into the photosensitive area of the detector D01 after passing through the attenuation sheet S01, which is detection channel one;

[0044] The light beam passing through the band-pass filter F02 is focused by the focusing lens L02 into the photosensitive area of the detector D02 after passing through the attenuation sheet S02, which is detection channel two;

[0045] The light beam passing through the band-pass filter F03 is focused by the focusing lens L03 into the photosensitive area of the detector D03 after passing through the attenuation sheet S03, which is detection channel three;

[0046] The light beam passing through the band-pass filter F04 is focused by the focusing lens L04 into the photosensitive area of the detector D04 after passing through the attenuation sheet S04, which is detection channel four;

[0047] The light beam passing through the band-pass filter F05 is attenuated by the attenuator S05 and then focused by the focusing lens L05 into the photosensitive area of the detector D05. This is Detection Channel Five;

[0048] The light beam passing through the band-pass filter F06 is attenuated by the attenuator S06 and then focused by the focusing lens L06 into the photosensitive area of the detector D06. This is Detection Channel Six;

[0049] The light beam passing through the band-pass filter F07 is attenuated by the attenuator S07 and then focused by the focusing lens L07 into the photosensitive area of the detector D07. This is Detection Channel Seven;

[0050] The light beam passing through the band-pass filter F08 is attenuated by the attenuator S08 and then focused by the focusing lens L08 into the photosensitive area of the detector D08. This is Detection Channel Eight;

[0051] The light beam passing through the band-pass filter F09 is attenuated by the attenuator S09 and then focused by the focusing lens L09 into the photosensitive area of the detector D09. This is Detection Channel Nine;

[0052] The light beam passing through the band-pass filter F10 is attenuated by the attenuator S10 and then focused by the focusing lens L10 into the photosensitive area of the detector D10. This is Detection Channel Ten;

[0053] The light beam passing through the band-pass filter F11 is attenuated by the attenuator S11 and then focused by the focusing lens L11 into the photosensitive area of the detector D11. This is Detection Channel Eleven;

[0054] The light beam passing through the band-pass filter F12 is attenuated by the attenuator S12 and then focused by the focusing lens L12 into the photosensitive area of the detector D12. This is Detection Channel Twelve;

[0055] The light beam passing through the band-pass filter F13 is attenuated by the attenuator S13 and then focused by the focusing lens L13 into the photosensitive area of the detector D13. This is Detection Channel Thirteen;

[0056] The light beam passing through the band-pass filter F14 is attenuated by the attenuator S14 and then focused by the focusing lens L14 into the photosensitive area of the detector D14. This is Detection Channel Fourteen;

[0057] The light beam passing through the band-pass filter F15 is attenuated by the attenuator S15 and then focused by the focusing lens L15 into the photosensitive area of the detector D15. This is Detection Channel Fifteen;

[0058] The light beam passing through the band-pass filter F16 is attenuated by the attenuator S16 and then focused by the focusing lens L16 into the photosensitive area of the detector D16. This is Detection Channel Sixteen;

[0059] The light beam passing through the bandpass filter F17 is focused by the focusing lens L17 into the photosensitive area of ​​the detector D17 after passing through the attenuation plate S17. This is the detection channel seventeen.

[0060] The light beam passing through the bandpass filter F18 is focused by the focusing lens L18 into the photosensitive area of ​​the detector D18 after passing through the attenuation plate S18. This is the detection channel 18.

[0061] The light beam passing through the bandpass filter F19 is focused by the focusing lens L19 into the photosensitive area of ​​the detector D19 after passing through the attenuation plate S19. This is the detection channel 19.

[0062] The light beam passing through the bandpass filter F20 is focused by the focusing lens L20 into the photosensitive area of ​​the detector D20 after passing through the attenuation plate S20. This is the detection channel 20.

[0063] In this embodiment, taking the first detection module as an example, the optical path from the bandpass filter F01 to the focusing lens L01 is greater than or equal to half of the collimation distance, ensuring that the light beam does not exceed the effective aperture of the focusing lens.

[0064] In addition, the optical path from the bandpass filter in one detection channel to the focusing lens is greater than the optical path from the bandpass filter in the next adjacent detection channel to the focusing lens, so that the detectors in each detection channel can be aligned in the same plane. Taking the first detection module as an example, the optical path from the bandpass filter F01 to the focusing lens L01 is greater than the optical path from the bandpass filter F02 to the focusing lens L02, and the optical path from the bandpass filter F02 to the focusing lens L02 is greater than the optical path from the bandpass filter F03 to the focusing lens L03, and so on. Specifically, the values ​​that decrease in sequence can be calculated based on the collimation distance and the incident angle of the bandpass filter. The purpose of this design is to make multiple detectors D01~D10 located in the same plane, so that it is convenient to weld or connect multiple detectors on the same circuit board, and the photocurrent can be directly processed. Compared with the switching method, the anti-interference ability is stronger and the structure is simpler.

[0065] It is worth mentioning that as the number of detection channels increases, the distance from the bandpass filter to the focusing lens is constantly shortening, which will limit the upper limit of the number of detection channels. Therefore, the number of detection channels is mainly affected by the collimation distance, the incident angle of the bandpass filter and the size of the detector's photosensitive area. The longer the collimation distance, the smaller the incident angle of the bandpass filter and the larger the size of the detector's photosensitive area, the greater the number of detection channels will be.

[0066] In summary, for the flow cytometer multi-channel detection device in the above embodiments of the present invention, by using a dichroic filter 03 to first divide the collimated light beam into two parts, namely transmitted light and reflected light, and then the detection component performs spectral separation on these two parts of the spectra respectively, the number of detection channels is doubled within a limited collimation distance, meeting the optical path design of multiple detection channels.

[0067] In the description of this specification, the description referring to terms such as "one embodiment", "some embodiments", "example", "specific example", or "some examples", etc. means that the specific features, structures, materials, or characteristics described in connection with the embodiment or example are included in at least one embodiment or example of the present invention. In this specification, the schematic expressions of the above terms do not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials, or characteristics described can be combined in a suitable manner in any one or more embodiments or examples.

[0068] The above-described embodiments only represent several implementation manners of the present invention, and the description is relatively specific and detailed, but it should not be construed as a limitation on the scope of the invention patent of the present invention. It should be noted that for those of ordinary skill in the art, without departing from the concept of the present invention, several modifications and improvements can still be made, and these all belong to the protection scope of the present invention. Therefore, the protection scope of the invention patent of the present invention shall be subject to the appended claims.

Claims

1. A multi-channel flow cytometer detection device, characterized in that: include: A positive lens is used to receive the optical signal generated when the laser irradiates the particles or cells to be detected and adjust it into a collimated beam; A dichroic filter, the dichroic filter is arranged on one side of the positive lens in the horizontal direction, and the dichroic filter is used to separate the collimated light beam into transmitted light and reflected light according to wavelength; A plane reflector, the plane reflector being disposed on one side of the dichroic filter in a vertical direction, and the plane reflector being used to reflect the reflected light again so as to make it parallel to the transmitted light; A detection component includes a first detection module for receiving the reflected light and a second detection module for receiving the transmitted light.

2. The multi-channel flow cytometer detection device according to claim 1, characterized in that: The first detection module includes a plurality of detection channels arranged in parallel. The first detection channel is configured to receive reflected light from the plane reflector and separate the reflected light according to wavelength, so that the reflected light within a preset wavelength range is used for detection, and the reflected light outside the preset wavelength range is reflected to the next adjacent group of detection channels, and so on.

3. The multi-channel flow cytometer detection device according to claim 2, characterized in that: The detection channel comprises a concave reflector, and a bandpass filter, a focusing lens and a detector which are sequentially and spaced apart and arranged on one side of the concave reflector.

4. The multi-channel flow cytometer detection device according to claim 3, characterized in that: The optical path from the image-side principal surface of the positive lens to the first concave reflector is the collimation distance. In each detection channel, the optical path from the concave reflector to the bandpass filter is half of the collimation distance, and the optical path from the bandpass filter in one detection channel to the concave reflector in the next adjacent detection channel is also half of the collimation distance.

5. The multi-channel flow cytometer detection device according to claim 4, characterized in that: In each detection channel, the concave curvature radius of the concave reflector is the same, and the size of the concave curvature radius is equal to the collimation distance.

6. The multi-channel detection device of flow cytometer according to claim 3, characterized in that: In each detection channel, the concave curvature radius of the concave reflector is different. As the optical path extends backward, the subsequent concave reflectors increase or decrease their respective concave curvature radii according to aberration adaptability.

7. The multi-channel flow cytometer detection device according to claim 3, characterized in that: The first detection module further includes an attenuation plate, and the attenuation plate is arranged between the bandpass filter and the focusing lens.

8. The multi-channel detection device of flow cytometer according to claim 4, characterized in that: In the first detection channel, the optical path from the bandpass filter to the focusing lens is greater than or equal to half of the collimation distance.

9. The multi-channel detection device of flow cytometer according to claim 3, characterized in that: The optical path from the bandpass filter to the focusing lens in one detection channel is greater than the optical path from the bandpass filter to the focusing lens in the next adjacent detection channel, so that the detectors in each detection channel can be aligned in the same plane.

10. The multi-channel flow cytometer detection device according to claim 1, characterized in that: An optical fiber is provided on a side of the positive lens away from the dichroic filter, and the optical fiber is used to transmit the optical signal generated by the particles or cells to be detected to the positive lens.

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