Multi-channel miniaturized fluorescence detection module

Abstract

The utility model relates to a multichannel miniaturized fluorescence detection module which comprises a micro-fluidic chip, a light source processing light path and a fluorescence collection detection light path, the light source processing light path and the fluorescence collection detection light path are arranged on two sides above the micro-fluidic chip, and the micro-fluidic chip is provided with an area to be detected; the light source processing light path comprises a transmitting end reflecting mirror and a plurality of excitation light sources with different wave bands, and excitation light emitted by the excitation light sources is arranged in a cascading manner and is reflected to a to-be-detected area of the micro-fluidic chip through the transmitting end reflecting mirror; the fluorescence collection and detection light path comprises a fluorescence collection objective lens group and a plurality of receiving detectors, the fluorescence collection objective lens group collects fluorescence signals with different wavelengths in a to-be-detected area of the micro-fluidic chip, and the plurality of receiving detectors respectively receive the fluorescence signals with different wavelengths output by the fluorescence collection objective lens group. Through the multi-channel design, fluorescence excitation and emission can be simultaneously carried out in a plurality of different wave bands, a plurality of different biomarkers or chemical substances can be simultaneously detected, and the application flexibility and universality are greatly enhanced.

Description

Technical Field

[0001] The utility model belongs to the technical field of biochemical fluorescence detection, and particularly relates to a multi-channel miniaturized fluorescence detection module. Background Art

[0002] In the fields of biomedical research and clinical diagnosis, fluorescence detection technology has been widely used in the detection of various biomarkers due to its high sensitivity and high specificity. This technology mainly relies on the excitation and emission characteristics of fluorescent molecules, and quantitatively analyzes the target molecules in biological samples by measuring the fluorescence intensity at specific wavelengths. However, with the increase in detection requirements and the improvement of sample complexity, traditional single-channel fluorescence detection systems show their limitations in the synchronous analysis of multiple samples and multiple indicators. These systems usually require repeated sample preparation and fluorescence excitation for each channel, resulting in low efficiency and time-consuming and laborious analysis processes.

[0003] In addition, traditional fluorescence detection devices are often bulky, relying on complex optical path designs and expensive optical components. This not only limits their application outside the laboratory but also increases the economic cost of the equipment. Therefore, developing a compact and cost-effective multi-channel fluorescence detection module that can be used in various scenarios such as rapid clinical on-site diagnosis, environmental monitoring, and food safety detection has important practical application value and market potential.

[0004] In view of this, it is particularly important to develop an integrated multi-channel miniaturized fluorescence detection module. Summary of the Utility Model

[0005] The purpose of the utility model is to provide a multi-channel miniaturized fluorescence detection module to solve the limitations of traditional technologies in terms of operation complexity, cost, and application scope.

[0006] To achieve the above purpose, the technical solution adopted by the utility model is: a multi-channel miniaturized fluorescence detection module, including a microfluidic chip, a light source processing optical path and a fluorescence collection and detection optical path arranged on both sides above the microfluidic chip. The microfluidic chip is provided with a region to be detected; the light source processing optical path includes a transmitting end mirror and multiple excitation light sources with different wavelength bands. The excitation light emitted by the multiple excitation light sources is cascaded and reflected by the transmitting end mirror to the region to be detected of the microfluidic chip; the fluorescence collection and detection optical path includes a fluorescence collection objective lens group and multiple receiving detectors. The fluorescence collection objective lens group collects fluorescence signals with different wavelengths in the region to be detected of the microfluidic chip, and the multiple receiving detectors respectively receive the fluorescence signals with different wavelengths output by the fluorescence collection objective lens group.

[0007] Furthermore, multiple excitation light sources are located above the emission end mirror. Along the optical path direction on the light-emitting side of each excitation light source, an excitation collimating mirror, an excitation band-pass filter, and an excitation dichroic mirror are sequentially provided. The excitation dichroic mirror is located directly above the emission end mirror.

[0008] Furthermore, the excitation light source at the uppermost position is arranged directly above the emission end mirror and emits excitation light downward, while the remaining excitation light sources are vertically spaced apart and emit excitation light to the right.

[0009] Furthermore, the projection of the excitation dichroic mirror forms a 45° angle with the horizontal plane.

[0010] Furthermore, multiple receiving detectors are vertically distributed; the fluorescence collection objective lens group outputs fluorescence signals of different wavelengths upward. Above the fluorescence collection objective lens group, multiple emission dichroic mirrors vertically distributed are provided. Above the multiple emission dichroic mirrors, a receiving end mirror is provided. The positions of the receiving end mirror, the multiple emission dichroic mirrors, and the multiple receiving detectors correspond one by one. Along the optical path direction between the receiving end mirror and the receiving detectors and between the correspondingly positioned emission dichroic mirrors and the receiving detectors, an emission band-pass filter and an emission collimating mirror are sequentially provided.

[0011] Furthermore, the projection of the emission dichroic mirror forms a 45° angle with the horizontal plane.

[0012] Furthermore, the microfluidic chip is arranged directly below the fluorescence collection objective lens and is parallel to the horizontal plane.

[0013] Furthermore, the microfluidic chip includes a chip body and microchannels installed on the chip body. The two side edges of the microchannels form boundary grooves on the chip body to define the boundaries of the flow channels; a detection area to be detected is arranged inside the microchannels. The detection area to be detected includes multiple grooves, and each groove contains a paper-based detection unit.

[0014] Furthermore, the material used for the paper-based detection unit is nitrocellulose membrane.

[0015] Compared with the prior art, the present utility model has the following effects: Through the multi-channel design, the present utility model can simultaneously perform fluorescence excitation and emission in multiple different wavelength bands, and can simultaneously detect multiple different biomarkers or chemical substances, greatly enhancing the flexibility and universality of its application; through the miniaturized optical path structure design, the overall volume of the optical module is reduced, and the production cost is lowered. Description of the Drawings

[0016] Figure 1 is a schematic structural diagram of an embodiment of the present utility model;

[0017] Figure 2It is a schematic structural diagram of the light source processing optical path in the embodiment of the present utility model;

[0018] Figure 3 It is a schematic structural diagram of the fluorescence collection and detection optical path in the embodiment of the present utility model.

[0019] In the figure:

[0020] 1 - First excitation light source; 2 - First excitation collimating mirror; 3 - First excitation band - pass filter; 4 - Second excitation band - pass filter; 5 - Second excitation collimating mirror; 6 - Second excitation light source; 7 - Third excitation collimating mirror; 8 - Third excitation light source; 9 - Fourth excitation collimating mirror; 10 - Fourth excitation light source; 11 - Fifth excitation collimating mirror; 12 - Fifth excitation light source; 13 - Sixth excitation collimating mirror; 14 - Sixth excitation light source; 15 - First excitation dichroic mirror; 16 - Second excitation dichroic mirror; 17 - Third excitation band - pass filter; 18 - Third excitation dichroic mirror; 19 - Fourth excitation band - pass filter; 20 - Fourth excitation dichroic mirror; 21 - Fifth excitation band - pass filter; 22 - Fifth excitation dichroic mirror; 23 - Sixth excitation band - pass filter; 24 - Emission - end reflector; 25 - Microfluidic chip; 26 - Fluorescence collection objective lens group; 27 - First emission band - pass filter; 28 - First emission dichroic mirror; 29 - Second emission band - pass filter; 30 - Second emission dichroic mirror; 31 - Third emission band - pass filter; 32 - Third emission dichroic mirror; 33 - Fourth emission band - pass filter; 34 - Fourth emission dichroic mirror; 35 - Fifth emission band - pass filter; 36 - Fifth emission dichroic mirror; 37 - Sixth emission band - pass filter; 38 - Receiver - end reflector; 39 - First receiving detector; 40 - First emission collimating mirror; 41 - Second receiving detector; 42 - Second emission collimating mirror; 43 - Third receiving detector; 44 - Third emission collimating mirror; 45 - Fourth receiving detector; 46 - Fourth emission collimating mirror; 47 - Fifth receiving detector; 48 - Fifth emission collimating mirror; 49 - Sixth receiving detector; 50 - Sixth emission collimating mirror; 51 - Area to be detected; 52 - Light source processing optical path; 53 - Fluorescence collection and detection optical path. Detailed implementation manners

[0021] The following further describes the present utility model in detail with reference to the accompanying drawings and specific implementation manners.

[0022] In the description of the present utility model, it should be understood that the orientation or positional relationship indicated by the terms "longitudinal", "transverse", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", etc. is based on the orientation or positional relationship shown in the drawings. It is only for the convenience of describing the present utility model, 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 should not be construed as a limitation to the present utility model.

[0023] As Figures 1 to 3 shown, a multi-channel miniaturized fluorescence detection module of the present utility model includes a microfluidic chip, a light source processing optical path 52 and a fluorescence collection and detection optical path 53 disposed above the microfluidic chip 25. The microfluidic chip 25 is provided with a to-be-detected area 51. The light source processing optical path and the fluorescence collection and detection optical path are distributed left and right. The light source processing optical path includes an emission-end reflector 24 and six excitation light sources with different bands. The excitation light emitted by the six excitation light sources is cascaded and reflected by the emission-end reflector 24 to the to-be-detected area 51 of the microfluidic chip 25. The fluorescence collection and detection optical path 53 includes a fluorescence collection objective lens group 26 and six receiving detectors. The fluorescence collection objective lens group 26 collects fluorescence signals of different wavelengths in the to-be-detected area 51 of the microfluidic chip 25, and the six receiving detectors respectively receive the fluorescence signals of different wavelengths output by the fluorescence collection objective lens group 26.

[0024] In this embodiment, the six excitation light sources are located above the emission-end reflector. Along the optical path direction on the light-emitting side of each excitation light source, an excitation collimating lens, an excitation band-pass filter and an excitation dichroic mirror are sequentially provided. The excitation dichroic mirror is located directly above the emission-end reflector. Further, the excitation light source located at the uppermost part is disposed directly above the emission-end reflector and emits excitation light downward, and the remaining excitation light sources are vertically spaced and emit excitation light to the right. The two excitation light sources located at the uppermost end share one excitation dichroic mirror, that is: the light source processing optical path includes six excitation light sources, one emission-end reflector, six excitation collimating lenses, six excitation band-pass filters and five excitation dichroic mirrors. The light source processing optical path is used to emit excitation light sources and perform collimation and filtering processing on the emitted light sources, and project the excitation light of different target bands into the to-be-detected area of the microfluidic chip by means of cascading of the excitation dichroic mirrors.

[0025] In this embodiment, the projection of the excitation dichroic mirror on the horizontal plane forms an angle of 45°.

[0026] In this embodiment, six excitation light sources are all LEDs, and their wavelength bands respectively cover 370 - 390 nm, 485 - 495 nm, 525 - 535 nm, 585 - 600 nm, 645 - 655 nm, and 670 - 690 nm. The corresponding emission filter is set to ensure that the fluorescence emission spectra of each channel respectively fall within 410 - 440 nm, 510 - 530 nm, 560 - 580 nm, 610 - 650 nm, 675 - 690 nm, and 705 - 730 nm. This design ensures efficient spectral separation and accurate target detection.

[0027] Specifically: The light source processing optical path includes a first excitation light source 1, a second excitation light source 6, a third excitation light source 8, a fourth excitation light source 10, a fifth excitation light source 12, and a sixth excitation light source 14 arranged in sequence from top to bottom; a first excitation collimating mirror 2, a second excitation collimating mirror 5, a third excitation collimating mirror 7, a fourth excitation collimating mirror 9, a fifth excitation collimating mirror 11, and a sixth excitation collimating mirror 13 arranged in sequence from top to bottom; a first excitation band - pass filter 3, a second excitation band - pass filter 4, a third excitation band - pass filter 17, a fourth excitation band - pass filter 19, a fifth excitation band - pass filter 21, and a sixth excitation band - pass filter 23 arranged in sequence from top to bottom; a first excitation dichroic mirror 15, a second excitation dichroic mirror 16, a third excitation dichroic mirror 18, a fourth excitation dichroic mirror 20, a fifth excitation dichroic mirror 22, and an emission - end reflecting mirror 24 arranged in sequence from top to bottom. Among them, the first excitation light source 1, the first excitation collimating mirror 2, and the first excitation band - pass filter 3 form a channel; the second excitation light source 6, the second excitation collimating mirror 5, and the second excitation band - pass filter 4 form a channel; the third excitation light source 8, the third excitation collimating mirror 7, and the third excitation band - pass filter 17 form a channel; the fourth excitation light source 10, the fourth excitation collimating mirror 9, and the fourth excitation band - pass filter 19 form a channel; the fifth excitation light source 12, the fifth excitation collimating mirror 11, and the fifth excitation band - pass filter 21 form a channel; the sixth excitation light source 14, the sixth excitation collimating mirror 13, and the sixth excitation band - pass filter 23 form a channel. The excitation light sources of the six channels are combined through the first, second, third, fourth, and fifth excitation dichroic mirrors into the emission - end reflecting mirror, and are projected through the emission - end reflecting mirror onto the area to be detected of the microfluidic chip. Particularly, the angle between the emission - end reflecting mirror and the plane where the microfluidic chip is located changes according to different working distances to meet the irradiation requirements.

[0028] In this embodiment, in the microfluidic chip, when the excitation beam irradiates the area to be detected on the chip, the sample in this area will produce a fluorescence reaction under the excitation of the excitation light in the target band. This fluorescence reaction is excited by the response of specific components in the sample to the laser light source, and the changes in its brightness and color can be used to analyze and identify various biological or chemical substances in the sample. The paper-based detection unit in the microfluidics will capture the fluorescence emitted by the sample to be detected. By integrating microfluidic technology with multi-channel fluorescence detection technology, not only can the limitations of traditional technologies in terms of operation complexity, cost, and application scope be solved, but also a more efficient and accurate analysis tool can be brought to scientific research and clinical diagnosis.

[0029] It should be noted that the microfluidic chip is a mature existing product and has been widely used in the field of biological analysis because it can achieve precise manipulation of trace reagents and samples. The microfluidic system can integrate multiple experimental steps, such as mixing, reaction, separation, and detection, on a single chip, greatly improving the automation level and repeatability of the experiment. By adopting the microfluidic chip in this embodiment, rapid detection of multi-channel fluorescence signals can be carried out simultaneously on a single platform, not only significantly improving the detection efficiency, but also enabling rapid analysis of multiple samples or multiple indicators on the basis of ensuring high sensitivity and high specificity.

[0030] In this embodiment, six receiving detectors are distributed vertically; the fluorescence collection objective lens group outputs fluorescence signals of different wavelengths upward. There are five emission dichroic mirrors distributed vertically directly above the fluorescence collection objective lens group. A receiving end mirror is arranged directly above the five emission dichroic mirrors. The positions of one receiving end mirror, five emission dichroic mirrors, and five receiving detectors correspond one by one. Along the optical path direction, an emission band-pass filter and an emission collimating mirror are successively arranged between the receiving end mirror and the receiving detector, and between the correspondingly positioned emission dichroic mirror and the receiving detector, that is: the fluorescence collection and detection optical path includes one fluorescence collection objective lens group, six receiving detectors, five emission dichroic mirrors, one receiving end mirror, six emission band-pass filters, and six emission collimating mirrors. The fluorescence collection and detection optical path is used to collect and analyze the fluorescence signals on the area to be detected of the microfluidic chip, and transmit the fluorescence signals of different bands to different receiving detectors for detection and analysis through the emission dichroic mirrors.

[0031] In this embodiment, the projection of the emission dichroic mirror on the horizontal plane forms an angle of 45°.

[0032] Specifically: The fluorescence collection and detection optical path includes a fluorescence collection objective lens group 26, a first emission dichroic mirror 28, a second emission dichroic mirror 30, a third emission dichroic mirror 32, a fourth emission dichroic mirror 34, a fifth emission dichroic mirror 36, and a receiving end mirror 38 arranged successively from bottom to top, a first emission band-pass filter 27, a second emission band-pass filter 29, a third emission band-pass filter 31, a fourth emission band-pass filter 33, a fifth emission band-pass filter 35, and a sixth emission band-pass filter 37 arranged successively from bottom to top, a first emission collimator 40, a second emission collimator 42, a third emission collimator 44, a fourth emission collimator 46, a fifth emission collimator 48, and a sixth emission collimator 50 arranged successively from bottom to top, and a first receiving detector 39, a second receiving detector 41, a third receiving detector 43, a fourth receiving detector 45, a fifth receiving detector 47, and a sixth receiving detector 49 arranged successively from bottom to top. Among them, the first emission band-pass filter 27, the first emission collimator 40, and the first receiving detector 39 form a fluorescence collection and detection channel, the second emission collimator 42, the second emission collimator, and the second receiving detector form a fluorescence collection and detection channel, the third emission collimator, the third emission collimator, and the third receiving detector form a fluorescence collection and detection channel, the fourth emission collimator, the fourth emission collimator, and the fourth receiving detector form a fluorescence collection and detection channel, the fifth emission collimator, the fifth emission collimator, and the fifth receiving detector form a fluorescence collection and detection channel, and the sixth emission collimator, the sixth emission collimator, and the sixth receiving detector form a fluorescence collection and detection channel. The fluorescence generated by the fluorescence reaction is collected by the collection objective lens group and transmitted to the first, second, third, fourth, and fifth emission dichroic mirrors and the receiving end mirror, and is respectively guided to the first, second, third, fourth, fifth, and sixth emission filters for filtering. Among them, the band-pass filter in each fluorescence collection and detection optical path is perpendicular to the optical axis direction, used to screen the fluorescence signal of the substance to be measured and filter out stray light. Finally, the fluorescence signal is converged on the first, second, third, fourth, fifth, and sixth receiving detectors through the first, second, third, fourth, fifth, and sixth emission collimators in each detection channel. The detector converts the collected optical signal into an electrical signal and further processes it into a digital signal for output.

[0033] In this embodiment, the microfluidic chip is disposed directly below the fluorescence collection objective lens and is arranged parallel to the horizontal plane.

[0034] In this embodiment, the microfluidic chip includes a chip body and microchannels installed on the chip body. The two side edges of the microchannels form boundary grooves on the chip body to define the boundaries of the channels. A region to be detected is provided inside the microchannels. The region to be detected includes a plurality of grooves, and a paper-based detection unit is placed in each groove. Further, a square groove is provided at the center of the region to be detected, and a paper-based detection unit is placed in the square groove. A target substance in the sample is fixed on the paper-based detection unit. The material used for these paper-based detection units is nitrocellulose membrane.

[0035] This detection module can simultaneously perform fluorescence excitation and emission in six different bands. Through the design of a miniaturized optical path structure, the overall volume of the optical module is reduced, greatly improving the ability of multi-component analysis and the detection sensitivity. A dichroic mirror and band-pass filters are arranged on the optical path to perform secondary filtering on the excitation light, effectively reducing stray light and reducing the interference of background noise during the detection process of the oblique-incidence optical system. By globally detecting the microfluidic chip, quantitative analysis of low-concentration samples to be detected is achieved.

[0036] In another embodiment, the high-performance microprocessor built into the module instantaneously processes and analyzes the received fluorescence signals. Through digital control, the intensity of the excitation light and the response time can be adjusted to optimize the detection conditions.

[0037] Embodiment:

[0038] The first, second, third, fourth, fifth, and sixth excitation light sources emit monochromatic lights corresponding to different wavelengths. After passing through the first, second, third, fourth, fifth, and sixth excitation collimating mirrors respectively, they are vertically incident on the first, second, third, fourth, fifth, and sixth excitation band-pass filters. After further filtering the stray light in the excitation light source by the band-pass filters, the monochromatic lights of different wavelengths in each channel are combined and output to the emission end mirror through the first, second, third, fourth, and fifth excitation dichroic mirrors. Subsequently, they irradiate the region to be detected in the microfluidic chip. After exciting the sample to be detected, the fluorescence signals of different wavelengths are collected and collimated by the fluorescence collection objective lens group and then transmitted to the first, second, third, fourth, and fifth emission dichroic mirrors and the receiving end mirror respectively, and are transmitted to different detection channels respectively. Subsequently, after filtering the stray light by the first, second, third, fourth, fifth, and sixth emission band-pass filters and passing through the first, second, third, fourth, and fifth emission focusing mirrors respectively, they are incident on the first, second, third, fourth, fifth, and sixth receiving detectors respectively. After the receiving detectors convert the optical signals into electrical signals, they are finally output to the user interface as digital signals.

[0039] The advantages of the present utility model are as follows:

[0040] (1)Multi-channel design: The six-channel design enables the detection module to perform multiple tests simultaneously, thus significantly improving throughput and efficiency. For the need to monitor multiple biomarkers or chemicals simultaneously, this can greatly reduce the required time and complexity.

[0041] (2)Miniaturization and portability: The miniaturized design means that the device not only occupies a small space but is also easy to carry, which enables it to be applied in environments outside the laboratory, such as on-site rapid diagnosis, environmental monitoring, or medical applications in remote areas, greatly expanding its application scope.

[0042] (3)Cost-effectiveness: Since multi-channel detection can be carried out on one device, compared with single-channel devices, the need for repeated purchases can be reduced, thus lowering the equipment investment and maintenance costs. In addition, such an integrated system can also save the usage of reagents and other experimental materials, further reducing the operating costs.

[0043] (4)Ease of operation: The design of integrating multiple detection channels simplifies the operation process. Users can complete multiple detection tasks without frequently replacing the device or components, which not only improves the convenience of experimental operation but also reduces the possibility of operation errors.

[0044] (5)Flexibility and scalability: The six-channel design provides higher flexibility. Users can configure and optimize the use of each channel according to needs to adapt to different experimental conditions and requirements. This design also facilitates future technological upgrades, such as adding more detection channels or integrating other types of biological / chemical detection functions.

[0045] Through the above technical solutions, the six-channel fluorescence detection module of the present utility model can effectively support the multi-parameter analysis of complex samples, which has important practical and commercial values for improving the overall performance and application scope of the microfluidic system.

[0046] In any of the technical solutions disclosed by the present utility model above, the terms used to represent the positional relationship or shape, unless otherwise stated, include states or shapes that are approximate, similar, or close thereto.

[0047] Any component provided by the present utility model can either be assembled from multiple separate components or be a single component manufactured by an integral forming process.

[0048] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and are not intended to limit them; although the present invention has been described in detail with reference to the preferred embodiments, those of ordinary skill in the art should understand that: it is still possible to modify the specific implementation manners of the present invention or perform equivalent replacements for some technical features; without departing from the spirit of the technical solutions of the present invention, they should all be covered within the scope of the technical solutions claimed by the present invention.

Claims

1. A multi-channel miniaturized fluorescence detection module, characterized in that: The invention comprises a microfluidic chip, a light source processing optical path and a fluorescence collection and detection optical path arranged on both sides above the microfluidic chip, wherein the microfluidic chip is provided with an area to be detected; the light source processing optical path comprises a transmitting end reflector and a plurality of excitation light sources with different wavelengths, and the excitation light emitted by the plurality of excitation light sources is cascaded and reflected to the area to be detected of the microfluidic chip through the transmitting end reflector; the fluorescence collection and detection optical path comprises a fluorescence collection objective lens group and a plurality of receiving detectors, the fluorescence collection objective lens group collects fluorescence signals of different wavelengths of the area to be detected of the microfluidic chip, and the plurality of receiving detectors respectively receive fluorescence signals of different wavelengths output by the fluorescence collection objective lens group.

2. A multi-channel miniaturized fluorescence detection module according to claim 1, characterized in that: A plurality of excitation light sources are located above the reflector at the emission end. The light emitting side of each excitation light source is provided with an excitation collimator, an excitation bandpass filter and an excitation dichroic mirror in sequence along the light path direction. The excitation dichroic mirror is located directly above the reflector at the emission end.

3. A multi-channel miniaturized fluorescence detection module according to claim 2, characterized in that: The excitation light source located at the top is arranged directly above the reflector at the emission end and emits the excitation light downward, and the remaining excitation light sources are distributed at intervals in the vertical direction and emit the excitation light to the right.

4. The multi-channel miniaturized fluorescence detection module according to claim 2, characterized in that: The projection of the excitation dichroic mirror to the horizontal plane forms an angle of 45°.

5. The multi-channel miniaturized fluorescence detection module according to claim 1, characterized in that: A plurality of receiving detectors are distributed vertically; the fluorescence collecting objective lens group outputs fluorescence signals of different wavelengths upwards; a plurality of emission dichroic mirrors distributed vertically are arranged directly above the fluorescence collecting objective lens group; a receiving end reflector is arranged directly above the plurality of emission dichroic mirrors; the positions of the receiving end reflector, the plurality of emission dichroic mirrors and the plurality of receiving detectors correspond one to one; emission bandpass filters and emission collimating mirrors are arranged in sequence along the optical path direction between the receiving end reflector and the receiving detector, and between the emission dichroic mirrors and the receiving detectors at corresponding positions.

6. The multi-channel miniaturized fluorescence detection module according to claim 5, characterized in that: The projection of the emission dichroic mirror to the horizontal plane forms an angle of 45°.

7. The multi-channel miniaturized fluorescence detection module according to claim 1, characterized in that: The microfluidic chip is arranged directly below the fluorescence collecting objective lens and parallel to the horizontal plane.

8. The multi-channel miniaturized fluorescence detection module according to claim 1, characterized in that: The microfluidic chip includes a chip body and a microchannel installed on the chip body. The two side edges of the microchannel form boundary grooves on the chip body to define the boundaries of the channel. An area to be detected is set inside the microchannel, and the area to be detected includes multiple grooves, and a paper-based detection unit is placed in each groove.

9. The multi-channel miniaturized fluorescence detection module according to claim 8, characterized in that: The material used in the paper-based detection unit is nitrocellulose membrane.

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