Image stream type optical system and image stream type detection device based on array waveguide light receiving

Abstract

An image streaming optical system based on array waveguide light reception is characterized by comprising: an array light field generation unit for generating array light fields in a prescribed spatial distribution for each of at least one laser beam, and forming an array light field group from a plurality of array light fields corresponding to each laser beam; a fluid focusing unit that focuses a biological particle sample, and shapes fluorescently labeled biological particles dispersed in the biological particle sample into a single particle flow at least in a detection region of the fluid focusing unit, i.e., a region irradiated by the array light field group; and an array waveguide light receiving unit that is provided with an array waveguide group comprising a plurality of array waveguides corresponding to the plurality of array light fields one by one, and that collects, by means of each of the plurality of array waveguides, light signals relating to the corresponding array light fields when a biological microparticle sample flows through the detection region. The optical signal contains a fluorescent component and a non-fluorescent component.

Description

Technical Field

[0001] This application relates to the field of image streaming detection technology based on arrayed waveguide light collection, and more particularly to an image streaming optical system based on arrayed waveguide light collection and an image streaming optical system using the multi-channel laser for image streaming detection. Background Technology

[0002] Flow cytometry, represented by flow cytometers, has been widely used in biological research and clinical applications. Flow cytometry devices can analyze biological particles such as cells, nucleic acids, and proteins at extremely high throughput, playing a vital role in scientific research fields such as biology and the pharmaceutical industry. However, traditional spectroscopic flow cytometry devices can only detect fluorescence signals, lacking morphological information of biological particles, and previously could only be used in conjunction with fluorescence microscopy for imaging. The low throughput of fluorescence microscopy, however, created a bottleneck in detection efficiency.

[0003] Imaging flow cytometry is an emerging flow cytometry technology that, based on traditional spectral flow cytometry, images each biological particle flowing at high speed through the detection area to obtain microscopic images. It overcomes the limitation of traditional spectral flow cytometry in obtaining images, and while maintaining the high throughput advantage of spectral flow cytometry, it greatly improves the efficiency of scientific research and clinical diagnosis by leveraging rich morphological information of biological particles.

[0004] With the continuous development of flow cytometry technology for detecting microparticles in organisms, the array laser imaging technology, which combines image flow cytometry and spectral flow cytometry, has further broadened the information dimension (see Patent Documents 1 to 3). However, in the application of multi-laser image flow cytometry detection devices, the fluorescence signals between multiple lasers are prone to crosstalk, and the spatial size of the laser spot is relatively large, making it impossible to use small-sized, low-cost detectors such as APDs for detection. The imaging quality and signal-to-noise ratio in multi-laser application scenarios are severely limited.

[0005] References Patent documents Patent Document 1: CN116046649A Patent Document 2: CN113624666A Non-patent literature Han Y , Zhao J , Chao Z ,et al.Imaging flow cytometry using lineararray spot excitation[J].Device, 2023, 1(6):100124.DOI:10.1016 / j.device.2023.100124.. Summary of the Invention

[0006] To address the aforementioned issues in the prior art, the purpose of this application is to provide an image streaming detection technology based on arrayed waveguide light collection, particularly an image streaming technology based on multi-channel laser light collection using arrayed waveguide light collection. This technology effectively avoids crosstalk between fluorescence signals from multiple lasers and resolves the contradiction between the large spatial size of the laser spot and the size limitation of the detector, thereby achieving high-throughput, high-resolution, and low-noise detection and analysis of biological particles.

[0007] According to one aspect of the present invention, an image streaming optical system based on arrayed waveguide light collection is characterized by comprising: An array light field generating unit generates an array light field with a specified spatial distribution for each of at least one laser beam, and the array light field group consists of multiple array light fields corresponding to each laser beam. A fluid focusing unit focuses a biological particle sample, at least within its detection area, shaping the dispersed fluorescently labeled biological particles into a single particle stream. The detection area of ​​the fluid focusing unit refers to the region irradiated by the array light field. The array waveguide light receiving unit comprises an array waveguide group consisting of multiple array waveguides that correspond one-to-one with the multiple array light fields. The array waveguides collect light signals related to the corresponding array light fields when biological particle samples flow through the detection area. The light signals contain fluorescent and non-fluorescent components.

[0008] According to the present invention, multi-channel laser image streaming detection can be realized. Furthermore, since the array optical field of each laser is received by a corresponding array waveguide, signal crosstalk between multiple lasers can be effectively avoided.

[0009] Preferably, in the array light field generating unit, the array light field generated by each of at least one laser beam consists of multiple array light spots irradiating the detection area.

[0010] According to the present invention, a large spatial spot can be divided into an array of smaller spatial spots, thereby enabling detection using a small-sized, low-cost detector such as an APD.

[0011] Preferably, in the arrayed waveguide receiving unit, each arrayed waveguide has multiple sub-waveguides and a main waveguide, and the multiple sub-waveguides correspond one-to-one with multiple array light spots in the corresponding array optical field. Optical signals collected by multiple sub-waveguides of the same array waveguide converge into the total waveguide of the array waveguide, serving as the optical signal corresponding to that laser path.

[0012] According to the present invention, detection can be performed using small-sized, low-cost detectors such as APDs by using arrayed light spots with relatively small spatial dimensions. Furthermore, by using sub-waveguides corresponding to each arrayed light spot to collect the optical signal of each scattered light spot into a separate sub-waveguide (optical fiber), crosstalk between different laser beams can be effectively avoided. Moreover, the configuration of multiple sub-waveguides leading to a total waveguide solves the problem of difficulty in collecting the optical signal from the arrayed light spots.

[0013] Preferably, in the array of light fields, each of the plurality of array light fields is arranged in any one of the following arrangements: staggered arrangement, single arrangement, or mixed arrangement. The term "interlaced arrangement" refers to the fact that multiple array spots of the array light field are interlaced with multiple scattered spots of other array light fields along the flow direction of the biological particle sample. The term "single arrangement" refers to the fact that the array light spots of this array light field do not intersect with the array light spots of other array light fields in the flow direction of the biological particle sample. The hybrid arrangement refers to the fact that some of the array light fields in the multiple array light fields are arranged in an alternating manner, while the remaining array light fields are arranged in a single manner.

[0014] According to the present invention, the light-gathering range of the array waveguide light-gathering unit can be fully utilized, and the arrangement scheme of multiple array light fields can be flexibly determined according to imaging requirements.

[0015] Preferably, for array light fields that prioritize imaging field of view, an alternating arrangement is adopted.

[0016] For array optical fields where detection flux is prioritized, a single arrangement is used.

[0017] Preferably, the total length of the array spot along the flow direction of the biological particles in each of the multiple array light fields is determined according to the requirements of the imaging field of view and the detection throughput.

[0018] According to the present invention, the arrangement scheme of multiple array optical fields can be determined more flexibly to meet the needs of various application scenarios.

[0019] According to the present invention, the arrangement scheme of multiple array optical fields can be flexibly determined according to the two requirements of imaging field of view priority and detection throughput priority.

[0020] Preferably, the array light field generated by each laser is composed of any one of the following: a one-dimensional linear array light spot, a regular two-dimensional array light spot, or a random two-dimensional array light spot illuminating the detection area.

[0021] Preferably, the multiple sub-waveguides of any one of the multiple array waveguides have an arrangement corresponding to the multiple array light spots in the corresponding array optical field.

[0022] Preferably, the fluid focusing unit is a focusing structure based on a flow cell or a focusing structure based on a microfluidic chip. The focusing structure based on the flow cell includes a conical flow cell, a direct current channel, and two symmetrically arranged inlet ports. After the sheath fluid is injected through the inlet ports, it encapsulates the sample to form a single-particle stream. The focusing structure based on the microfluidic chip includes a central channel and two symmetrical microchannels on both sides. After the sheath fluid is injected through the microchannels, the sample is compressed into a single microparticle stream.

[0023] Another aspect of the present invention is an image streaming detection device, comprising: The aforementioned image streaming optical system based on arrayed waveguide light collection; and Optical signal processing system The optical signal processing system includes a beam splitting unit, which separates the optical signal collected by the arrayed waveguide receiving unit into fluorescent and non-fluorescent components, and further separates the fluorescent components into spatially discrete fluorescence spectra according to wavelength.

[0024] According to the present invention, multi-channel laser image streaming detection can be realized. Furthermore, since the array optical field of each laser is received by a corresponding array waveguide, signal crosstalk between multiple lasers can be effectively avoided.

[0025] Preferably, the optical signal processing system further comprises: A photoelectric conversion unit is used to convert the various fluorescence spectra and laser components of the fluorescent component in an optical signal into electrical signals; and The signal processing unit analyzes and processes the electrical signals to generate fluorescence spectral images and label-free images of biological particles. Attached Figure Description

[0026] Figure 1 This is a structural schematic diagram illustrating the overall configuration of the image streaming device of this application.

[0027] Figure 2 This is a schematic diagram illustrating the structure of the array light field generating unit of this application.

[0028] Figure 3 This is a schematic diagram used to illustrate the array optical field of this application.

[0029] Figure 4 This is a schematic diagram illustrating one embodiment of the fluid focusing unit of this application.

[0030] Figure 5 This is a schematic diagram illustrating another embodiment of the fluid focusing unit of this application.

[0031] Figure 6This is a schematic diagram illustrating the array optical field of the multi-channel laser of the array optical field generating unit of this application.

[0032] Figure 7 This is a schematic diagram of an array waveguide group that collects multiple laser beams, used to illustrate the array waveguide light-collecting unit of this application.

[0033] Figure 8 These are diagrams illustrating the arrangement of the array light field of the multi-channel laser in this application. (a) is a diagram illustrating the relationship between the size of the imaging field of view and the arrangement of the array light spots, (b) is a diagram illustrating the staggered arrangement of the array light field, (c) is a diagram illustrating the single arrangement of the array light field, and (d) is a diagram illustrating the mixed arrangement of the array light field.

[0034] Figure 9 This is a diagram used to illustrate the phase difference compensation of the optical signal of each laser in the multi-channel laser of this application.

[0035] Symbol explanation: 100 Image Streaming Optical System 200 Optical Signal Processing System 1. Arrayed light field generating unit 2 Fluid Focusing Unit 3 Arrayed waveguide receiving unit 4 Spectrometers 5 Photoelectric conversion unit 6. Signal Processing Unit 11 Laser source Sub-sources 11a~11c 12 Scattered Array Forming Elements 13 Focusing Lens 21 Conical Flow Pool 22 Input Port 23 DC Channel 24 Detection Area 21' Central runner 22' microchannel 23' Detection area 31 Light-collecting objective lens 32 Condenser objective lens 33 Arrayed Waveguide Group Arrayed waveguides 33a, 33b, and 33c Sub-waveguides 331a, 331b, and 331c 332a, 332b, 332c total waveguide Detailed Implementation

[0036] Various exemplary embodiments of this application are described in detail below with reference to the accompanying drawings. The descriptions of the exemplary embodiments are merely illustrative and are in no way intended to limit the application or its application or use. This application can be implemented in many different forms and is not limited to the embodiments described herein. These embodiments are provided to make the application thorough and complete, and to fully express the scope of the application to those skilled in the art. It should be noted that, unless otherwise stated, the relative arrangement of components and steps, numerical expressions, and values ​​set forth in these embodiments should be interpreted as merely exemplary and not as limiting.

[0037] As used in this application, the words “including” or “comprising” or similar terms mean that the element preceding the word covers the element listed after the word, and do not exclude the possibility that it may also cover other elements.

[0038] All terms used in this application (including technical or scientific terms) have the same meaning as understood by one of ordinary skill in the art to which this application pertains, unless otherwise specifically defined. It should also be understood that terms defined in general dictionaries should be interpreted as having meanings consistent with their meanings in the context of the relevant art, and not as being interpreted with idealized or highly formalized meanings, unless explicitly defined herein.

[0039] For components, specific model numbers and other parameters of components not described in detail in this section, the interrelationships between components and control circuits, these may be considered as techniques, methods and devices known to those skilled in the art, but where appropriate, such techniques, methods and devices should be considered part of the specification.

[0040] Flow cytometry and fluorescence microscopy are two important instruments in scientific research fields such as biology and pharmaceuticals. Flow cytometry can analyze biological particles with extremely high throughput, but it lacks morphological information about these particles. Fluorescence microscopy can acquire morphological information about biological particles, but its throughput remains a bottleneck.

[0041] Imaging flow cytometry combines flow cytometry and fluorescence microscopy, enabling the acquisition of morphological information on biological particles with extremely high throughput. Imaging flow cytometry requires the detection of biological particle samples flowing at speeds on the order of m / s, and currently, single-laser imaging flow cytometry is the mainstream approach. When attempting to apply multi-laser imaging flow cytometry, crosstalk between the fluorescence signals of multiple lasers is common, and the large spatial size of the laser spot prevents the use of small, low-cost detectors such as APDs. This severely limits the imaging quality and signal-to-noise ratio in multi-laser applications.

[0042] This invention aims to realize a multi-laser image streaming detection device, thereby greatly expanding the information dimension.

[0043] Next, embodiments of the present invention will be described in detail with reference to the accompanying drawings. First, refer to... Figure 1 The overall structure of the image flow cytometry detection device of the present invention is described.

[0044] like Figure 1 As shown, the image streaming detection device consists of a front-end image streaming optical system 100 and a back-end optical signal processing system 200. The image streaming optical system 100 uses a laser to irradiate fluorescently labeled biological particles and collects the emitted light signals. These light signals include fluorescent and non-fluorescent components (also known as laser components). Furthermore, the optical signal processing system 200 separates the light signals by wavelength, converts them into electrical signals, and performs subsequent data processing.

[0045] Specifically, the image streaming optical system 100 includes: an array light field generating unit 1, a fluid focusing unit 2, and an array waveguide light receiving unit 3. The optical signal processing system 200 includes: a beam splitting unit 4, a photoelectric conversion unit 5, and a signal processing unit 6. Figure 1 The arrows in the diagram indicate the processing flow. The image streaming optical system 100 can also be referred to as preprocessing, and the optical signal processing system 200 can also be referred to as postprocessing.

[0046] The array light field generating unit 1 generates an array light field with a predetermined spatial distribution for each of at least one laser beam. Here, the present invention does not limit the number of laser beams; multiple laser beams of different wavelengths can be set as needed. Furthermore, in the image streaming optical system 100 equipped with multiple laser beams, combinations of certain laser beams can be selected for activation as needed. The array light fields generated by the multiple laser beams collectively constitute an array light field group, which illuminates the detection area of ​​the fluid focusing unit 2, described in detail later.

[0047] The fluid focusing unit 2 is used to focus the flowing biological particle sample. Specifically, through geometric structural constraints, the flowing biological particle sample is directed to flow in a straight line through the detection area. The detection area is a portion of the area in the fluid focusing unit 2 where the biological particle sample flows in a straight line, and the array of light fields is irradiated onto this detection area.

[0048] It is worth noting that the biological particles referred to in this application include, but are not limited to, cells, nucleic acids, viruses, and proteins. Furthermore, the detection area of ​​the fluid focusing unit 2 is an area that can be irradiated by the array light field. That is, the fluid focusing unit 2 has a straight-line flow channel of a certain length, and a portion of the entire straight-line flow channel suitable for irradiation by the array light field is selected as the detection area of ​​the fluid focusing unit 2.

[0049] The arrayed waveguide receiving unit 3 is used to collect the optical signals generated by biological particles in the microparticle sample after being irradiated by the arrayed light field. The optical signal generated by the laser exciting fluorescently labeled biological particles is called the fluorescent component, while the laser light that is not excited by fluorescently labeled biological particles and is directly transmitted or scattered is called the non-fluorescent component. Because the laser light that is not excited by fluorescently labeled biological particles retains its original wavelength, it is sometimes also called the laser component. The fluorescent component and the laser component are collectively referred to as the optical signal.

[0050] Spectrometer 4 separates the optical signal into fluorescent and laser components, and further separates the fluorescent components into spatially discrete fluorescence spectra. Specifically, when the laser irradiates biological particles, the pre-labeled biological particles are excited, producing fluorescence of various spectra, i.e., fluorescent components. At the same time, the laser not used for fluorescence excitation serves as a non-fluorescent component, used for morphological imaging, i.e., label-free imaging.

[0051] The photoelectric conversion unit 5 is used to convert the various fluorescence spectra and laser components of the fluorescent component in the optical signal into electrical signals.

[0052] The signal processing unit 6 analyzes and processes the electrical signals to generate fluorescence spectral images and label-free images of biological particles for scientific research and clinical diagnosis. Here, label-free images refer to images containing morphological information generated using non-fluorescent components that have not undergone fluorescence excitation, i.e., laser components, such as bright-field images and dark-field images.

[0053] Next, refer to Figures 2-7 Further details on the configuration of each part of the image streaming optical system 100.

[0054] First, based on Figure 2 This paper describes the detailed configuration of the array light field generating unit 1 of the image streaming optical system 100 of this application. For ease of explanation, Figure 2 The example shown is only one instance of generating an array of optical fields with a predetermined spatial distribution based on a single laser beam. Multiple arrays of optical fields generated based on multi-laser distributions follow the same principle.

[0055] like Figure 2 As shown, the array light field generating unit 1 includes a laser source 11, a scatter array forming element 12, and a focusing lens 13. Figure 2 The detection area 24 of the fluid focusing unit 2 is only schematically shown in the figure; other parts of the fluid focusing unit 2 are omitted from the figure.

[0056] Laser source 11 may include sub-sources 11a, 11b, 11c... capable of emitting lasers of multiple wavelengths. Figure 2The diagram only schematically illustrates a sub-source 11a of laser light with one wavelength. The wavelength of the laser can be, for example, 355nm, 375nm, 405nm, 488nm, 530nm, 561nm, 640nm, etc.

[0057] Furthermore, the laser source 11 may not be composed of multiple sub-sources, but rather a multi-purpose laser source capable of emitting lasers of different wavelengths. The laser source 11 can be referenced from embodiments in the prior art, and this application does not specifically limit it thereto.

[0058] The scattered array forming unit 12 is typically a diffraction light source device, with relief structures or nanoscale microstructures fabricated on its surface through microfabrication. When the laser beam generated by the laser source 11 irradiates the surface of the scattered array forming unit 12, it is modulated into multiple beams with a predetermined spatial distribution. For example... Figure 2 As shown, these multiple light beams exhibit a prescribed spatial distribution in the flow direction of biological particles, forming an array of scattered light spots in the detection area 24 of the fluid focusing unit 2, hence also known as an array light field.

[0059] In other words, the scattered array forming unit 12 in this application divides a laser beam into multiple finer beams, thereby forming multiple smaller light spots in the detection area 24. Compared with the scheme of directly illuminating the detection area 24 with a single laser beam, the area of ​​each light spot is smaller, thus enabling the application of small-sized, low-cost detectors such as APDs for detection. Similarly, because the area of ​​each light spot is smaller, crosstalk between lasers of different wavelengths is less likely to occur.

[0060] The scattered array forming unit 12 of this application is not limited to diffractive optical devices, but can also be other optical devices with the same function. This application does not make specific limitations on this.

[0061] The array light field of the laser source 11, after passing through the condenser lens 13, illuminates the focal plane of the focusing lens 13, forming a corresponding array light field. The fluid focusing unit 2 is positioned at the focal plane of the focusing lens 13, thereby forming an array of light spots in the detection area 24. The array light field is used to irradiate the biological microparticle sample stained with a fluorescent dye, exciting the fluorescent component, and generating a non-fluorescent component, i.e., the laser component, under the action of the cells.

[0062] based on Figure 3 The array light field generated by array light field generating unit 1 will be described in further detail. Similarly, for ease of explanation, Figure 3 The example shown is only an example of an array of light fields with a specified spatial distribution generated by a single laser.

[0063] like Figure 3As shown in (a), the array light field generated by the array light field generating unit 1 is projected onto the detection area 24 of the fluid focusing unit 2, thereby forming an array light spot. The array light spot can be a regular two-dimensional array light spot that is equally spaced along the flow direction of the biological particles and randomly arranged in a direction perpendicular to the flow direction of the biological particles. The regular two-dimensional array light spot includes a total of n light spots, which are denoted as light spot 1 to light spot n.

[0064] On the focal plane of focusing lens 13, a Cartesian coordinate system is established with the flow direction of the biological particles as the x-axis, the direction perpendicular to the flow direction of the biological particles as the y-axis, and any point as the origin. Therefore, the coordinates of spot 1 in the regular two-dimensional array of light spots can be determined as (x1, y1), the coordinates of spot 2 can be determined as (x2, y2), and so on, the coordinates of spot n can be determined as (x... n y n Along the flow direction of biological particles, the interval between adjacent spots in a regular two-dimensional array of light spots, that is, the difference Δx between the abscissas of adjacent spots in a regular two-dimensional array of light spots, is equal.

[0065] More specifically, along the flow direction of the biological particles, the interval between spot 2 and spot 1 in the regular two-dimensional array of light spots is Δx. 2-1 =x2-x1, the horizontal distance between spot 3 and spot 2 is Δx 3-2 =x3-x2,Δx 2-1 With Δx 3-2 equal.

[0066] like Figure 3 As shown in (b), the array of light spots can also be one-dimensional linear arrays arranged at equal intervals along a straight line, with a predetermined angle relative to the flow direction of the biological particles. The one-dimensional linear array of light spots is also arranged at equal intervals in the direction perpendicular to the flow direction of the biological particles. That is, the difference Δy between the ordinates of adjacent light spots in the one-dimensional linear array is equal.

[0067] More specifically, perpendicular to the flow direction of the biological particles, the interval between spot 2 and spot 1 in the one-dimensional linear array is Δy. 2-1 =y2-y1, the interval between spot 3 and spot 2 in a one-dimensional linear array is Δy 3-2 =y3-y2,Δy 2-1 with Δy 3-2 equal.

[0068] To ensure that a single biological particle is illuminated by only one light spot at a time, the spacing between adjacent light spots in a regular two-dimensional array or one-dimensional linear array along the flow direction of the biological particles should be greater than the size of the biological particles in the sample. On the other hand, to ensure that every part of a single biological particle is covered by the light spot during flow, the total offset between light spot n and light spot 1 in a regular two-dimensional array or one-dimensional linear array perpendicular to the flow direction of the biological particles should be greater than the size of the biological particles in the sample.

[0069] For example, the biological particles in a sample could be human cells, with common human cell sizes ranging from 20 μm to 30 μm. Therefore, the interval between adjacent light spots along the flow direction of the biological particles, i.e., the difference in the abscissa of adjacent light spots, should be greater than 30 μm. In the direction perpendicular to the flow direction of the biological particles, the total offset between light spot n and light spot 1, i.e., the difference in the ordinate of light spot n and light spot 1, is ΔY = y. n -y1 is greater than 30μm. For a one-dimensional linear array spot, the total offset between spot n and spot 1 in the direction perpendicular to the flow direction of the biological particles can also be expressed as (n-1)Δy.

[0070] When biological particles in a sample pass through a regular two-dimensional array of light spots or a one-dimensional linear array of light spots, sequentially passing through spots 1 to n, the fluorescent markers on the surface or inside the biological particles are excited by each spot in a predetermined order along the flow direction perpendicular to the particles, generating corresponding fluorescent components. By detecting the fluorescent components, the distribution of the fluorescent markers can be encoded in the time domain. By splitting and recombining the fluorescent components in the time domain, an image of the biological particles can be reconstructed. Similarly, non-fluorescent components can be processed in a similar way.

[0071] like Figure 3As shown in (c), the array light field can also be a random two-dimensional array of light spots. A random two-dimensional array of light spots is a series of arrayed light spots randomly and statically distributed within a preset area. When biological particles in a biological particle sample flow through the random two-dimensional array of light spots, the fluorescent markers on the cell surface or inside the cell are excited by each light spot, producing corresponding fluorescent components. The intensity distribution of the fluorescent components is a convolution of the random two-dimensional array of light spot patterns. Based on the known intensity distribution patterns of the light spots, the intensity distribution of the fluorescent components can be determined through deconvolution operations, thereby reconstructing the cell image. Similarly, non-fluorescent components can be processed in a similar way. The process of determining the intensity distribution of the fluorescent components can be performed using algorithms for solving inverse problems in compressed sensing, such as the Two-Step Iterative Shrinkage / Thresholding (TwIST) algorithm, or other algorithms; this application does not specifically limit this.

[0072] Next, based on Figure 4 and Figure 5 Explanation of fluid focusing unit 2. Figure 4 This is a schematic diagram illustrating one embodiment of the fluid focusing unit 2 of this application, showing a fluid focusing unit based on a flow cell. Figure 5 This is a schematic diagram illustrating another embodiment of the fluid focusing unit 2 of this application, showing a fluid focusing unit based on a microfluidic chip.

[0073] like Figure 4 As shown, the fluid focusing unit 2 consists of a conical flow cell 21 and a direct current channel 23. Two approximately symmetrical inlet ports 22 are located on the side wall of the conical flow cell 21. When a biological microparticle sample is injected into the conical flow cell 21, two streams of sheath fluid are injected into the conical flow cell 21 through the two symmetrical inlet ports 22. The sheath fluid can encapsulate the biological microparticle sample flow. After being constrained by the conical flow cell 21, it forms a single-cell axial flow and enters the direct current channel 23, passing through the detection area 24 irradiated by the array light field.

[0074] It can also replace the above Figure 4 The fluid focusing unit 2 based on the flow cell shown adopts... Figure 5 The fluid focusing unit 2 based on a microfluidic chip is shown. Figure 5As shown, the fluid focusing unit 2 includes a central channel 21' and symmetrically positioned microchannels 22' on both sides. Two streams of sheath fluid are injected into the fluid focusing unit 2 through the symmetrical microchannels 22', while the biological particle sample is injected through the central channel 21'. Under the fluid compression of the two streams of sheath fluid, the biological particle sample can be converted into a constant single-cell axial flow and passed through the detection area 23' irradiated by the array light field. By using a microfluidic chip as the fluid focusing unit 2 to focus the biological particle sample, it has the advantage of being fully enclosed and pollution-free. The sheath fluid can be implemented according to related technologies, such as using a balanced electrolyte solution with no fluorescence background; this application does not specifically limit its use.

[0075] In the following description, the fluid focusing unit 2 based on the flow cell will be used as an example.

[0076] Regarding the beam splitting unit 4, photoelectric conversion unit 5, and signal processing unit 6, please refer to the technical solutions in Patent Documents 1 and 2, for example. Since the back-end optical signal processing system 200 is not the focus of this application, detailed descriptions are omitted.

[0077] Next, refer to Figure 6 and Figure 7 Further details are provided on the array optical field generating unit 1 and the array waveguide receiving unit 3. Figure 6 This is a schematic diagram illustrating the array optical field of the multi-channel laser in the array optical field generating unit 1 of this application. Figure 7 This is a schematic diagram illustrating the array waveguide receiving unit 1 of this application, which is an array waveguide group that receives multiple laser beams.

[0078] like Figure 6 As shown, the array light field generating unit 1 has multiple laser light sources 11a, 11b, 11c... Figure 6 Only three laser sources are shown. Multiple laser sources 11a, 11b, 11c... generate lasers of different wavelengths λa, λb, λc... respectively. Each laser path is transmitted through... Figure 2 As shown, after the diffractive light source device forms an array of light fields, it undergoes beam shaping and spatial filtering before finally illuminating the detection area 24 of the fluid focusing unit 2. Thus, the array of light fields of each laser has a specific spatial distribution, such as the aforementioned regular two-dimensional array or random two-dimensional array. Furthermore, the array light spots formed by the array light fields of different wavelengths illuminating the detection area 24 of the fluid focusing unit 2 do not overlap. The array light fields of all lasers together constitute an array light field group, and all the scattered light spots formed by the array light field group illuminating the detection area 24 of the fluid focusing unit 2 serve as the output of the array light field generating unit 1.

[0079] The arrangement of the array light field for multi-channel lasers will be explained in detail later. Figure 6 In the example shown, the array spots of three lasers λa, λb, and λc are arranged in an alternating manner. For instance, the array spots of the three lasers are arranged in an alternating manner in the order of λa, λb, λc, λa, λb, λc... Depending on the arrangement of the array light fields of the multi-laser, the arrangement of the array spots formed by each laser in the detection area 24 is also different.

[0080] Figure 6 A schematic diagram of the array light field generating unit 1 is provided, which is suitable for shaping and combining multiple laser sources of different wavelengths. Multiple laser sources 11a, 11b, 11c… first undergo beam shaping to form parallel beams. Beam shaping uses devices such as diffractive optics (DOE), spatial light modulators (SLM), or digital micromirrors (DMD) to split and shape the incident beams into parallel beams at multiple angles. After shaping, the beams pass through a spatial filtering section, such as a mirror group, with a spatial light filter placed on the image plane of the mirror group to filter out higher-order diffracted light or stray light, forming a clean, desired light spot. The laser beam combining section uses a dichroic mirror group to combine the light fields of multiple lasers into a single beam, which is then projected onto the target plane to form an array of light spots, with the spatial positions of the array light spots for each wavelength separated from each other.

[0081] The biological microparticle samples flowing in the fluid focusing unit 2 are typically fluorescently stained or labeled with antibodies, thus carrying fluorescent information. When the biological microparticles flow through the detection area 24 of the fluid focusing unit 2, they emit light signals containing both fluorescent and non-fluorescent components. These light signals enter the array waveguide receiving unit 3 and are then separated into fluorescent and non-fluorescent components by the subsequent beam splitting unit 4. The fluorescent components are further separated according to wavelength, while the non-fluorescent components are separated into bright-field, dark-field, and scattered components. The non-fluorescent components are used for bright-field imaging, dark-field imaging, and scattered imaging, collectively referred to as label-free imaging.

[0082] like Figure 7 As shown, the arrayed waveguide light-collecting unit 3 includes a light-collecting objective lens 31, a condensing objective lens 32, and an arrayed waveguide group 33.

[0083] The array waveguide group 33 consists of multiple array waveguides 33a, 33b, 33c, etc., corresponding to each wavelength of laser light. Each array waveguide has multiple sub-waveguides made of optical fibers at the front end and a main waveguide at the rear end. Each sub-waveguide corresponds to each scattered spot in the array beam of that laser path. The optical signals received by multiple sub-waveguides of the same array waveguide are converged into a main waveguide as the optical signal corresponding to that laser path.

[0084] Specifically, such as Figure 7 As shown, the array waveguide group 33 includes multiple array waveguides 33a, 33b, 33c..., which are used to receive optical signals from array optical fields with wavelengths of λa, λb, and λc, respectively. That is, the multiple array waveguides 33a, 33b, 33c... correspond one-to-one with the array optical fields of the aforementioned multiple laser light sources 11a, 11b, 11c... Specifically, array waveguide 33a includes multiple sub-waveguides 331a at the front end and a single main waveguide 332a at the rear end; array waveguide 33b includes multiple sub-waveguides 331b at the front end and a single main waveguide 332b at the rear end; and array waveguide 33c includes multiple sub-waveguides 331c at the front end and a single main waveguide 332c at the rear end.

[0085] The light-receiving ends of multiple array waveguides 33a, 33b, 33c... are each located on the same end face and are pre-arranged to correspond to multiple scattered light spots. In addition, the end faces where the light-receiving ends of the multiple sub-waveguides 331a, 331b, 331c... are located are pre-set on the focal plane of the condenser lens 32.

[0086] After the biological particle sample is illuminated by the scattered light spots, the light signal passes through the receiving objective lens 31 and the condensing objective lens 32, and is focused onto the focal plane of the condensing objective lens 32. Since the focal plane of the condensing objective lens 32 and the focal plane of the receiving objective lens 31 are in an object-image conjugate relationship, the light signal on the focal plane of the condensing objective lens 32 forms an arrangement corresponding to the arrangement of the array light field group. Furthermore, due to object-image conjugate, the light signal on the focal plane of the condensing objective lens 32 is opposite to that of the array light field group. More specifically, when the array light spots of the multi-channel laser are arranged in the order λa, λb, λc, λa, λb, λc, multiple sub-waveguides are arranged in the order 331c, 331b, 331a, 331c, 331b, 331a according to the conjugate order λc, λb, λa, λc, λb, λa.

[0087] That is, in the image streaming optical system 100 based on arrayed waveguide light collection of multiple lasers, for each of the multiple lasers, the array light field generating unit 1 generates an array light field with a predetermined spatial distribution, and the multiple array light fields corresponding to each laser constitute an array light field group. The array light field group illuminates the detection area 24 of the fluid focusing unit 2, forming scattered light spots. These scattered light spots contain the array light spots of each laser. Then, the optical signal of each scattered light spot is collected into a separate sub-waveguide (optical fiber) through the sub-waveguide corresponding to each scattered light spot.

[0088] Since the optical signal of each scattered spot is received by a single sub-waveguide, the sub-waveguides that receive the optical signals of each scattered spot of the same laser are used as a group of arrayed waveguides. The optical signals are then gathered into a single beam at the rear end. This allows the optical signals excited by different lasers and received by the split fiber to be re-gathered into a single beam according to the wavelength of the laser and then fed into the beam splitting unit 4 for subsequent processing.

[0089] For example, sub-waveguides can use single-mode or multimode fiber with a numerical aperture of 0.2-0.5, with the core diameter matched to the spot size (1-5μm) to ensure efficient coupling of optical signals. The main waveguide uses low-loss fiber to reduce energy attenuation during optical signal transmission and ensure signal strength. The arrangement accuracy of the array waveguides is controlled within ±0.5μm to ensure precise alignment between the sub-waveguides and the array spot.

[0090] As mentioned above, human cells, a typical example of biological particles, are typically in the size range of 20 μm to 30 μm. Therefore, in the detection area 24 of the fluid focusing unit 2, the interval between adjacent light spots along the flow direction of the biological particles, i.e., the difference in the abscissa of adjacent light spots, should be greater than 30 μm. In the direction perpendicular to the flow direction of the biological particles, the total offset between light spot n and light spot 1, i.e., the difference in the ordinate of light spot n and light spot 1, ΔY = y... n -y1 is greater than 30μm.

[0091] In other words, due to the size of biological particles, the spacing between adjacent laser beams in an array cannot be infinitely small; the array of laser beams in the same path needs to maintain a certain sparsity. Thus, each laser beam needs to have a certain spatial scale. If a single waveguide is used to collect the light signals excited by the entire array, the waveguide size would be too large. Especially in the case of multi-laser imaging streaming optical systems, using a single waveguide to collect the light signals from each laser beam inevitably leads to crosstalk.

[0092] To address this issue, the inventors of this application, through dedicated research, employed a structure where multiple sub-waveguides collect the optical signal from each individual light spot, and then converge these multiple sub-waveguides into a single main waveguide. Thus, the optical signal from each scattered light spot is collected by a single sub-waveguide, thereby preventing crosstalk. Furthermore, the slender sub-waveguides do not result in an excessively large waveguide size.

[0093] According to the structure of this application, the spatial size of each scattered light spot is small, enabling the use of small-sized and low-cost detectors such as APDs for detection. Furthermore, since the optical signal from each scattered light spot is collected into a separate sub-waveguide (fiber), and then the sub-waveguides collecting the optical signals from each scattered light spot from the same laser path are converged into a single overall waveguide, the structure is more compact. This significantly improves the imaging quality and signal-to-noise ratio in multi-laser applications, and fundamentally resolves the contradiction between detector size limitations and the large size of the array optical field.

[0094] Next, refer to Figure 8 Explain the arrangement of the array spot size in a multi-channel laser. Figure 8 The following explanation uses a regular two-dimensional array of light spots as an example.

[0095] Regarding the arrangement of the array spot of multi-channel lasers, various arrangement methods such as staggered arrangement and single arrangement can be adopted according to the requirements of both the size of the imaging field of view and the size of the detection throughput. Each arrangement method has its own advantages.

[0096] First, based on Figure 8 Explain the relationship between the size of the imaging field of view and the arrangement of the array light spots. For example... Figure 8 As shown in (a), the field of view in the x and y directions of imaging is determined by the arrangement of the array of light spots. Specifically, the field of view FOVy in the y direction is determined by the spacing between adjacent light spots in the y direction, i.e., FOVy = Δy. The field of view FOVx in the x direction is determined by the range of the N light spots arranged, i.e., FOVx = (N-1)Δx. A square field of view is typically used; however, this invention does not impose restrictions on the length and width of the field of view.

[0097] Especially in the x-direction, since the array spot is located on the focal plane of the condenser lens 13 of the array light field generating unit 1, the total length of the array spot that can be arranged is limited and needs to be smaller than the total size of the field of view FOVobj of the receiving objective lens 31: (N-1) Δx < FOVobj. In addition, the total number of array spots for each laser path is usually predetermined.

[0098] For a given laser beam, its array spot can either cover the entire field of view (FOVobj) of the receiving objective 31, or it can be arranged only on a portion of the FOVobj. When the array spot covers the entire FOVobj, the distance between adjacent spots is relatively large, meaning the spots are relatively sparse; when the array spot is arranged only on a portion of the FOVobj, the distance between adjacent spots is relatively small, meaning the spots are relatively dense. Based on the requirements for the size of the imaging field of view and the detection throughput, how to flexibly utilize the FOVobj of the receiving objective 31 becomes an important issue.

[0099] For the same laser beam, the longer the total length of the array spot in the x-direction, the greater the probability that two biological particles are simultaneously located within the array spot of that laser beam. When two or more biological particles are simultaneously located within the array spot of that laser beam, the optical signals of the two or more biological particles will be captured by the array waveguide receiving unit 3 at the same time. This is detrimental to the acquisition and imaging of optical signals and therefore becomes ineffective flux.

[0100] In this scenario, to ensure that only one biological particle is imaged within the array spot, the concentration of biological particles flowing through the detection area 24 of the fluid focusing unit 2 needs to be lower, i.e., the biological particles need to be more sparse. Therefore, the theoretical maximum flux (the number of biological particles imaged per second) decreases. Conversely, the shorter the total length of the array spot in the x-direction, the higher the theoretical maximum flux. In other words, for the same laser path, minimizing the total length of the array spot in the x-direction is beneficial for increasing the theoretical maximum flux.

[0101] On the other hand, for the same laser beam, the longer the total length of the array spot in the x-direction, the greater the possible spot spacing Δx and the number of spots N, resulting in a larger usable imaging field of view; conversely, the longer the total length of the array spot in the x-direction, the smaller the usable imaging field of view. A larger imaging field of view leads to a clearer image. In other words, for the same laser beam, maximizing the total length of the array spot in the x-direction is beneficial for improving image quality, especially for imaging large biological particles.

[0102] Therefore, depending on whether detection throughput or imaging field of view is prioritized, different array spot arrangements can be adopted to obtain the optimal combination of imaging field of view and imaging throughput.

[0103] Figure 8 (b) shows the arrangement of three laser beams in a manner that maximizes the imaging field of view. That is, all three laser beams prioritize the imaging field of view. In this case, the array spots of the three laser beams need to fill the field of view (FOVobj) of the collecting objective 31 as much as possible. Therefore, the array spots of the three laser beams are arranged in an interleaved manner, that is, arranged in a cyclical manner according to λa, λb, λc, λa, λb, λc…

[0104] With this arrangement, the array spot of each laser beam can achieve the maximum arrangement range, and each laser beam has the maximum imaging field of view: FOVy = Δy, FOVx = (N-1)Δx. This arrangement is suitable for detecting larger biological particles, such as cancer cells, and can be applied to a wide range of sample sizes.

[0105] Figure 8(c) illustrates the arrangement of three laser beams in a manner that maximizes detection flux. That is, all three laser beams prioritize detection flux. In this configuration, the array spots of each of the three laser beams need to be set to the smallest possible total length in the x-direction. Therefore, the array spots of each of the three laser beams can each occupy a portion of the field of view (FOVobj) of the receiving objective 31, for example, each occupying 1 / 3. That is, after the array spots of one laser beam are completely arranged in the order λa, λa, λa…λb, λb, λb…λc, λc, λc, the array spots of the next laser beam are arranged, with each laser beam's array spot occupying 1 / 3 of the entire field of view (FOVobj) of the receiving objective 31.

[0106] Therefore, relative to Figure 8 With the arrangement shown in (b), the theoretical maximum detection throughput is tripled. For each laser beam, the spacing between adjacent spots is reduced to 1 / 3, thus changing the size of the imaging field of view. Figure 8 1 / 3 of (b): FOVy = Δy / 3, FOVx = (N1)Δx / 3. This arrangement is suitable for applications that detect small biological particles, such as bacteria and small cells, and also require high throughput.

[0107] Figure 8 Figure (d) illustrates a configuration that balances detection throughput and imaging field of view. In this configuration, the lasers λa and λb prioritize the imaging field of view and are therefore arranged in an interleaved manner. The array light field of both lasers occupies 2 / 3 of the field of view (FOVobj) of the receiving objective 31. The field of view of λa and λb is relative to... Figure 8 (c) becomes twice: FOVy = 2Δy / 3, FOVx = (N-1)2Δx / 3. On the other hand, the detection throughput becomes Figure 8 2 / 3 times of (b).

[0108] For λc lasers, detection flux is prioritized; therefore, its theoretical maximum flux and imaging field of view are related to... Figure 8 (c) remains consistent. This combination arrangement can maximize the use of the field of view (FOVobj) of the light-collecting objective lens 31, and flexibly detect different types of biological particles using different lasers. For example, λc is suitable for detecting small particle samples, while λa and λb lasers are suitable for detecting cell samples of moderate size.

[0109] That is, the array spot of a multi-channel laser can be arranged in one of the following ways: staggered, single-channel, or mixed. For example, a staggered arrangement... Figure 8 As shown in (b), multiple array spots of each array light field intersect with multiple array spots of other array light fields in the flow direction of the biological particle sample. A single arrangement is as follows: Figure 8As shown in (c), the array spot of each array light field does not intersect with the array spot of other array light fields in the flow direction of the biological particle sample. The mixed arrangement is as follows... Figure 8 As shown in (d), some of the array light fields in the multiple array light fields are arranged in an alternating manner, while the remaining array light fields are arranged in a single manner.

[0110] In addition to various arrangement methods, a "arrangement method + spacing adjustment" mode can also be adopted. That is, in addition to determining which array light fields in multiple array light fields are arranged in an alternating, single, or mixed manner, the total length of each array light field in the flow direction of the biological particles is also determined.

[0111] For example, Figure 8 In case (d), the array light field of lasers λa and λb can also occupy 1 / 2 of the field of view FOVobj of the light-collecting objective lens 31, while the array light field of laser λc occupies the other 1 / 2 of the field of view FOVobj of the light-collecting objective lens 31.

[0112] In this case, the imaging fields of λa and λb are relative to Figure 8 (c) becomes 1.5 times: FOVy = 3Δy / 2, FOVx = (N-1)3Δx / 2. On the other hand, the detection throughput becomes Figure 8 1 / 2 times (b).

[0113] The theoretical maximum flux of λc is Figure 8 (c) is 2 / 3, and the imaging field of view is Figure 8 1.5 times that of (c).

[0114] Other arrangements of beam spots under multi-channel lasers will not be listed one by one. Those skilled in the art, based on the technical concept of this invention, can adjust key parameters such as the arrangement of array beam spots and array waveguides of multi-channel lasers, as well as the flow rate of biological particle samples, under various needs and application scenarios.

[0115] For example, key parameters of the array spot are optimized for common biological particle sizes (cells 20-30 μm, viruses 50-100 nm, proteins 1-10 nm). For cell detection, the spot spacing Δx along the flow direction is ≥35 μm, and the total offset perpendicular to the flow direction is ≥35 μm; for tiny particles such as viruses and proteins, Δx can be reduced to 5-10 μm, and the total offset is ≥10 μm, ensuring that the spot effectively covers the particle surface. The spot size is designed to be 1-5 μm, adapting to the detection range of small-sized detectors such as APDs, thus improving signal acquisition efficiency.

[0116] In clinical diagnostic scenarios, staggered array light fields can be prioritized to acquire large field-of-view, high-resolution images, adapting to the morphological recognition needs of cancer cells, abnormal cells, etc. Equipped with 4-6 lasers of different wavelengths, it supports simultaneous detection of multiple fluorescent markers, improving diagnostic accuracy. Utilizing a microfluidic chip-type fluid focusing unit reduces sample consumption, adapting to the clinical needs of detecting small sample volumes.

[0117] In high-throughput screening scenarios in the pharmaceutical industry, a single-array optical field can be used to maximize detection throughput (≥5000 particles per second), adapting to the rapid analysis of large-scale samples in drug screening. Configuring 2-3 core wavelength lasers simplifies system structure and reduces operating costs. Employing a flow cell-type fluid focusing unit supports continuous detection of large-volume samples, improving screening efficiency.

[0118] In environmental microbiology detection scenarios, a hybrid array light field can be used to accommodate the detection needs of microorganisms of different sizes (bacteria, fungi, algae). A broadband laser light source (355nm-640nm) is configured to adapt to the fluorescent labeling characteristics of different microorganisms. The anti-contamination design of the fluid focusing unit is optimized to improve the stability of the device in complex environmental sample detection.

[0119] For example, based on the viscosity and concentration of different samples, the flow rate ratio of sheath fluid to sample is optimized (typically the sheath fluid flow rate is 5-10 times the sample flow rate) to stabilize the flow velocity of single microparticles at 0.5-5 m / s, ensuring both detection throughput and clear imaging. The inner walls of the flow cell or microchannel are treated with a hydrophobic coating to reduce the adsorption of biological particles and improve detection stability.

[0120] Next, refer to Figure 9 This application describes the phase difference compensation for the optical signal of each laser in a multi-channel laser system. Figure 9 For simplicity, this explanation will only use two laser beams as an example.

[0121] like Figure 9 As shown, the laser has two wavelengths, λa and λb. The array spots of the two laser wavelengths are arranged at equal intervals, with a distance of Δx in the x-direction and a distance of Δy in the y-direction. Simultaneously, the array spots of the two lasers are staggered, with the laser spot of λb located at the midpoint of the laser spot of λa. It should be noted that this equal-interval arrangement is one possible implementation; in actual implementation, the spot distribution can be adjusted according to the specific circumstances. When cells pass through the array light field formed by the two laser beams, they are sequentially excited with fluorescence signals.

[0122] For example, the fluorescence signal excited by laser λa consists of n pulses, and the fluorescence signal excited by laser λb also consists of n pulses. Since the laser spots of the two lasers are offset by a distance Δx / 2, the fluorescence signals corresponding to the two lasers will have a phase difference of Δx / 2v in the time domain, where v is the velocity of cell flow. In practical applications, an electronic acquisition system is needed to perform delayed synchronization processing on the optical signals of these two laser beams, that is, after the signal of λa is triggered, the signal excited by laser λb is acquired and stored after a delay of Δx / 2v.

[0123] exist Figure 9 In the example, lasers λa and λb are arranged in an alternating manner, both occupying the entire field of view FOVobj of the receiving objective lens 31. Therefore, the phase difference that laser λb needs to compensate for relative to laser λa is Δx / 2v = FOVobj / 2(n-1)v.

[0124] The above explains phase difference compensation when two lasers are arranged in an alternating pattern. However, depending on the number of lasers and their arrangement, the phase difference that needs to be compensated in terms of timing varies for each laser signal. Using one laser from the multiple laser streams as a reference, phase difference compensation is performed on the remaining laser streams to ensure that the first spot in the array of the remaining laser streams is in sync with the first spot in the array of the reference laser.

[0125] Furthermore, although the field of view of the light-collecting objective 31 occupied by the array spots of each laser is different, and therefore the density of their respective array spots is different, as long as the first spot in the array spots of each laser is consistent with each other in time, and multiplied by a coefficient corresponding to the density of its own array spot, the light signals of the array spots of each laser can be made to correspond.

[0126] The specific embodiments of this application have been described above. Those skilled in the art should understand that the specific embodiments described above are only for explaining this application, and the scope of protection of this application is not limited thereto. Any modifications, substitutions, or combinations made by those skilled in the art within the technical scope disclosed in this application, based on the technical solution and inventive concept of this application, should be covered within the scope of protection of this application.

Claims

1. An image streaming optical system based on arrayed waveguide light collection, characterized in that, have: An array light field generating unit generates an array light field with a specified spatial distribution for each of at least one laser beam, and the array light field group consists of multiple array light fields corresponding to each laser beam. A fluid focusing unit focuses a biological particle sample and, at least in the detection area of ​​the fluid focusing unit, shapes the dispersed fluorescently labeled biological particles in the biological particle sample into a single particle stream. The detection area of ​​the fluid focusing unit refers to the area irradiated by the array light field group. as well as The array waveguide light receiving unit comprises an array waveguide group consisting of multiple array waveguides that correspond one-to-one with the multiple array light fields. The array waveguides collect light signals related to the corresponding array light fields when biological particle samples flow through the detection area. The light signals contain fluorescent and non-fluorescent components.

2. The image streaming optical system based on arrayed waveguide light collection according to claim 1, characterized in that, In the array light field generating unit, the array light field generated by each of the at least one laser beam consists of multiple array light spots irradiating the detection area.

3. The image streaming optical system based on arrayed waveguide light collection according to claim 2, characterized in that, In the arrayed waveguide receiving unit, each arrayed waveguide has multiple sub-waveguides and a main waveguide. The multiple sub-waveguides correspond one-to-one with multiple array light spots in the corresponding array optical field. Optical signals collected by multiple sub-waveguides of the same array waveguide converge into the total waveguide of the array waveguide, serving as the optical signal corresponding to that laser path.

4. The image streaming optical system based on arrayed waveguide light collection according to claim 1, characterized in that, In the array of light fields, each of the plurality of array light fields is arranged in any one of the following ways: staggered arrangement, single arrangement, or mixed arrangement. The term "interlaced arrangement" refers to the fact that multiple array spots of this array light field are interlaced with multiple array spots of other array light fields along the flow direction of the biological particle sample. The term "single arrangement" refers to the fact that the array light spots of this array light field do not intersect with the array light spots of other array light fields in the flow direction of the biological particle sample. The hybrid arrangement refers to the fact that some of the array light fields in the multiple array light fields are arranged in an alternating manner, while the remaining array light fields are arranged in a single manner.

5. The image streaming optical system based on arrayed waveguide light collection according to claim 4, characterized in that, For array optical fields prioritizing imaging field of view, an alternating arrangement is adopted. For array optical fields where detection flux is prioritized, a single arrangement is used.

6. The image streaming optical system based on arrayed waveguide light collection according to claim 4 or 5, characterized in that, Based on the requirements of imaging field of view and detection throughput, the total length of the array spot in each of the multiple array light fields along the flow direction of the biological particles is determined.

7. The image streaming optical system based on arrayed waveguide light collection according to any one of claims 3-6, characterized in that, The array light field generated by each laser beam consists of any one of the following: a one-dimensional linear array light spot, a regular two-dimensional array light spot, or a random two-dimensional array light spot illuminating the detection area.

8. The image streaming optical system based on arrayed waveguide light collection according to claim 7, characterized in that, The multiple sub-waveguides of any one of the multiple array waveguides have an arrangement corresponding to the multiple array light spots in the corresponding array optical field.

9. The image streaming optical system based on arrayed waveguide light collection according to claim 1, characterized in that, The fluid focusing unit is a focusing structure based on a flow cell or a focusing structure based on a microfluidic chip. The focusing structure based on the flow cell includes a conical flow cell, a direct current channel, and two symmetrically arranged inlet ports. After the sheath fluid is injected through the inlet ports, it encapsulates the sample to form a single-particle stream. The focusing structure based on the microfluidic chip includes a central channel and two symmetrical microchannels on both sides. After the sheath fluid is injected through the microchannels, the sample is compressed into a single microparticle stream.

10. An image streaming detection device, characterized in that, have: The image streaming optical system based on arrayed waveguide light collection according to any one of claims 1-9; and Optical signal processing system The optical signal processing system includes a beam splitting unit, which separates the optical signal collected by the arrayed waveguide receiving unit into fluorescent and non-fluorescent components, and further separates the fluorescent components into spatially discrete fluorescence spectra according to wavelength.

11. The image streaming detection device according to claim 10, characterized in that, The optical signal processing system also features: A photoelectric conversion unit is used to convert the various fluorescence spectra and laser components of the fluorescent component in an optical signal into electrical signals; and The signal processing unit analyzes and processes the electrical signals to generate fluorescence spectral images and label-free images of biological particles.

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