Multi-LED full-field optical coherence microscope system, imaging method, device and medium

Abstract

The invention provides a multi-LED full-field optical coherence microscope system, an imaging method, equipment and a medium, and the system comprises at least two LED light sources which are used for providing low-coherence illumination beams with different illumination characteristics; the at least one beam splitter is used for coupling the light beams emitted by the at least two LED light sources into an illumination light path of the full-field optical coherence microscope system; the area-array camera is used for collecting an interference image of the sample; the synchronous signal generator is respectively connected with the at least two LED light sources and the area-array camera, and is used for generating synchronous control signals, controlling the at least two LED light sources to be alternately lightened in a time division multiplexing mode, synchronizing with an image acquisition time sequence of the area-array camera, acquiring interference images corresponding to different LED light sources in the same view field, and outputting the interference images. The problem that the imaging flexibility, the comprehensive performance and the application scene of a traditional FF-OCM system are greatly limited is solved.

Description

Technical Field

[0001] This invention relates to the field of full-field optical coherence microscopy, and more particularly to a multi-LED full-field optical coherence microscopy system, imaging method, device, and medium. Background Technology

[0002] Full-field optical coherence microscopy (FF-OCM, also known as full-field optical coherence tomography, FF-OCT) is an advanced three-dimensional imaging technology that combines the depth-penetrating capability of optical coherence tomography (OCT) with the advantages of high-resolution microscopy. It is widely used in biomedical research and non-invasive clinical imaging. Its core working principle is based on low-coherence interferometry. By acquiring interferometric images through an area array camera and performing phase demodulation, it overcomes the depth-of-field limitations of traditional OCT. Utilizing a high numerical aperture optical system, it achieves subcellular (<1μm) lateral resolution while simultaneously acquiring emphyseal images parallel to the sample surface. This allows for clear observation of microscopic structures and functions without damaging tissues, providing a powerful tool for non-invasive biological tissue detection.

[0003] A typical optical path configuration of a conventional FF-OCM system includes a low-coherence light source, usually a halogen lamp or LED, which exhibits spatial incoherence and low temporal coherence; a beam splitter (BS); a microscope objective (MO); a piezoelectric transducer (PZT); a reference mirror; a sample stage; a tube lens; and an area array camera. The light emitted from the light source is split into a reference beam and a sample beam by the beam splitter. These beams then pass through the reference arm (the reference mirror is fixed to the PZT) and the sample arm (the sample to be imaged is placed at the focal point of the objective lens), respectively. The two returning beams are then rejoined by the beam splitter and focused by the tube lens onto the area array camera to complete the imaging. To obtain intensity and phase information, two phase demodulation methods are commonly used in existing technologies: one is the four-step phase shifting method (FPA), which uses a PZT to drive the reference mirror to move and acquire images of four phases: 0, π / 2, π, and 3π / 2. Then, the intensity A(x,y) and phase φ(x,y) are calculated using formulas. The other is the single-step phase shifting method (SPA), which only acquires two frames of images with an optimal phase difference of π. This method has higher demodulation efficiency and the imaging time is only half that of FPA. Moreover, in biological tissue imaging, since the phase information of the tissue is random and discontinuous, its imaging effect is basically the same as that of FPA.

[0004] However, existing FF-OCM systems face significant technical bottlenecks in light source applications: First, a single LED light source cannot simultaneously achieve both penetration and resolution. While long-wavelength LEDs improve the penetration of biological tissues, they result in low camera response and require increased illumination intensity. Short-wavelength LEDs, while improving resolution, struggle to meet the demands of deep imaging. Second, there is an inherent contradiction between LED bandwidth and imaging performance. Broadband LEDs can improve longitudinal resolution, but the shortened coherence length exacerbates the separation between the coherence plane and the focal plane caused by tissue refractive index, reducing imaging depth. Narrowband LEDs, on the other hand, have the opposite effect. Third, different components in biological tissues (such as deoxyhemoglobin and oxyhemoglobin) exhibit specific responses to particular wavelengths, making simultaneous imaging of multiple targets impossible with a single LED. Furthermore, some existing multi-band schemes use dichroic mirrors to split a single LED band for detection, which not only limits the LED's wavelength range, bandwidth, and power but also sacrifices the camera's field of view. Moreover, the system structure is complex and difficult to meet practical application requirements.

[0005] Therefore, there is an urgent need for a multi-LED full-field optical coherence microscope system to solve the technical problems that the imaging flexibility, overall performance and applicable scenarios of traditional FF-OCM systems are greatly limited. Summary of the Invention

[0006] To overcome the problems existing in related technologies, this disclosure provides a multi-LED full-field optical coherence microscope system, imaging method, device and medium to solve the technical problem that the imaging flexibility, overall performance and applicable scenarios of traditional FF-OCM systems in related technologies are greatly limited.

[0007] This specification provides one or more embodiments of a multi-LED full-field optical coherence microscope system, including a tube mirror, a beam splitter, a microscope objective, a piezoelectric ceramic, and a reference mirror, characterized in that it further includes: At least two LED light sources are used to provide low-coherence illumination beams with different illumination characteristics; At least one beam splitter is used to couple the light beams emitted by the at least two LED light sources into the illumination path of the full-field optical coherence microscope system. Area array camera, used to acquire interference images of the sample; A synchronization signal generator is connected to the at least two LED light sources and the area array camera, respectively, to generate a synchronization control signal to control the at least two LED light sources to light up alternately in a time-division multiplexing manner and synchronize with the image acquisition timing of the area array camera, so as to acquire interference images corresponding to different LED light sources under the same field of view.

[0008] Preferably, the at least two LED light sources are provided with multiple beam splitters that sequentially couple the optical path; The synchronization signal generator triggers the area array camera to acquire images at a frequency four times the lighting frequency of a single LED light source, sequentially acquiring the illumination images of each LED light source.

[0009] Preferably, the at least two LED light sources include LEDs whose output light polarization directions are orthogonal to each other, and the at least two LED light sources are LED light sources with the same / different center wavelengths and the same / different spectral bandwidths; The beam splitter is any one of a broadband optical beam splitter, a polarization beam splitter, or a dichroic beam splitter.

[0010] Preferably, the synchronization signal generator is further configured to: Control the at least two LED light sources to operate with different duty cycles; The area scan camera is controlled to use different integration times when acquiring images under different LED light source illumination. This ensures that the brightness of images acquired under different LED light source illumination remains consistent.

[0011] Preferably, the synchronization control signal generated by the synchronization signal generator includes a first square wave signal and a second square wave signal; The first square wave signal is a 100Hz TTL square wave, used to control the LED light source to light up alternately; The second square wave signal is a 200Hz square wave, which is used to trigger the area array camera to acquire data synchronously, so that odd-numbered frames correspond to the illumination of the first LED light source, and even-numbered frames correspond to the illumination of the second LED light source.

[0012] Preferably, it also includes an optical switch, optical shutter, or chopper disposed on the output optical path of each LED light source, for controlling the opening and closing of the corresponding LED light source.

[0013] Preferably, the interferometric image acquired by the area array camera is demodulated using a single-step phase-shifting method; The single-step phase-shifting method selects two interferometric images with a phase difference of π and demodulates them to obtain intensity information.

[0014] This specification provides one or more embodiments of an imaging method using a multi-LED full-field optical coherence microscope system as described above, comprising the following steps: A synchronization control signal is generated by a synchronization signal generator; Control at least two LED light sources to alternately illuminate in a time-division multiplexing manner; The lighting sequence of the control area array camera and the LED light source is synchronized to acquire interference images corresponding to each LED light source; Phase demodulation was performed on the acquired interferometric images to obtain full-field optical coherence tomography images corresponding to different illumination characteristics.

[0015] This specification provides one or more embodiments of a computer device, including a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor executes the computer program to implement the imaging method described above.

[0016] This specification provides one or more embodiments of a computer-readable storage medium storing a computer program that, when executed by a processor, implements the steps of the imaging method described above.

[0017] This disclosure provides a multi-LED full-field optical coherence microscope system, imaging method, device, and medium. Its advantages lie in configuring at least two LED light sources with different illumination characteristics, overcoming the performance limitations of a single LED. It can simultaneously meet the requirements of deep penetration and high-resolution imaging, adapt to the specific responses of different tissue components, and achieve synchronous imaging of multiple targets. This resolves the contradiction between penetration and resolution, and between longitudinal resolution and imaging depth, that a single light source cannot simultaneously achieve. It achieves efficient coaxial coupling of multiple LED light sources, ensuring a unified illumination field of view without sacrificing the camera's effective field of view. It supports various selections such as broadband, polarization, and dichroism, adapting to specific needs such as polarization imaging while maximizing light source utilization efficiency, avoiding the wavelength and power limitations of traditional multi-band schemes. It establishes a rigid temporal correlation between the LEDs and the camera, using time-division multiplexing to achieve alternating LED illumination and synchronous camera acquisition, ensuring that images all originate from the same location on the sample, eliminating the need for post-registration steps. Without requiring modifications to core components of traditional systems, upgrading becomes less difficult and costly, and multi-LED imaging can be achieved using a single optical path. It accurately captures interference images from different LEDs, providing high-quality data for phase demodulation and meeting the high-efficiency imaging requirements of single-step phase-shifting methods. By matching the integration time of different LEDs and adjusting the light source duty cycle, consistent image brightness is achieved, significantly reducing the difficulty of subsequent algorithm matching. Attached Figure Description

[0018] To more clearly illustrate the technical solutions in one or more embodiments of this specification or in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in this specification. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0019] Figure 1 A schematic diagram of the structure of a multi-LED full-field optical coherence microscope system provided for one or more embodiments of this specification; Figure 2 A schematic diagram of a multi-LED full-field optical coherence microscope system including a polarization beam splitter, provided for one or more embodiments of this specification; Figure 3 This is a schematic diagram of the structure of four LED light sources provided in one or more embodiments of this specification; Figure 4 A schematic flowchart illustrating an imaging method for a multi-LED full-field optical coherence microscope provided in one or more embodiments of this specification; Figure 5 This is a schematic diagram of the structure of a computer device provided for one or more embodiments of this specification. Detailed Implementation

[0020] To enable those skilled in the art to better understand the technical solutions in one or more embodiments of this specification, the technical solutions in one or more embodiments of this specification will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only a part of the embodiments of this specification, and not all of the embodiments. Based on one or more embodiments of this specification, all other embodiments obtained by those skilled in the art without creative effort should fall within the protection scope of this invention.

[0021] The present invention will now be described in detail with reference to specific embodiments and accompanying drawings.

[0022] System Implementation Examples According to embodiments of the present invention, a multi-LED full-field optical coherence microscope system is provided, including a tube mirror, a beam splitter, microscope objectives, piezoelectric ceramics, and a reference mirror, such as... Figure 1 The diagram shown is a structural schematic of the multi-LED full-field optical coherence microscope system provided in this embodiment. The multi-LED full-field optical coherence microscope system according to this embodiment further includes: At least two LED light sources 1 are used to provide low-coherence illumination beams with different illumination characteristics. These two LED light sources have the same / different center wavelengths and the same / different spectral bandwidths. When the at least two LED light sources 1 are two light sources with different center wavelengths and bandwidths, two wavelength-correlated images of the sample are obtained by alternating acquisition. For example, LED1 has a longer wavelength and narrower bandwidth to achieve deep imaging within the sample, while LED2 has a shorter wavelength and wider bandwidth to achieve high-resolution imaging. When the at least two LED light sources 1 are two light sources with the same center wavelength and bandwidth, a polarizer is added to each light source so that the output light of the light source is an orthogonally polarized signal, and beam splitter 2 is a polarization beam splitter. This allows the camera to obtain images of the sample in two polarization directions, achieving full-field polarization OCT imaging, such as... Figure 2 The figure shown is a schematic diagram of the structure of the multi-LED full-field optical coherence microscope system including a polarization beam splitter provided in this embodiment.

[0023] At least one beam splitter 2 is used to couple the light beams emitted by the at least two LED light sources into the illumination optical path of the full-field optical coherence microscope system. The beam splitter can be any one of a broadband beam splitter, a polarization beam splitter, or a dichroic beam splitter. The polarization beam splitter can obtain images of two polarization directions related to the sample, realizing full-field polarization OCT imaging. The dichroic beam splitter can maximize the utilization efficiency of the light source.

[0024] The area array camera 3 is used to acquire interference images of the sample. The single-step phase-shifting method is used to demodulate the phase of the interference images. Specifically, the single-step phase-shifting method selects two interference images with a phase difference of π and demodulates the intensity information.

[0025] A synchronization signal generator 4 is connected to the at least two LED light sources 1 and the area array camera 3 respectively, and is used to generate a synchronization control signal to control the at least two LED light sources 1 to light up alternately in a time-division multiplexing manner, and synchronize with the image acquisition timing of the area array camera 3, so as to acquire interference images of samples at the same position corresponding to different LED light sources under the same field of view.

[0026] The synchronization control signals generated by the synchronization signal generator 4 include a first square wave signal and a second square wave signal. The first square wave signal is a 100Hz TTL square wave, used to control the alternating illumination of the LED light source; the second square wave signal is a 200Hz square wave, used to trigger the area scan camera to synchronously acquire images, so that odd-numbered frames correspond to the illumination of the first LED light source, and even-numbered frames correspond to the illumination of the second LED light source. For example, the 100Hz TTL square wave causes the two LEDs to illuminate alternately, while the synchronization signal inputs the 200Hz square wave to the area scan camera 3 for synchronous acquisition. For example, frames 1, 3, 5, and 7 are all images acquired when light source 1 is lit, and frames 2, 4, 6, and 8 are all images acquired when light source 2 is lit.

[0027] The system provided in this embodiment is configured with at least two LED light sources with different illumination characteristics, breaking through the performance limitations of a single LED. It can simultaneously meet the requirements of deep penetration and high-resolution imaging, adapt to the specific responses of different tissue components, and achieve synchronous imaging of multiple targets. This solves the contradiction that a single light source cannot simultaneously achieve both penetration and resolution, or longitudinal resolution and imaging depth. It achieves efficient coaxial coupling of multiple LED light sources, ensuring a unified illumination field of view without sacrificing the effective field of view of the camera. It supports multiple selections such as broadband, polarization, and dichroism, which not only adapt to specific requirements such as polarization imaging but also maximize the utilization efficiency of the light source, avoiding the wavelength and power limitations of traditional multi-band schemes. It establishes a rigid temporal correlation between the LEDs and the camera, and achieves synchronous acquisition of the LEDs through time-division multiplexing, ensuring that the images all come from the same location on the sample, eliminating the need for post-registration steps. It does not require modification of the core components of traditional systems, reducing the difficulty and cost of upgrades. Multi-LED imaging can be completed using a single optical path. It accurately captures the interference images of different LEDs, providing high-quality data for phase demodulation and adapting to the high-efficiency imaging requirements of single-step phase-shifting methods. By matching the integration time of different LEDs and adjusting the duty cycle of the light source, consistent image brightness can be achieved, significantly reducing the difficulty of subsequent algorithm matching.

[0028] In one embodiment, such as Figure 3 The diagram shown is a structural schematic of the four LED light sources provided in this embodiment. At least two LED light sources 1 are provided with multiple beam splitters 2 to sequentially couple the optical path, thereby enabling more LEDs to input light.

[0029] The synchronization signal generator 4 triggers the area array camera 3 to acquire images at a frequency four times that of a single LED light source, and acquires the illumination images of each LED light source in sequence.

[0030] The system provided in this embodiment features multi-stage beam splitters that couple sequentially, adapting to multiple LEDs for expansion with a unified field of view and high light source utilization. The synchronous signal generator enables the camera to acquire images at four times the frequency of a single LED, sequentially acquiring images of each LED to ensure that the sample is imaged at the same location, eliminating the need for post-registration and efficiently acquiring multi-dimensional data.

[0031] In one embodiment, the synchronization signal generator is further configured to: The at least two LED light sources are controlled to operate with different duty cycles. Specifically, LED1 and LED2 can have different light source brightness, with one light source being brighter and the other being weaker. The LED with the stronger light source can use a lower duty cycle, such as 30%, while the LED with the weaker light source can use a higher duty cycle, such as 70%.

[0032] When controlling the area scan camera to acquire images under different LED light source illumination, different integration times are used according to the trigger signal, that is, a weaker light signal uses a longer integration time, so that the brightness of the images acquired under different LED light source illumination remains consistent.

[0033] The system provided in this embodiment uses a synchronization signal generator to control each LED light source to operate with a different duty cycle, while simultaneously adjusting the integration time of the corresponding acquisition frame of the area array camera. This directly achieves consistent image brightness under different LED lighting conditions during the acquisition process, eliminating the need for post-processing software and reducing the difficulty of subsequent algorithm matching.

[0034] In one embodiment, in addition to using the switching modulation of the LED itself, a fast aperture or optical shutter can be used to replace the fast switching of the LED. The fast switching of the LED may cause the power stability of the LED to deteriorate, while the external spatial light switch or optical shutter will not affect the stability of the LED. Therefore, it also includes an optical switch, optical shutter or chopper set in the output optical path of each LED light source to control the opening and closing of the corresponding LED light source.

[0035] Method Implementation Examples According to embodiments of the present invention, an imaging method using a multi-LED full-field optical coherence microscope system as described above is provided, such as... Figure 4 The diagram shown is a flowchart illustrating the imaging method of a multi-LED full-field optical coherence microscope provided in this embodiment. The multi-LED full-field optical coherence microscope method according to this embodiment includes the following steps: S410 generates a synchronization control signal through a synchronization signal generator.

[0036] S420 controls at least two LED light sources to alternately illuminate in a time-division multiplexing manner.

[0037] The S430 controls the timing of the illumination of the area array camera and the LED light source, and acquires interference images corresponding to each LED light source.

[0038] S440. Perform phase demodulation on the acquired interferometric image to obtain full-field optical coherence tomography images corresponding to different illumination characteristics.

[0039] The method provided in this embodiment establishes a rigid timing reference for LED light source illumination and camera acquisition through a precise synchronization control signal generated by a synchronization signal generator. This ensures the consistency of subsequent LED alternation and image acquisition, avoiding imaging deviations caused by timing misalignment from the source and laying a core control foundation for the orderly implementation of multi-LED multi-dimensional imaging. The time-division multiplexing mechanism is used to realize the alternating illumination of multiple LEDs, which not only avoids light interference caused by multiple light sources working simultaneously, but also efficiently utilizes the resources of a single optical path. This fully leverages the differentiated lighting characteristics of different LED light sources, providing orderly hardware support for acquiring multi-dimensional imaging data. The camera acquisition timing is precisely synchronized with the LED lighting timing, ensuring that each frame of the acquired image accurately matches the corresponding LED illumination period. This enables bias-free capture of interferometric images of the same sample location under different LED illuminations, eliminating the need for post-processing image registration and significantly improving imaging efficiency and the accuracy of multi-dimensional data. By extracting effective tomographic information from the interferometric images through phase demodulation, the original acquisition data corresponding to multiple LEDs is transformed into full-field OCT tomographic images with differentiated illumination characteristics. This directly outputs high-quality analytical data that meets diverse needs such as deep imaging, high-resolution imaging, and specific imaging, expanding the system's application scenario adaptability.

[0040] The embodiments of the present invention are method embodiments corresponding to the above system embodiments. The specific operations of each module processing step can be understood with reference to the description of the system embodiments, and will not be repeated here.

[0041] like Figure 5 As shown, the present invention also provides a computer-readable storage medium having a computer program stored thereon, wherein the computer program, when executed by a processor, implements the multi-LED full-field optical coherence microscope system of the above embodiments, or the computer program, when executed by a processor, implements the multi-LED full-field optical coherence microscope system of the above embodiments.

[0042] Those skilled in the art will understand that all or part of the processes in the methods of the above embodiments can be implemented by a computer program instructing related hardware. The computer program can be stored in a non-volatile computer-readable storage medium, and when executed, it can include the processes of the embodiments of the above methods. Any references to memory, storage, databases, or other media used in the embodiments provided in this application can include non-volatile and / or volatile memory. Non-volatile memory can include read-only memory (ROM), programmable ROM (PROM), electrically programmable ROM (EPROM), electrically erasable programmable ROM (EEPROM), or flash memory. Volatile memory can include random access memory (RAM) or external cache memory. By way of illustration and not limitation, RAM is available in various forms, such as static RAM (SRAM), dynamic RAM (DRAM), synchronous DRAM (SDRAM), dual data rate SDRAM (DDRSDRAM), enhanced SDRAM (ESDRAM), synchronous link DRAM (SLDRAM), Rambus direct RAM (RDRAM), direct memory bus dynamic RAM (DRDRAM), and memory bus dynamic RAM (RDRAM), etc.

[0043] The various embodiments in this specification are described in a progressive manner. Similar or identical parts between embodiments can be referred to mutually. Each embodiment focuses on describing the differences from other embodiments. In particular, for method or system embodiments, since they are basically similar to method embodiments, the description is relatively simple; relevant parts can be referred to the description of the method embodiments. The method and system embodiments described above are merely illustrative. The units described as separate components may or may not be physically separate. The components shown as units may or may not be physical units; that is, they may be located in one place or distributed across multiple network units. Some or all of the modules can be selected to achieve the purpose of this embodiment according to actual needs. Those skilled in the art can understand and implement this without creative effort.

[0044] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, and not to limit them. Although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some or all of the technical features. These modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present invention, and the contents not described in detail in the specification of the present invention are known to those skilled in the art.

Claims

1. A multi-LED full-field optical coherence microscope system, comprising a tube mirror, a beam splitter, microscope objectives, piezoelectric ceramics, and a reference mirror, characterized in that, Also includes: At least two LED light sources are used to provide low-coherence illumination beams with different illumination characteristics; At least one beam splitter is used to couple the light beams emitted by the at least two LED light sources into the illumination path of the full-field optical coherence microscope system. Area array camera, used to acquire interference images of the sample; A synchronization signal generator is connected to the at least two LED light sources and the area array camera, respectively, to generate a synchronization control signal to control the at least two LED light sources to light up alternately in a time-division multiplexing manner and synchronize with the image acquisition timing of the area array camera, so as to acquire interference images corresponding to different LED light sources under the same field of view.

2. The multi-LED full-field optical coherence microscope system as described in claim 1, characterized in that, The at least two LED light sources are respectively provided with multiple beam splitters to couple the optical path in stages; The synchronization signal generator triggers the area array camera to acquire images at a frequency four times the lighting frequency of a single LED light source, sequentially acquiring the illumination images of each LED light source.

3. The multi-LED full-field optical coherence microscope system as described in claim 1, characterized in that, The at least two LED light sources include LEDs whose output light polarization directions are orthogonal to each other, and the at least two LED light sources are LED light sources with the same / different center wavelengths and the same / different spectral bandwidths; The beam splitter is any one of a broadband optical beam splitter, a polarization beam splitter, or a dichroic beam splitter.

4. The multi-LED full-field optical coherence microscope system as described in claim 1 or 3, characterized in that, The synchronization signal generator is also configured to: Control the at least two LED light sources to operate with different duty cycles; The area scan camera is controlled to use different integration times when acquiring images under different LED light source illumination. This ensures that the brightness of images acquired under different LED light source illumination remains consistent.

5. The multi-LED full-field optical coherence microscope system as described in claim 1, characterized in that, The synchronization control signal generated by the synchronization signal generator includes a first square wave signal and a second square wave signal; The first square wave signal is a 100Hz TTL square wave, used to control the LED light source to light up alternately; The second square wave signal is a 200Hz square wave, which is used to trigger the area array camera to acquire data synchronously, so that odd-numbered frames correspond to the illumination of the first LED light source, and even-numbered frames correspond to the illumination of the second LED light source.

6. The multi-LED full-field optical coherence microscope system as described in claim 1, characterized in that, It also includes optical switches, optical shutters, or choppers installed on the output optical path of each LED light source to control the opening and closing of the corresponding LED light source.

7. The multi-LED full-field optical coherence microscope system as described in claim 1, characterized in that, The interferometric images acquired by the area array camera are demodulated using a single-step phase-shifting method; The single-step phase-shifting method selects two interferometric images with a phase difference of π and demodulates them to obtain intensity information.

8. An imaging method using a multi-LED full-field optical coherence microscope system as described in any one of claims 1-7, characterized in that, Includes the following steps: A synchronization control signal is generated by a synchronization signal generator; Control at least two LED light sources to alternately illuminate in a time-division multiplexing manner; The lighting timing of the control area array camera and the LED light source is synchronized, and interference images corresponding to each LED light source are acquired; Phase demodulation was performed on the acquired interferometric images to obtain full-field optical coherence tomography images corresponding to different illumination characteristics.

9. A computer device comprising a memory, a processor, and a computer program stored in the memory and executable on the processor, characterized in that, When the processor executes the computer program, it implements the multi-LED full-field optical coherence microscope method as described in claim 8.

10. A computer-readable storage medium storing a computer program, characterized in that, When the computer program is executed by the processor, it implements the steps of the multi-LED full-field optical coherence microscope method as described in claim 8.

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