A dynamic closed-loop fundus photobiological modulation system and closed-loop control device

Abstract

This invention relates to the field of ophthalmic phototherapy and medical optical imaging technology, and discloses a dynamic closed-loop fundus photobiomodulation system and closed-loop control device. The system includes a light source module, a fundus camera module, and a control module. The light source module has at least two independently controllable treatment light channels. The control module executes a T1 initiation phase, a T2 activation phase, a T3 inhibition phase, and a T4 relaxation phase according to the treatment cycle. During the baseline acquisition phase and the treatment sampling phase, the illuminated treatment light is used as the imaging illumination light to acquire fundus vascular images, obtain baseline vascular parameters and real-time vascular parameters, determine fundus vascular response parameters, and adjust the peak power, pulse frequency, duty cycle, or duration of the corresponding treatment light channel according to the fundus vascular response parameters for closed-loop control of fundus photobiomodulation.

Description

Technical Field

[0001] This invention relates to the field of ophthalmic phototherapy and medical optical imaging technology, and particularly to a dynamic closed-loop fundus photobiological modulation system and a closed-loop control device for controlling the system. Background Technology

[0002] Fundus diseases, such as dry age-related macular degeneration, diabetic retinopathy, glaucoma, and retinitis pigmentosa, are important types of diseases affecting visual function. Photobiomodulation (PBM), as a non-invasive phototherapy method, typically uses low-intensity light within a specific wavelength range to irradiate fundus tissues in order to improve local tissue metabolism and microcirculation. It has become an important research direction in the field of adjunctive treatment for fundus diseases.

[0003] In the existing technology, a variety of multi-wavelength fundus phototherapy devices, systems, and related control schemes have been proposed. For example, some existing schemes deliver therapeutic light of two or more different wavelengths to eye tissue in a coordinated manner, and treatment parameters such as light intensity, duration, frequency, and sequence can be set or adjusted by a controller; some schemes can also be combined with sensor feedback or camera observation for auxiliary positioning, pupil status detection, or safety control.

[0004] However, in the actual implementation of fundus photobiological modulation, existing multi-wavelength treatment protocols typically still rely on preset treatment parameters. The duration of each stage within the treatment cycle, as well as parameters such as peak power, pulse frequency, and duty cycle of each treatment optical channel, often cannot be adaptively updated based on the real-time response of the fundus tissue during treatment. Consequently, mismatches between treatment dosage and tissue response can easily occur in different patients, under different fundus blood flow conditions, or at different treatment stages.

[0005] Furthermore, existing feedback control methods tend to focus on parameters such as temperature, pupillary status, eye position, or other safety parameters, primarily for safety interlocking, position correction, or auxiliary control during treatment. A quantitative closed-loop control mechanism based on changes in fundus vessel diameter, blood flow velocity, and blood perfusion has not yet been fully established. For fundus photobiological modulation, changes in microcirculation in the treatment area are crucial for evaluating tissue response. If vessel diameter and blood flow velocity parameters corresponding to the treatment area cannot be obtained during treatment, and if vessel diameter change coefficients, blood perfusion indices, and their average time windows cannot be used for control decisions, closed-loop dose regulation oriented towards tissue response will be difficult to achieve.

[0006] Furthermore, regarding fundus image acquisition during treatment, existing solutions typically require independent illumination, independent diagnostic light sources, or additional imaging paths when real-time monitoring of fundus tissue responses is needed. Alternatively, they may not explicitly specify the use of the treatment light output from the illuminated treatment light channel as the imaging illumination light for synchronous exposure sampling. Such solutions may lead to an unstable correspondence between the treatment light irradiation area and the imaging sampling area, thereby affecting the correlation between closed-loop feedback parameters and the actual treatment area.

[0007] In addition, existing treatment modalities such as continuous irradiation, simple pulse irradiation, or fixed-duration phases often have difficulty in adjusting the peak power, pulse frequency, duty cycle, or phase duration of the corresponding treatment phase when the treatment response is insufficient or excessive. This is not conducive to dynamically balancing the treatment stimulus and relaxation recovery according to the tissue response.

[0008] In the specific structural design of multi-channel therapeutic light projection onto the target area of ​​the fundus, the lack of effective optical path shaping or coupling design may lead to uneven irradiation distribution within the target treatment area, or an unstable optical path correspondence between the therapeutic light projection and the fundus reflected light acquisition. These problems can be improved by further designing optical path shaping components and coupling components between the therapeutic and imaging optical paths.

[0009] Based on this, it is necessary to propose a dynamic closed-loop fundus photobiological modulation system and a closed-loop control device. Based on at least two therapeutic light channels, the therapeutic light output from the illuminated therapeutic light channel is used as the imaging illumination light for baseline acquisition and synchronous sampling of the treatment process. Based on the fundus vascular quantification parameters, at least one of the peak power, pulse frequency, and duty cycle of the therapeutic light channel, and / or the duration of the corresponding stage are adjusted in a closed loop to improve the matching between the therapeutic parameters and the real-time response of the fundus tissue. Summary of the Invention

[0010] The technical problem this invention aims to solve is that existing fundus photobiomodulation schemes mostly rely on preset treatment parameters, lacking a control mechanism that utilizes therapeutic light as imaging illumination to acquire fundus vascular responses in the treatment area, and performs closed-loop adjustments based on vascular quantification parameters to at least one of the peak power, pulse frequency, and duty cycle of the therapeutic light channel, and / or the duration of the corresponding phase. This results in treatment parameters being difficult to match with the real-time responses of fundus tissues during treatment. Therefore, this invention proposes a dynamic closed-loop fundus photobiomodulation system and a closed-loop control device.

[0011] The technical solution adopted by this invention to solve its technical problem is: A dynamic closed-loop fundus photobiological modulation system, comprising: The light source module has at least two independently controllable therapeutic light channels; The fundus camera module is used to acquire images of fundus vessels when the therapeutic light is used as the imaging illumination light, so as to obtain parameters such as vessel diameter and blood flow velocity. The control module is connected to the light source module and the fundus camera module respectively, and is used to control the light source module to output therapeutic light cyclically according to the treatment cycle, and to execute the T1 initiation period, T2 activation period, T3 inhibition period and T4 relaxation period in each treatment cycle; wherein, there is therapeutic light output in the T1 to T3 stages, and no therapeutic light output in the T4 stage. The control module is also used in the baseline acquisition stage and the synchronous exposure sampling stage during the treatment process to use the treatment light output by the illuminated treatment light channel as the imaging illumination light of the fundus camera module, and to make the imaging field of view of the fundus camera module at least partially overlap with the treatment light irradiation area. The control module is also used to obtain baseline vascular parameters and real-time vascular parameters based on the fundus vascular image, determine fundus vascular response parameters based on the baseline vascular parameters and real-time vascular parameters, and perform closed-loop adjustment of at least one treatment parameter based on the fundus vascular response parameters. The treatment parameters include at least one of the peak power, pulse frequency, and duty cycle of the treatment optical channel at the corresponding stage, and / or the duration of the corresponding stage.

[0012] Preferably, the control module is configured to execute the following closed-loop control process: a. Control the light source module to output therapeutic light cyclically according to the treatment cycle, and execute the T1 start-up period, T2 activation period, T3 inhibition period and T4 relaxation period in sequence within each treatment cycle; wherein, therapeutic light is output in the T1 to T3 stages, and no therapeutic light is output in the T4 stage, and the duration of each stage in the treatment cycle can be updated according to the closed-loop adjustment result. b. Before treatment begins, the light source module is controlled to illuminate at least one treatment light channel according to the baseline imaging illumination mode, and the fundus camera module is driven to acquire a baseline video sequence. The baseline vessel diameter D is obtained from the baseline video sequence. baseline Compared with baseline blood flow velocity V baseline The baseline imaging illumination mode is an illumination mode used for image acquisition rather than for treatment output, and its output power is lower than the peak power of the treatment light channel during the treatment output phase. c. During the treatment process, when at least one treatment light channel is lit during the T1 to T3 stages, the fundus camera module is controlled to perform synchronous exposure sampling, and the real-time blood vessel diameter D(t) and real-time blood flow velocity V(t) of the corresponding stage are extracted based on the sampled video. d. Based on D(t), V(t), and D baseline With V baselineThe fundus vascular response parameters for the corresponding stage are calculated. These parameters include the vessel diameter variation coefficient Kd(t) and the blood perfusion index PI(t). The blood perfusion index PI(t) further undergoes time window averaging to obtain the average blood perfusion index PI for the corresponding stage. avg ; e. With PI avg The comparison result with the preset target interval is used as the main closed-loop discrimination criterion, and Kd(t) is used to adjust at least one treatment parameter in the closed loop. The treatment parameters include at least one of the peak power, pulse frequency, and duty cycle of the treatment optical channel at the corresponding stage, and / or the duration of the corresponding stage; the duration of the corresponding stage includes parameters used to obtain the PI. avg The duration of the corresponding therapeutic output phase in T1 to T3, and / or the duration of the T4 relaxation phase used for relaxation regulation.

[0013] Preferably, the dynamic closed-loop fundus photobiological modulation system further includes: an optical path shaping component and an optical path coupling component; wherein, The optical path shaping component is disposed on the light output path of the treatment light channel of the light source module, and is used to shape the treatment light into a light spot with a relatively uniform irradiation distribution and project it onto the target treatment area of ​​the fundus; the optical path shaping component adopts any one of the following: diffuse reflection homogenizer, diffuse reflection cavity, microlens array, compound eye lens and diffractive optical element; The optical path coupling component is located at the intersection of the treatment optical path and the imaging optical path, and is used to couple the treatment light to the imaging optical path, while allowing the fundus reflected light to enter the fundus camera module; the optical path coupling component adopts any one of the following: a semi-transparent mirror, a polarizing beam splitter, a non-polarizing beam splitter, and an adjustable beam splitter.

[0014] Preferably, the at least two independently controllable therapeutic light channels include a channel combination consisting of at least two of the following: a green light channel, a yellow-orange light channel, a red light channel, and a near-infrared channel.

[0015] The channel combinations include: a two-channel combination consisting of any two channels from the green light channel, yellow-orange light channel, red light channel, and near-infrared channel; a three-channel combination consisting of any three channels; or a four-channel combination consisting of all four channels.

[0016] As a further preferred embodiment, within one treatment cycle, the control module selects any one of the following preferred timing output modes based on the channel combination: When the channel combination is a two-channel combination consisting of a red light channel and a near-infrared channel, during the T1 start-up period, the red light channel outputs continuously or in pulse modulation mode; during the T2 activation period, the red light channel and the near-infrared channel output in a preset alternating time sequence; and during the effective output time slice of any treatment light channel, the treatment light channel outputs continuously or in pulse modulation mode; during the T3 inhibition period, the near-infrared channel outputs continuously or in pulse modulation mode; and during the T4 relaxation period, there is no light output at all. When the channel combination is a three-channel combination consisting of a yellow-orange light channel, a red light channel, and a near-infrared light channel, the yellow-orange light channel outputs continuously or in pulse modulation mode during the T1 start-up period, the red light channel and the near-infrared light channel output in a preset alternating time sequence during the T2 activation period, and the therapeutic light channel outputs continuously or in pulse modulation mode within the effective output time slice of any therapeutic light channel, the yellow-orange light channel outputs continuously or in pulse modulation mode during the T3 inhibition period, and the yellow-orange light channel outputs continuously or in pulse modulation mode during the T4 relaxation period, and there is no light output at all. When the channel combination is a four-channel combination consisting of a green light channel, a yellow-orange light channel, a red light channel, and a near-infrared light channel, the green light channel outputs continuously or in pulse modulation mode during the T1 start-up period. During the T2 activation period, the yellow-orange light channel and the near-infrared light channel output in a preset alternating time sequence. Within the effective output time slice of any treatment light channel, the treatment light channel outputs continuously or in pulse modulation mode. During the T3 inhibition period, the red light channel outputs continuously or in pulse modulation mode. During the T4 relaxation period, there is no light output at all.

[0017] Preferably, the green light channel is located in the green light band of 500-560nm; the yellow-orange light channel is located in the yellow-orange light band of 570-620nm; the red light channel is located in the red light band of 620-700nm; and the near-infrared channel is located in the near-infrared band of 780-950nm.

[0018] Preferably, the blood vessel diameter variation coefficient Kd(t) satisfies: Kd(t)=[D(t)- D baseline ] / D baseline ×100%; The blood perfusion index PI(t) satisfies: PI(t) = [V(t)·A(t)] / [V baseline ·A baseline ], Where A(t) is the approximate value of the blood vessel cross-sectional area obtained from D(t): A(t) = π × (D(t) / 2) 2 ; A baseline For D baselineThe approximate value of the cross-sectional area of ​​the blood vessel is obtained, and A baseline =π×(D baseline / 2) 2 .

[0019] Preferably, the control module obtains D baseline When dealing with D(t), the width of the blood vessel pixels is converted into the physical size based on preset calibration parameters to obtain the blood vessel diameter.

[0020] Preferably, the time window consists of at least two consecutive treatment cycles, including either the initial treatment cycle or a treatment cycle adjusted via closed-loop control. The control module averages the blood perfusion index PI(t) obtained at corresponding stages within multiple treatment cycles to obtain the average blood perfusion index PI for each stage. avg .

[0021] Preferably, the control module performs closed-loop discrimination according to the following priority order: When PI avg If the value exceeds the upper limit of the preset target range, or if Kd(t) exceeds the preset safety limit, the control module determines that the response is excessive and reduces at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel, and / or shortens the duration of the corresponding treatment output stage, and / or extends the duration of the T4 relaxation period. When the over-response condition is not met, when PI avg If the value is lower than the lower limit of the preset target range, or if Kd(t)≤0, the control module determines that the response is insufficient and increases at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel, and / or extends the duration of the corresponding treatment output stage. When PI is not met, the conditions for over-response and under-response are not satisfied. avg When the treatment parameters are within the preset target range and 0 < Kd(t) ≤ the preset safety upper limit, the control module maintains the current treatment parameters.

[0022] In one specific implementation, the preset target range is 1.2 ≤ PI_avg ≤ 1.5, and the preset safety upper limit is 12%. When PI avg When the value is >1.5 or Kd(t) >12%, the control module determines that the response is excessive and adjusts at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel in a preset step, and / or shortens the duration of the corresponding treatment output stage, and / or prolongs the duration of the T4 relaxation period. When the over-response condition is not met, when PI avgWhen <1.2 or Kd(t)≤0, the control module determines that the response is insufficient and increases at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel in a preset step, and / or extends the duration of the corresponding treatment output stage. Without satisfying the over-response and under-response conditions, when 1.2 ≤ PI avg When ≤1.5 and 0<Kd(t)≤12%, the control module maintains the current treatment parameters.

[0023] On the other hand, the present invention also provides a closed-loop control device for controlling the above-mentioned dynamic closed-loop fundus photobiological modulation system, comprising a processor and a memory, wherein the memory stores a computer program, and when the computer program is executed by the processor, the processor performs the following operations: Generate treatment timing control instructions from T1 to T4 based on the selected channel combination; During the baseline acquisition and treatment sampling phases, camera synchronization trigger commands are generated to enable the fundus camera module to acquire images when the treatment light is used as the imaging illumination light. Calculate Kd(t), PI(t), and PI based on the acquired images. avg ; According to PI avg The comparison results with the preset target range are combined with Kd(t) to generate treatment parameter adjustment instructions for adjusting at least one of the peak power, pulse frequency and duty cycle of the treatment light channel in the corresponding stage, and / or adjusting the duration of the corresponding stage.

[0024] The dynamic closed-loop fundus photobiomodulation system of this invention can be used for the control of treatment parameters, monitoring of tissue response, and quantitative evaluation during fundus photobiomodulation. Applicable scenarios include, but are not limited to, the adjunctive treatment of fundus diseases such as dry age-related macular degeneration, diabetic macular edema, wet age-related macular degeneration, glaucoma, retinal vein occlusion, and fundus lesions of high myopia.

[0025] The beneficial effects of this invention are: 1. This invention uses the therapeutic light as the imaging illumination light of the fundus camera module, so that both the baseline acquisition stage and the treatment sampling stage can be based on the area irradiated by the therapeutic light. This helps to reduce the optical path registration error caused by additional diagnostic light sources or independent monitoring optical paths, and keeps the monitoring area and the area irradiated by the therapeutic light in correspondence.

[0026] 2. This invention acquires a baseline video sequence before treatment to obtain the baseline vessel diameter D. baseline Compared with baseline blood flow velocity V baselineDuring treatment, simultaneous exposure sampling was performed to obtain real-time vessel diameter D(t) and real-time blood flow velocity V(t), and Kd(t), PI(t), and PI were further calculated. avg This transforms the closed-loop control from relying on a single preset treatment parameter to using quantitative feedback parameters based on fundus vascular responses, which helps improve the targeted nature of treatment parameter adjustments.

[0027] 3. This invention uses PI avg The comparison result with the preset target interval is used as the basis for the main closed-loop discrimination, and Kd(t) is combined to determine the safety or response state; when PI avg When the value exceeds the upper limit of the preset target range or Kd(t) exceeds the preset safety limit, the control module determines it as an over-response and reduces at least one of the peak power, pulse frequency, and duty cycle of the corresponding treatment optical channel, and / or shortens the duration of the corresponding treatment output phase, and / or extends the duration of the T4 relaxation period; when PI avg When the value is below the lower limit of the preset target range or Kd(t) ≤ 0, the control module determines that the response is insufficient and increases at least one of the peak power, pulse frequency, and duty cycle of the corresponding treatment optical channel, and / or extends the duration of the corresponding treatment output stage; when PI avg When the treatment parameters are within the preset target range and 0 < Kd(t) ≤ preset safety upper limit, the control module maintains the current treatment parameters, thus forming a dynamic closed-loop adjustment that matches the tissue response. Through this closed-loop adjustment, the control module can appropriately increase the treatment output when the fundus vascular response is insufficient, and promptly reduce the treatment output or prolong the relaxation time when the fundus vascular response is excessive, thereby avoiding the risk of insufficient response or excessive irradiation caused by long-term fixed treatment parameters.

[0028] 4. This invention sets up a T1 initiation period, a T2 activation period, a T3 inhibition period, and a T4 relaxation period within each treatment cycle. Treatment light is output during stages T1 to T3, but not during stage T4. Furthermore, during the T2 activation period, different treatment light channels can output light in a pre-set alternating sequence, allowing different wavelengths of treatment light to act at different times, avoiding continuous superposition of multiple wavelengths of treatment light at the same time. Further, through multi-stage treatment timing, the alternating output method of the T2 stage, and PI... avg The dynamic adjustment of Kd closed-loop discrimination, peak power, pulse frequency, duty cycle and / or stage duration, and T4 relaxation period regulation work together to enable the treatment output to change dynamically with the fundus vascular response. This helps to reduce the risks of local over-irradiation, local light dose superposition and heat accumulation caused by continuous irradiation with fixed parameters, and improves the tissue tolerance and safety control margin of the staged irradiation process.

[0029] 5. This invention forms different configuration levels through any two-channel combination, any three-channel combination, and any four-channel combination of green light channel, yellow-orange light channel, red light channel, and near-infrared channel. Furthermore, through the preferred two-channel combination of red light channel and near-infrared channel, the preferred three-channel combination of yellow-orange light channel, red light channel, and near-infrared channel, and the preferred four-channel combination of green light channel, yellow-orange light channel, red light channel, and near-infrared channel, it realizes the staged treatment output and closed-loop adjustment under different hardware complexities and treatment needs, taking into account the system scalability and implementation flexibility.

[0030] 6. By incorporating an optical path shaping component, this invention helps improve the uniformity of irradiation of the therapeutic light in the target treatment area of ​​the fundus; by incorporating an optical path coupling component, it facilitates the coupling of the therapeutic optical path and the imaging optical path, enabling the projection of the therapeutic light and the acquisition of the reflected light from the fundus to be realized in the same system optical path. Attached Figure Description

[0031] Figure 1 This is a system structure block diagram of a preferred embodiment of the present invention; Figure 2 This is a schematic diagram of the output and timing sampling of each treatment optical channel in a four-channel embodiment of the present invention with an initial treatment cycle of 100 s; Figure 3 This is a schematic diagram of the closed-loop feedback control process of the present invention.

[0032] Figure 4 This is a schematic diagram showing the positions of the light source module and the fundus camera module when there are no optical path components, with a four-channel arrangement as an example.

[0033] Among them, 110-control module, 120-light source module, 121-first treatment light channel Ch1, 122-second treatment light channel Ch2, 123-third treatment light channel Ch3, 124-fourth treatment light channel Ch4, 130-optical path shaping component, 131-diffuse reflection homogenizer, 140-optical path coupling component, 141-semi-transparent and semi-reflective mirror, 150-fundus camera module, and 160-image processing unit. Detailed Implementation

[0034] The present invention will now be described in further detail with reference to the accompanying drawings and specific embodiments. It should be understood that the specific embodiments described herein are for illustrative purposes only and are not intended to limit the scope of protection of the invention. Where there is no conflict, the technical features in the following embodiments can be combined with each other.

[0035] In this invention, a "therapeutic light channel" refers to a controllable output channel that can output specific wavelength therapeutic light for fundus photobiological modulation under the control of the control module 110. The therapeutic light channel can be formed by physically independent light source devices, or by a single light source combined with a spectral selection structure. In embodiments employing physically independent light source devices, each therapeutic light channel can be composed of an LED, laser diode, superluminescent diode, or other light source devices capable of outputting therapeutic light of the corresponding wavelength, and its illumination state, peak power, pulse frequency, duty cycle, and corresponding stage duration can be independently controlled by the control module 110.

[0036] In this invention, "baseline imaging illumination mode" refers to an imaging illumination mode in which at least one treatment optical channel is illuminated before treatment begins to obtain a baseline fundus vascular image. This mode is used for image acquisition rather than for treatment output, and its output power is lower than the peak power of the treatment optical channel during the treatment output phase. The specific output power under the baseline imaging illumination mode can be set according to the photosensitivity of the fundus camera module, exposure time, fundus reflection signal intensity, and safety control requirements.

[0037] In this invention, "corresponding stage" refers to obtaining the average value of the corresponding blood perfusion index PI. avg The treatment output phase. For the T1 initiation phase, T2 activation phase, and T3 inhibition phase, the duration of the corresponding phase is the duration of the corresponding treatment output phase; for the T4 relaxation phase, the duration of the corresponding phase is the duration of the light-free output phase used for relaxation regulation. The control module can adjust the PI according to the treatment output phase. avg Based on the comparison results with the preset target range, and combined with the blood vessel diameter change coefficient Kd(t), at least one of the peak power, pulse frequency, and duty cycle of the treatment optical channel in the corresponding stage, and / or the duration of the corresponding stage, is adjusted.

[0038] Example 1: A preferred embodiment is a four-channel optical path shaping component and an optical path coupling component. I. System Overall Structure and Connection Relationships The following description, in conjunction with the accompanying drawings, further illustrates this embodiment.

[0039] like Figure 1 As shown, this embodiment provides a dynamic closed-loop fundus photobiological modulation system, including a control module 110, a light source module 120, an optical path shaping component 130, an optical path coupling component 140, a fundus camera module 150, and an image processing unit 160. The image processing unit 160 can be set as an independent module or integrated into the control module 110.

[0040] The light source module 120 has four independently controllable therapeutic light channels, namely: The first therapeutic light channel, Ch1 121, is a 510 nm green LED; The second therapeutic light channel, Ch2 122, is a 590 nm yellow-orange LED; The third therapeutic light channel, Ch3 123, is a 660 nm red LED; The fourth therapeutic light channel, Ch4 124, is an 850 nm near-infrared LED.

[0041] In this embodiment, the first treatment light channel Ch1 121 is a green light channel, the second treatment light channel Ch2 122 is a yellow-orange light channel, the third treatment light channel Ch3 123 is a red light channel, and the fourth treatment light channel Ch4 124 is a near-infrared channel. Each treatment light channel is controlled by an independent constant current drive circuit. As an example, the output power adjustment range of each treatment light channel can be 0-50 mW, and the wavelength error can be no greater than ±5 nm; the above values ​​are only specific implementation methods of this embodiment and do not constitute a limitation on the scope of protection of this invention.

[0042] Furthermore, the four independently controllable therapeutic light channels can be implemented in a variety of ways.

[0043] In one implementation, four independently controllable sub-light sources are integrated into the same light bead unit. The light source module 120 includes multiple such light bead units, which can be distributed around the fundus camera module 150, such as... Figure 4 As shown. The four sub-light sources in each light bead unit correspond to the first treatment light channel Ch1 121, the second treatment light channel Ch2 122, the third treatment light channel Ch3 123 and the fourth treatment light channel Ch4 124 respectively, and are electrically connected to the control module 110 respectively, so that the control module 110 can control the lighting state and output parameters of each sub-light source respectively.

[0044] In another implementation, the light source module 120 may also include a broadband light source and an adjustable filter, wherein the adjustable filter is disposed in the light output path of the broadband light source. The control module 110 controls the transmission band, transmittance, and / or switching sequence of the adjustable filter to enable the broadband light source to selectively output therapeutic light of different therapeutic bands, thereby forming multiple independently controllable therapeutic light channels corresponding to different therapeutic bands.

[0045] The optical path shaping component 130 is disposed on the light output path of the four treatment optical channels. In this embodiment, a diffuse reflection homogenizer 131 is used to shape the treatment light emitted from the four treatment optical channels into a more uniformly distributed light spot and project it onto the target treatment area of ​​the fundus. The diffuse reflection homogenizer 131 can improve the uniformity of illumination within the target treatment area of ​​the fundus and reduce the impact of local light intensity distribution differences on subsequent image sampling and loop closure discrimination.

[0046] The optical path coupling component 140 is located at the intersection of the treatment optical path and the imaging optical path. In this embodiment, a semi-transparent mirror 141 is used to couple the treatment light to the imaging optical path, so that the treatment light is projected onto the patient's fundus along the imaging optical path, while the fundus reflected light enters the fundus camera module 150. The reflectivity and transmittance of the semi-transparent mirror 141 can be 50%; other combinations of reflectivity and transmittance can also be selected according to the intensity of the treatment light, the intensity of the fundus reflected signal, and the photosensitivity of the fundus camera module 150.

[0047] The fundus camera module 150 includes an imaging lens and an image sensor for acquiring images of fundus vessels when therapeutic light is used as imaging illumination. The image sensor can be a CMOS image sensor or a CCD image sensor. As an example, the fundus camera module 150 may have a resolution of 1920×1080 and a frame rate of 30fps; these parameters are merely an example configuration and do not limit the specific specifications of the fundus camera module 150.

[0048] The image processing unit 160 is connected to the fundus camera module 150 and the control module 110, and is used to preprocess fundus images or fundus video sequences acquired by the fundus camera module 150, and calculate vessel diameter and blood flow velocity parameters. The preprocessing includes one or more of the following: denoising, brightness normalization, contrast enhancement, motion correction, and inter-frame registration. The vessel diameter and blood flow velocity parameters are used to further calculate the vessel diameter variation coefficient Kd(t), the blood perfusion index PI(t), and the average blood perfusion index PI. avg .

[0049] The control module 110 is connected to the light source module 120, the fundus camera module 150, and the image processing unit 160, respectively. It is used to control the peak power, pulse frequency, duty cycle, and timing of each stage within the treatment cycle of each treatment light channel, and generates treatment parameter adjustment instructions after closed-loop discrimination. The treatment parameters include at least one of the peak power, pulse frequency, and duty cycle of the treatment light channel in the corresponding stage, and / or the duration of the corresponding stage.

[0050] II. Realization of Optical Path Based on Same Source and Same Path like Figure 1 As shown, the therapeutic light emitted from the four therapeutic light channels Ch1 to Ch4 is first processed by the optical path shaping component 130 and then reaches the semi-transparent mirror 141. The therapeutic light is coupled into the imaging optical path by the semi-transparent mirror 141 and projected onto the fundus tissue or retina. The reflected light formed by the reflection of the fundus tissue returns to the semi-transparent mirror 141 and then enters the fundus camera module 150, thus forming a control link of "therapeutic light output-fundus imaging-image processing-closed-loop feedback".

[0051] In the baseline acquisition phase and the synchronous exposure sampling phase during treatment, this embodiment does not require the introduction of an additional diagnostic laser. Instead, it utilizes the therapeutic light output from the illuminated therapeutic light channel as the imaging illumination light for the fundus camera module 150. Since the area irradiated by the therapeutic light at least partially overlaps with the imaging field of view of the fundus camera module 150, the acquired fundus vascular images can establish a correspondence with the area affected by the therapeutic light, thereby providing an image data basis for subsequent closed-loop parameter tuning based on fundus vascular responses.

[0052] In this embodiment, the diffuse reflector 131 is used to shape the point or beam light emitted from the treatment light channel into a more uniformly distributed treatment light, thereby improving the uniformity of illumination within the target treatment area of ​​the fundus. The semi-transparent mirror 141 is used to couple the treatment light path and the imaging light path, allowing the treatment light to be projected onto the target treatment area of ​​the fundus, while simultaneously allowing reflected light from the fundus to be collected by the fundus camera module 150.

[0053] In the above embodiments, the optical path shaping component 130 may also be any one of a diffuse reflection cavity, a microlens array, a compound eye lens, and a diffractive optical element.

[0054] In the above embodiments, the optical path coupling component 140 may also be any one of a polarizing beam splitter, a non-polarizing beam splitter, and an adjustable beam splitter.

[0055] III. Treatment Procedures and Timeline Output like Figure 2 As shown, the control module 110 controls the output of the therapeutic light in a cyclical manner according to the treatment cycle. In this embodiment, 100s is used as an initial treatment cycle for illustration; this 100s treatment cycle and the duration of each stage below are only examples, and the control module 110 can update the duration of each stage according to the closed-loop adjustment results.

[0056] Within an initial treatment cycle, the control module 110 sequentially executes the T1 initiation phase, T2 activation phase, T3 inhibition phase, and T4 relaxation phase. Treatment light is output during phases T1 to T3, but not during phase T4.

[0057] Specifically, in the initial 100-second treatment cycle of this embodiment: The T1 start-up period is 0–15 s, during which only the first therapeutic light channel Ch1 121 outputs green light in either continuous output or pulse modulation mode; The T2 activation period is 15–65 s. The second treatment light channel Ch2 122 and the fourth treatment light channel Ch4 124 are output in a time-division manner according to a preset alternating time sequence. Within the effective output time slice of any treatment light channel, the treatment light channel outputs yellow-orange light and near-infrared light in a continuous output mode or a pulse modulation mode. The T3 inhibition period is 65–85 s, and only the third therapeutic light channel Ch3 123 outputs red light in either continuous output or pulse modulation mode; The T4 relaxation period is 85–100 s, resulting in complete darkness and no light output.

[0058] The complementary pulse mode can be as follows: the second treatment light channel Ch2 122 and the fourth treatment light channel Ch4 124 are output in a time-division manner according to a preset alternating time sequence. Within the effective output time slice of either treatment light channel, the treatment light channel outputs in either a continuous output mode or a pulse modulation mode, such that when the second treatment light channel Ch2 122 is lit, the fourth treatment light channel Ch4 124 is turned off, and when the second treatment light channel Ch2 122 is turned off, the fourth treatment light channel Ch4 124 is lit. The time slice length, pulse frequency, and duty cycle of the complementary pulse can be preset according to the treatment plan or updated based on the closed-loop feedback results.

[0059] During the T1 to T3 phases, when at least one treatment light channel is lit, the control module 110 triggers the fundus camera module 150 to perform synchronous exposure sampling so as to use the treatment light output from the lit treatment light channel as the imaging illumination light.

[0060] IV. Closed-loop feedback control process like Figure 3 As shown, the closed-loop control process in this embodiment includes establishing a baseline before treatment, synchronous sampling during treatment, extracting parameters through image processing, calculating Kd(t) and PI(t), and averaging PI(t) over a time window to obtain PI. avg and based on PI avg The treatment parameters are adjusted in a closed loop using Kd(t). For ease of understanding, the closed-loop feedback control process in this embodiment can be executed according to steps S0 to S7.

[0061] S0: Baseline establishment before treatment Before treatment begins, the control module 110 controls at least one treatment light channel in the light source module 120 to be lit according to the baseline imaging illumination mode, and drives the fundus camera module 150 to acquire the baseline video sequence.

[0062] The baseline imaging illumination mode is an illumination mode used for image acquisition rather than for treatment output, and its output power is lower than the peak power of the treatment light channel during the treatment output phase. As an example, the output power in the baseline imaging illumination mode can be 0.5 mW; this value is only an example, and the specific output power can be set according to the photosensitivity of the fundus camera module 150, the exposure time, and the intensity of the fundus reflection signal.

[0063] In this embodiment, the control module 110 can control the first treatment light channel Ch1 121 and / or the fourth treatment light channel Ch4 124 to be lit according to the baseline imaging illumination mode, or it can select any one or more treatment light channels from Ch1 to Ch4 to be lit according to the response spectrum of the fundus camera module 150 and the intensity of the fundus reflection signal.

[0064] In this embodiment, the fundus camera module 150 acquires a baseline video sequence lasting 5 seconds at a frame rate of 30 fps. The image processing unit 160 performs multi-frame averaging on the baseline video sequence and obtains the baseline vessel diameter D. baseline Compared with baseline blood flow velocity V baseline .

[0065] Specifically, baseline establishment may include the following steps: (1) The control module 110 instructs the light source module 120 to illuminate at least one treatment light channel according to the baseline imaging illumination mode; for example, only the first treatment light channel Ch1 121 is illuminated; (2) The fundus camera module 150 acquires a continuous video sequence, for example, 30 frames per second for 5 seconds; (3) The image processing unit 160 preprocesses the acquired image. The preprocessing includes at least one or more of the following: noise reduction, brightness normalization and contrast enhancement. The inventor declares that the preprocessing is a conventional image preprocessing method, which is no different from the conventional processing methods known to those skilled in the art and does not involve the core inventive problem of the present invention. Therefore, it will not be described in detail here.

[0066] (4) The image processing unit 160 performs blood vessel segmentation on the preprocessed image to obtain a retinal blood vessel region mask. In this embodiment, blood vessel segmentation is completed using a traditional image processing flow, or a trained blood vessel segmentation model can be used to complete blood vessel segmentation. (5) The image processing unit 160 extracts the center line of the target blood vessel segment within the segmented blood vessel area and establishes a normal profile at the corresponding position of the center line. The two sides of the blood vessel are determined according to the gray change or edge position of the normal profile, and the pixel value of the blood vessel width is obtained from the pixel distance between the two sides. (6) The image processing unit 160 calls the system preset calibration parameters to convert the blood vessel width pixel value into physical size and obtain the baseline blood vessel diameter D. baseline Among them, the preset calibration parameters include the correspondence between pixel size, imaging magnification, and field of view scale; (7) The image processing unit 160 extracts blood flow signals from the corresponding target blood vessel segments in consecutive image frames. For example, it obtains the relative blood flow velocity index by constructing a spatiotemporal image and estimating the displacement of adjacent frames, thereby obtaining the baseline blood flow velocity V. baselineIn an optional implementation, speckle contrast analysis can also be used to estimate relative blood flow velocity. (8) The image processing unit 160 averages the measurements over a continuous time period to obtain D. baseline With V baseline .

[0067] S1: Cyclic output of therapeutic light according to the treatment cycle. The control module 110 outputs therapeutic light in a cycle according to the treatment cycle, and executes the T1 initiation period, T2 activation period, T3 inhibition period and T4 relaxation period in sequence within each treatment cycle.

[0068] In this embodiment, with an initial treatment cycle of 100 s, during the T1 activation period, only the first treatment light channel Ch1 121 outputs light; during the T2 activation period, the second treatment light channel Ch2 122 and the fourth treatment light channel Ch4 124 output light alternately in a complementary pulse manner; during the T3 inhibition period, only the third treatment light channel Ch3 123 outputs light in a pulse modulation manner; and during the T4 relaxation period, there is no light output at all.

[0069] S2: Simultaneous Exposure Sampling During the T1 to T3 phases, when at least one treatment light channel is lit, the control module 110 sends a synchronous exposure trigger command to the fundus camera module 150 so that the fundus camera module 150 performs synchronous exposure sampling when the treatment light is used as the imaging illumination light.

[0070] In this embodiment, synchronous exposure sampling is performed when the first treatment light channel Ch1 121 is output during stage T1; synchronous exposure sampling is performed when the second treatment light channel Ch2 122 and / or the fourth treatment light channel Ch4 124 is output during stage T2; and synchronous exposure sampling is performed when the third treatment light channel Ch3 123 is output during stage T3.

[0071] S3: Image Processing Extraction Parameters Image frames or video sequences obtained from synchronous exposure sampling are sent to the image processing unit 160 in real time. The image processing unit 160 performs vessel segmentation, calibration and feature extraction on them, and outputs the real-time vessel diameter D(t) and real-time blood flow velocity V(t) corresponding to each stage from T1 to T3.

[0072] For stages T1, T2, and T3, the image processing unit 160 can generate D(t) and V(t) for the corresponding stages, respectively, for subsequent calculation of Kd(t), PI(t), and PI for the corresponding stages. avg .

[0073] S4: Calculate feedback quantity The image processing unit 160 obtains D(t) and V(t) corresponding to each stage from T1 to T3, and combines them with D baselineWith V baseline The coefficient of change in vessel diameter Kd(t) and the perfusion index PI(t) were calculated.

[0074] The coefficient of change in vessel diameter, Kd(t), satisfies: Kd(t)=[D(t)- D baseline ] / D baseline ×100%.

[0075] The blood perfusion index PI(t) satisfies: PI(t) = [V(t)·A(t)] / [V baseline ·A baseline ].

[0076] Where A(t) is an approximate value of the blood vessel cross-sectional area obtained from D(t): A(t)=π×(D(t) / 2) 2 ; A baseline For D baseline Approximate cross-sectional area of ​​the blood vessel obtained: A baseline =π×(D baseline / 2) 2 .

[0077] S5: Average over a time window To reduce the impact of single-frame image noise, eye micro-movements, physiological vascular pulsations, or transient blood flow fluctuations on the closed-loop discrimination results, the control module 110 performs time-window averaging on PI(t) to obtain the average blood perfusion index PI for the corresponding stage. avg .

[0078] In this embodiment, the time window is defined as at least two consecutive treatment cycles, including either the initial treatment cycle or a closed-loop adjusted treatment cycle. The control module 110 averages the blood perfusion index PI(t) obtained at corresponding stages within multiple treatment cycles to obtain the average blood perfusion index PI for the corresponding stage. avg .

[0079] For example, the control module 110 can average the PI(t) obtained in stage T1 over two consecutive treatment cycles to obtain the PI corresponding to stage T1. avg The average of the PI(t) obtained in phase T2 over two consecutive treatment cycles is used to obtain the PI corresponding to phase T2. avg The average of the PI(t) obtained in the T3 phase over two consecutive treatment cycles is used to obtain the PI corresponding to the T3 phase. avg .

[0080] It should be noted that in this embodiment, PIavg As the primary criterion for loop closure, it is used to reduce the impact of blood flow velocity fluctuations, eye movements, or noise in single-frame images on perfusion status assessment. Kd(t) serves as an auxiliary discriminant and safety constraint, and can be the vessel diameter change coefficient at the current effective sampling time, or the maximum value, the last effective value, or the average value within the same time window as a representative value for the stage. For ease of description, the vessel diameter change coefficient participating in the loop closure assessment will be uniformly referred to as Kd(t) below.

[0081] S6: Loop Closure Detection and Parameter Tuning Control module 110 uses PI avg The comparison result with the preset target interval serves as the main closed-loop discrimination criterion, and is combined with Kd(t) to perform closed-loop adjustment of at least one treatment parameter. The treatment parameter includes at least one of the peak power, pulse frequency, and duty cycle of the treatment optical channel at the corresponding stage, and / or the duration of the corresponding stage. The duration of the corresponding stage includes the parameters used to obtain the PI. avg The duration of the corresponding therapeutic output phase in T1 to T3, and / or the duration of the T4 relaxation phase used for relaxation regulation.

[0082] In this embodiment, the preset target interval is 1.2 ≤ PI. avg ≤1.5, with a preset safety limit of 12%.

[0083] Control module 110 performs closed-loop discrimination according to the following priority order: When PI avg When the value is greater than 1.5 or Kd(t) is greater than 12%, the control module 110 determines that the response is excessive and adjusts at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel according to the preset step, and / or shortens the duration of the corresponding treatment output stage, and / or prolongs the duration of the T4 relaxation period. When the over-response condition is not met, when PI avg When <1.2 or Kd(t)≤0, the control module 110 determines that the response is insufficient and increases at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel in a preset step, and / or extends the duration of the corresponding treatment output stage. Without satisfying the over-response and under-response conditions, when 1.2 ≤ PI avg When ≤1.5 and 0<Kd(t)≤12%, the control module 110 maintains the current treatment parameters.

[0084] In particular, prolonging the duration of T4 relaxation can manifest as prolonging the duration of total darkness within the current treatment cycle.

[0085] In this embodiment, the initial treatment parameters are: T1 initiation phase: The peak power of the first treatment light channel Ch1 121 is 5-10 mW, and the duty cycle is 100%; T2 activation period: The peak power of the second treatment light channel Ch2 122 is 10-20 mW, the peak power of the fourth treatment light channel Ch4 124 is 15-25 mW, the duty cycle is 50%, and the pulse frequency is 1 Hz; T3 inhibition phase: The peak power of the third therapeutic optical channel Ch3 123 is 5-10 mW, and the duty cycle is 70%; T4 relaxation period: Complete darkness with no light output.

[0086] The above initial treatment parameters are merely examples; the control module 110 can adjust them according to the PI. avg The comparison results with the preset target interval, combined with Kd(t), are used to update at least one of the peak power, pulse frequency, and duty cycle of the treatment optical channel at the corresponding stage, and / or the duration of the corresponding stage in subsequent treatment cycles.

[0087] S7: Entering the next cycle The control module 110 applies the updated treatment parameters to subsequent treatment cycles and repeats steps S1 to S6.

[0088] At the end of the treatment, the control module 110 shuts down all treatment light channels and saves the treatment parameters, sampling data and closed-loop adjustment records during the treatment process.

[0089] Example 2: Four-channel + optical path-free component It should be noted that, Figure 4 Taking a four-channel arrangement as an example, the positional relationship between the light source module 120 and the fundus camera module 150 is shown when there is no optical path component. In the three-channel combination or two-channel combination embodiments, only the treatment light channel in the corresponding channel combination can be set under the same or similar arrangement, or the unused treatment light channel can be omitted.

[0090] like Figure 4 As shown, this embodiment provides a dynamic closed-loop fundus photobiological modulation system without the optical path shaping component 130 and the optical path coupling component 140. The system of this embodiment includes a control module 110, a light source module 120, a fundus camera module 150, and an image processing unit 160. The image processing unit 160 can be set as an independent module or integrated into the control module 110.

[0091] Compared with Embodiment 1, the difference in this embodiment is that: in this embodiment, the optical path shaping component 130 and the optical path coupling component 140 are not provided. The treatment light channel of the light source module 120 and the fundus camera module 150 are arranged in a coaxial, near-coaxial or surrounding manner, so that the imaging field of view of the fundus camera module 150 and the treatment light irradiation area at least partially overlap.

[0092] In this embodiment, the fundus camera module 150 is disposed in the center of the light source module 120, and each treatment light channel in the light source module 120 is arranged around the fundus camera module 150. The treatment light output from the treatment light channel is directly projected onto the target treatment area of ​​the patient's fundus, and the reflected light formed by the reflection of the fundus tissue is collected by the fundus camera module 150. Thus, even without the optical path coupling component 140, the treatment light irradiation area can still at least partially overlap with the imaging field of view of the fundus camera module 150.

[0093] In this embodiment, the light source module 120 has four independently controllable therapeutic light channels, namely: The first therapeutic light channel, Ch1 121, is a 510 nm green LED; The second therapeutic light channel, Ch2 122, is a 590 nm yellow-orange LED; The third therapeutic light channel, Ch3 123, is a 660 nm red LED; The fourth therapeutic light channel, Ch4 124, is an 850 nm near-infrared LED.

[0094] Among them, the first treatment light channel Ch1 121 is a green light channel, the second treatment light channel Ch2 122 is a yellow-orange light channel, the third treatment light channel Ch3 123 is a red light channel, and the fourth treatment light channel Ch4 124 is a near-infrared channel. Each treatment light channel can be controlled by an independent constant current drive circuit, and the control module 110 controls its lighting state, peak power, pulse frequency, duty cycle, and corresponding stage duration, respectively.

[0095] The control module 110 controls the output of the therapeutic light in a cyclical manner according to the treatment cycle. In this embodiment, 100 seconds is used as an initial treatment cycle for illustration; this 100-second treatment cycle and the duration of each stage are only examples, and the control module 110 can update the duration of each stage based on the closed-loop adjustment results.

[0096] Within an initial treatment cycle, control module 110 sequentially executes the T1 initiation phase, T2 activation phase, T3 inhibition phase, and T4 relaxation phase. Specifically: The T1 start-up period is 0–15 s, during which only the first therapeutic light channel Ch1 121 outputs green light in either continuous output or pulse modulation mode; The T2 activation period is 15–65 s. The second treatment light channel Ch2 122 and the fourth treatment light channel Ch4 124 are output in a time-division manner according to a preset alternating time sequence. Within the effective output time slice of any treatment light channel, the treatment light channel outputs yellow-orange light and near-infrared light in a continuous output mode or a pulse modulation mode. The T3 inhibition period is 65–85 s, and only the third therapeutic light channel Ch3 123 outputs red light in either continuous output or pulse modulation mode; The T4 relaxation period is 85–100 s, resulting in complete darkness and no light output.

[0097] The complementary pulse mode can be as follows: the second treatment light channel Ch2 122 and the fourth treatment light channel Ch4 124 are output in a time-division manner according to a preset alternating time sequence. Within the effective output time slice of either treatment light channel, the treatment light channel outputs in either a continuous output mode or a pulse modulation mode, such that when the second treatment light channel Ch2 122 is lit, the fourth treatment light channel Ch4 124 is turned off, and when the second treatment light channel Ch2 122 is turned off, the fourth treatment light channel Ch4 124 is lit. The time slice length, pulse frequency, and duty cycle of the complementary pulse can be preset according to the treatment plan or updated based on the closed-loop feedback results.

[0098] Before treatment begins, the control module 110 controls at least one treatment light channel in the light source module 120 to illuminate according to the baseline imaging illumination mode, and drives the fundus camera module 150 to acquire the baseline video sequence. The baseline imaging illumination mode is an illumination mode used for image acquisition rather than for treatment output, and its output power is lower than the peak power of the treatment light channel during the treatment output phase.

[0099] In this embodiment, the control module 110 can control the first treatment light channel Ch1 121 and / or the fourth treatment light channel Ch4 124 to be lit according to the baseline imaging illumination mode; it can also select any one or more treatment light channels from Ch1 to Ch4 to be lit according to the response spectrum, exposure time, and fundus reflection signal intensity of the fundus camera module 150.

[0100] The fundus camera module 150 acquires a baseline video sequence in baseline imaging illumination mode. The image processing unit 160 preprocesses the baseline video sequence, segments blood vessels, measures blood vessel width, and estimates blood flow velocity to obtain the baseline blood vessel diameter D. baseline Compared with baseline blood flow velocity V baselinePreprocessing can include one or more of the following: denoising, brightness normalization, contrast enhancement, motion correction, and inter-frame registration; vessel width measurement can be achieved by extracting the centerline of the target vessel segment, establishing a normal profile, and identifying the boundaries on both sides of the vessel; blood flow velocity estimation can be performed using inter-frame displacement analysis based on spatiotemporal images, or it can be performed using speckle contrast analysis.

[0101] During the treatment process, in the T1 to T3 phases, when at least one treatment light channel is lit, the control module 110 sends a synchronous exposure trigger command to the fundus camera module 150, so that the fundus camera module 150 performs synchronous exposure sampling when the treatment light is used as the imaging illumination light.

[0102] In this embodiment, synchronous exposure sampling can be performed in stage T1 when the first treatment light channel Ch1 121 is lit; synchronous exposure sampling can be performed in stage T2 when the second treatment light channel Ch2 122 and / or the fourth treatment light channel Ch4 124 is lit; and synchronous exposure sampling can be performed in stage T3 when the third treatment light channel Ch3 123 is lit. The sampled image frames or video sequences are sent to the image processing unit 160, which extracts the real-time blood vessel diameter D(t) and real-time blood flow velocity V(t) for the corresponding stage.

[0103] Image processing unit 160 based on D(t), V(t), D baseline With V baseline Calculate the vessel diameter change coefficient Kd(t) and blood perfusion index PI(t) for the corresponding stage.

[0104] The blood vessel diameter variation coefficient Kd(t) satisfies: Kd(t)=[D(t)- D baseline ] / D baseline ×100%.

[0105] The blood perfusion index PI(t) satisfies: PI(t) = [V(t)·A(t)] / [V baseline ·A baseline ].

[0106] Where A(t) is an approximate value of the blood vessel cross-sectional area obtained from D(t): A(t)=π×(D(t) / 2) 2 ; A baseline For D baseline Approximate cross-sectional area of ​​the blood vessel obtained: A baseline =π×(D baseline / 2) 2 .

[0107] The control module 110 performs a time-window averaging of the blood perfusion index PI(t) obtained at corresponding stages within multiple treatment cycles to obtain the average blood perfusion index PI for the corresponding stage. avg In this embodiment, the time window is at least two consecutive treatment cycles, and the treatment cycle includes the initial treatment cycle or the treatment cycle after closed-loop adjustment.

[0108] It should be noted that in this embodiment, PI avg As the primary criterion for loop closure, it is used to reduce the impact of blood flow velocity fluctuations, eye movements, or noise in single-frame images on perfusion status assessment. Kd(t) serves as an auxiliary discriminant and safety constraint, and can be the vessel diameter change coefficient at the current effective sampling time, or the maximum value, the last effective value, or the average value within the same time window as a stage representative value. For ease of description, this embodiment uniformly uses Kd(t) to represent the vessel diameter change coefficient involved in loop closure assessment.

[0109] Control module 110 uses PI avg The comparison result with the preset target interval serves as the main closed-loop discrimination criterion, and is combined with Kd(t) to perform closed-loop adjustment of at least one treatment parameter. The treatment parameters include at least one of the peak power, pulse frequency, and duty cycle of the treatment optical channel at the corresponding stage, and / or the duration of the corresponding stage. The duration of the corresponding stage includes the parameters used to obtain the PI. avg The duration of the corresponding therapeutic output phase in T1 to T3, and / or the duration of the T4 relaxation phase used for relaxation regulation.

[0110] In this embodiment, the preset target interval is 1.2 ≤ PI. avg ≤1.5, with a preset safety limit of 12%.

[0111] Control module 110 performs closed-loop discrimination according to the following priority order: When PI avg When the value is greater than 1.5 or Kd(t) is greater than 12%, the control module 110 determines that the response is excessive and adjusts at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel according to the preset step, and / or shortens the duration of the corresponding treatment output stage, and / or prolongs the duration of the T4 relaxation period. When the over-response condition is not met, when PI avg When <1.2 or Kd(t)≤0, the control module 110 determines that the response is insufficient and increases at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel in a preset step, and / or extends the duration of the corresponding treatment output stage. Without satisfying the over-response and under-response conditions, when 1.2 ≤ PIavg When ≤1.5 and 0<Kd(t)≤12%, the control module 110 maintains the current treatment parameters.

[0112] This embodiment illustrates that, even without the optical path shaping component 130 and the optical path coupling component 140, as long as the treatment light irradiation area of ​​the light source module 120 at least partially overlaps with the imaging field of view of the fundus camera module 150, and the treatment light output from the illuminated treatment light channel is used as the imaging illumination light during the baseline acquisition phase and the synchronous exposure sampling phase during treatment, baseline acquisition, synchronous treatment sampling, Kd(t) and PI(t) calculations, and PI... avg The time window averaging and closed-loop parameter tuning process are described. This embodiment is used to illustrate that the optical path shaping component 130 and the optical path coupling component 140 are optional structures, rather than necessary structures for realizing dynamic closed-loop control.

[0113] Example 3: Three-channel + optical path-free component This embodiment provides a three-channel dynamic closed-loop fundus photobiological modulation system. The system includes a control module 110, a light source module 120, a fundus camera module 150, and an image processing unit 160. The image processing unit 160 can be configured as an independent module or integrated within the control module 110.

[0114] Compared with Embodiment 2, the difference in this embodiment is that: the light source module 120 has three independently controllable treatment light channels, namely the yellow-orange light channel, the red light channel, and the near-infrared channel; this embodiment does not set the optical path shaping component 130 and the optical path coupling component 140, and the treatment light channel of the light source module 120 and the fundus camera module 150 are arranged coaxially, nearly coaxially, or around the fundus camera module 150, so that the imaging field of view of the fundus camera module 150 at least partially overlaps with the treatment light irradiation area.

[0115] In this embodiment, the three treatment light channels are as follows: Yellow-orange light channel, used to output 590 nm yellow-orange light; The red light channel is used to output 660 nm red light; Near-infrared channel, used to output 850 nm near-infrared light.

[0116] The yellow-orange light channel is located in the 570-620 nm yellow-orange light band, the red light channel is located in the 620-700 nm red light band, and the near-infrared channel is located in the 780-950 nm near-infrared band. The aforementioned 590 nm, 660 nm, and 850 nm are merely examples of preferred center wavelengths in this embodiment and do not constitute a limitation on the scope of protection of this invention.

[0117] The control module 110 is connected to the yellow-orange light channel, the red light channel and the near-infrared channel respectively, and is used to independently control the lighting status, peak power, pulse frequency, duty cycle and corresponding stage duration of each treatment light channel.

[0118] The control module 110 controls the output of the therapeutic light in a cyclical manner according to the treatment cycle. In this embodiment, 100 seconds is used as an initial treatment cycle for illustration; this 100-second treatment cycle and the duration of each stage are only examples, and the control module 110 can update the duration of each stage based on the closed-loop adjustment results.

[0119] Within an initial treatment cycle, control module 110 sequentially executes the T1 initiation phase, T2 activation phase, T3 inhibition phase, and T4 relaxation phase. Specifically: The T1 start-up period is 0–15 s, and only the yellow-orange light channel outputs 590 nm yellow-orange light in either continuous output or pulse modulation mode; The T2 activation period is 15–65 s. The red light channel and the near-infrared channel are output in a time-sharing manner according to a preset alternating sequence. Within the effective output time slot of any treatment light channel, the treatment light channel outputs 660 nm red light and 850 nm near-infrared light in a continuous output mode or a pulse modulation mode. The T3 suppression period is 65–85 s, and only the yellow-orange light channel outputs 590 nm yellow-orange light in either continuous output or pulse modulation mode; The T4 relaxation period is 85–100 s, resulting in complete darkness and no light output.

[0120] The complementary pulse mode can be implemented as follows: the red light channel and the near-infrared channel are output in a time-division manner according to a preset alternating sequence. Within the effective output time slice of any treatment light channel, the treatment light channel outputs in a continuous output mode or a pulse modulation mode, such that when the red light channel is lit, the near-infrared channel is turned off, and when the red light channel is turned off, the near-infrared channel is lit. The time slice length, pulse frequency, and duty cycle of the complementary pulse can be preset according to the treatment plan or updated based on the closed-loop feedback results.

[0121] Before treatment begins, the control module 110 controls at least one treatment light channel in the light source module 120 to illuminate according to the baseline imaging illumination mode, and drives the fundus camera module 150 to acquire the baseline video sequence. The baseline imaging illumination mode is an illumination mode used for image acquisition rather than for treatment output, and its output power is lower than the peak power of the treatment light channel during the treatment output phase.

[0122] In this embodiment, the control module 110 can control the yellow-orange light channel and / or the near-infrared channel to be lit according to the baseline imaging illumination mode; it can also select any one or more treatment light channels among the yellow-orange light channel, red light channel and near-infrared channel to be lit according to the response spectrum, exposure time and fundus reflection signal intensity of the fundus camera module 150.

[0123] The fundus camera module 150 acquires a baseline video sequence in baseline imaging illumination mode. The image processing unit 160 preprocesses the baseline video sequence, segments blood vessels, measures blood vessel width, and estimates blood flow velocity to obtain the baseline blood vessel diameter D. baseline Compared with baseline blood flow velocity V baseline .

[0124] Preprocessing may include one or more of the following: denoising, brightness normalization, contrast enhancement, motion correction, and inter-frame registration. Vessel width measurement can be achieved by extracting the centerline of the target vessel segment, establishing a normal profile, and identifying the vessel's lateral boundaries. Blood flow velocity estimation can employ inter-frame displacement analysis based on spatiotemporal images, or it can use speckle contrast analysis.

[0125] During the treatment process, in the T1 to T3 phases, when at least one treatment light channel is lit, the control module 110 sends a synchronous exposure trigger command to the fundus camera module 150, so that the fundus camera module 150 performs synchronous exposure sampling when the treatment light is used as the imaging illumination light.

[0126] In this embodiment, synchronous exposure sampling can be performed in stage T1 when the yellow-orange light channel is lit; synchronous exposure sampling can be performed in stage T2 when the red light channel and / or near-infrared channel is lit; and synchronous exposure sampling can be performed in stage T3 when the yellow-orange light channel is lit. The sampled image frames or video sequences are sent to the image processing unit 160, which extracts the real-time blood vessel diameter D(t) and real-time blood flow velocity V(t) for the corresponding stage.

[0127] Image processing unit 160 based on D(t), V(t), D baseline With V baseline Calculate the vessel diameter change coefficient Kd(t) and blood perfusion index PI(t) for the corresponding stage.

[0128] The blood vessel diameter variation coefficient Kd(t) satisfies: Kd(t)=[D(t)- D baseline ] / D baseline ×100%.

[0129] The blood perfusion index PI(t) satisfies: PI(t) = [V(t)·A(t)] / [V baseline ·Abaseline ].

[0130] Where A(t) is an approximate value of the blood vessel cross-sectional area obtained from D(t): A(t)=π×(D(t) / 2) 2 ; A baseline For D baseline Approximate cross-sectional area of ​​the blood vessel obtained: A baseline =π×(D baseline / 2) 2 .

[0131] The control module 110 performs a time-window averaging of the blood perfusion index PI(t) obtained at corresponding stages within multiple treatment cycles to obtain the average blood perfusion index PI for the corresponding stage. avg In this embodiment, the time window is at least two consecutive treatment cycles, including the initial treatment cycle or the treatment cycle after closed-loop adjustment.

[0132] It should be noted that in this embodiment, PI avg As the primary criterion for loop closure, it is used to reduce the impact of blood flow velocity fluctuations, eye movements, or noise in single-frame images on perfusion status assessment. Kd(t) serves as an auxiliary discriminant and safety constraint, and can be the vessel diameter change coefficient at the current effective sampling time, or the maximum value, the last effective value, or the average value within the same time window as a stage representative value. For ease of description, this embodiment uniformly uses Kd(t) to represent the vessel diameter change coefficient involved in loop closure assessment.

[0133] Control module 110 uses PI avg The comparison result with the preset target interval serves as the main closed-loop discrimination criterion, and is combined with Kd(t) to perform closed-loop adjustment of at least one treatment parameter. The treatment parameter includes at least one of the peak power, pulse frequency, and duty cycle of the treatment optical channel at the corresponding stage, and / or the duration of the corresponding stage. The duration of the corresponding stage includes the parameters used to obtain the PI. avg The duration of the corresponding therapeutic output phase in T1 to T3, and / or the duration of the T4 relaxation phase used for relaxation regulation.

[0134] In this embodiment, the preset target interval is 1.2 ≤ PI. avg ≤1.5, the preset safety upper limit is 12%.

[0135] Control module 110 performs closed-loop discrimination according to the following priority order: When PI avgWhen the value is greater than 1.5 or Kd(t) is greater than 12%, the control module 110 determines that the response is excessive and adjusts at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel according to the preset step, and / or shortens the duration of the corresponding treatment output stage, and / or prolongs the duration of the T4 relaxation period. When the over-response condition is not met, when PI avg When <1.2 or Kd(t)≤0, the control module 110 determines that the response is insufficient and increases at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel in a preset step, and / or extends the duration of the corresponding treatment output stage. Without satisfying the over-response and under-response conditions, when 1.2 ≤ PI avg When ≤1.5 and 0<Kd(t)≤12%, the control module 110 maintains the current treatment parameters.

[0136] In this embodiment, the initial treatment parameters can be: T1 startup phase: The peak power of the yellow-orange optical channel is 5-10 mW, and the duty cycle is 100%; T2 activation period: peak power of red channel is 10-20 mW, peak power of near-infrared channel is 15-25 mW, duty cycle is 50%, pulse frequency is 1 Hz; T3 suppression period: The peak power of the yellow-orange light channel is 5-10 mW, and the duty cycle is 70%; T4 relaxation period: Complete darkness with no light output.

[0137] The above initial treatment parameters are merely examples; the control module 110 can adjust them according to the PI. avg The comparison results with the preset target interval, combined with Kd(t), are used to update at least one of the peak power, pulse frequency, and duty cycle of the treatment optical channel at the corresponding stage, and / or the duration of the corresponding stage in subsequent treatment cycles.

[0138] This embodiment uses a three-channel output scheme consisting of a yellow-orange light channel, a red light channel, and a near-infrared light channel. This scheme can perform T1 to T4 staged output, therapeutic light synchronous imaging sampling, vascular quantitative parameter calculation, and closed-loop parameter tuning process with less than a four-channel hardware configuration.

[0139] Example 4: Two-channel + optical path-free component This embodiment provides a two-channel dynamic closed-loop fundus photobiological modulation system. The system includes a control module 110, a light source module 120, a fundus camera module 150, and an image processing unit 160. The image processing unit 160 can be configured as an independent module or integrated within the control module 110.

[0140] Compared with Embodiment 2, the difference in this embodiment is that: the light source module 120 has two independently controllable treatment light channels, namely the red light channel and the near-infrared channel; this embodiment does not set the optical path shaping component 130 and the optical path coupling component 140, and the treatment light channel of the light source module 120 and the fundus camera module 150 are arranged coaxially, nearly coaxially, or around the fundus camera module 150, so that the imaging field of view of the fundus camera module 150 at least partially overlaps with the treatment light irradiation area.

[0141] In one specific embodiment, the two therapeutic light channels are respectively: The red light channel is used to output 660 nm red light; Near-infrared channel, used to output 850 nm near-infrared light.

[0142] The red light channel is located in the red light band of 620-700 nm, and the near-infrared channel is located in the near-infrared band of 780-950 nm. The aforementioned 660 nm and 850 nm are merely examples of preferred center wavelengths in this embodiment and do not constitute a limitation on the scope of protection of this invention.

[0143] The control module 110 is connected to the red light channel and the near-infrared channel respectively, and is used to independently control the lighting status, peak power, pulse frequency, duty cycle and corresponding stage duration of each treatment light channel.

[0144] The control module 110 controls the output of the therapeutic light in a cyclical manner according to the treatment cycle. In this embodiment, 100 seconds is used as an initial treatment cycle for illustration; this 100-second treatment cycle and the duration of each stage are only examples, and the control module 110 can update the duration of each stage based on the closed-loop adjustment results.

[0145] Within an initial treatment cycle, control module 110 sequentially executes the T1 initiation phase, T2 activation phase, T3 inhibition phase, and T4 relaxation phase. Specifically: The T1 start-up period is 0–15 s, and only the red light channel outputs 660 nm red light in either continuous output or pulse modulation mode; The T2 activation period is 15–65 s. The red light channel and the near-infrared channel are output in a time-sharing manner according to a preset alternating sequence. Within the effective output time slot of any treatment light channel, the treatment light channel outputs 660 nm red light and 850 nm near-infrared light in a continuous output mode or a pulse modulation mode. The T3 suppression period is 65–85 s, and only the near-infrared channel outputs 850 nm near-infrared light in either continuous output or pulse modulation mode. The T4 relaxation period is 85–100 s, resulting in complete darkness and no light output.

[0146] Before treatment begins, the control module 110 controls the red light channel and / or near-infrared channel to illuminate according to the baseline imaging illumination mode, and drives the fundus camera module 150 to acquire a baseline video sequence, from which the baseline vessel diameter D is obtained. baseline Compared with baseline blood flow velocity V baseline .

[0147] During the treatment process, in the T1 to T3 stages, when the red light channel and / or near-infrared channel are lit, the control module 110 controls the fundus camera module 150 to perform synchronous exposure sampling, and extracts the real-time blood vessel diameter D(t) and real-time blood flow velocity V(t) of the corresponding stage based on the sampled video.

[0148] Control module 110 based on D(t), V(t), D baseline With V baseline The coefficient of change in vessel diameter Kd(t) and the perfusion index PI(t) for the corresponding stage were calculated, and the average perfusion index PI(t) was obtained by averaging PI(t) over a time window. avg .

[0149] Control module 110 uses PI avg The comparison result with the preset target interval serves as the main closed-loop discrimination criterion, and is combined with Kd(t) to perform closed-loop adjustment of at least one treatment parameter. The treatment parameters include at least one of the peak power, pulse frequency, and duty cycle of the treatment optical channel at the corresponding stage, and / or the duration of the corresponding stage. The duration of the corresponding stage includes the parameters used to obtain the PI. avg The duration of the corresponding therapeutic output phase in T1 to T3, and / or the duration of the T4 relaxation phase used for relaxation regulation.

[0150] In this embodiment, the preset target interval is 1.2 ≤ PI. avg ≤1.5, with a preset safety limit of 12%.

[0151] Control module 110 performs closed-loop discrimination according to the following priority order: When PI avg When the value is greater than 1.5 or Kd(t) is greater than 12%, the control module 110 determines that the response is excessive and adjusts at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel according to the preset step, and / or shortens the duration of the corresponding treatment output stage, and / or prolongs the duration of the T4 relaxation period. When the over-response condition is not met, when PI avg When <1.2 or Kd(t)≤0, the control module 110 determines that the response is insufficient and increases at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel in a preset step, and / or extends the duration of the corresponding treatment output stage. Without satisfying the over-response and under-response conditions, when 1.2 ≤ PI avg When ≤1.5 and 0<Kd(t)≤12%, the control module 110 maintains the current treatment parameters.

[0152] In this embodiment, the initial treatment parameters can be: T1 startup period: The peak power of the red light channel is 5-10 mW, and the duty cycle is 100%; T2 activation period: peak power of red channel is 10-20 mW, peak power of near-infrared channel is 15-25 mW, duty cycle is 50%, pulse frequency is 1 Hz; T3 suppression period: The peak power of the near-infrared channel is 5-10 mW, and the duty cycle is 70%; T4 relaxation period: Complete darkness with no light output.

[0153] The above initial treatment parameters are merely examples; the control module 110 can adjust them according to the PI. avg The comparison results with the preset target interval, combined with Kd(t), are used to update at least one of the peak power, pulse frequency, and duty cycle of the treatment optical channel at the corresponding stage, and / or the duration of the corresponding stage in subsequent treatment cycles.

[0154] This embodiment forms a two-channel output scheme through the red light channel and the near-infrared channel, which can perform T1 to T4 staged output, synchronous imaging sampling of therapeutic light, calculation of vascular quantitative parameters, and closed-loop parameter tuning process with a hardware configuration of at least two therapeutic light channels.

[0155] Example 5: Closed-loop control device This embodiment provides a closed-loop control device for controlling the aforementioned dynamic closed-loop fundus photobiological modulation system. The closed-loop control device can be used to control the dynamic closed-loop fundus photobiological modulation system described in any one of Embodiments 1 to 4.

[0156] The closed-loop control device includes a processor and a memory. The memory stores a computer program. When the computer program is executed by the processor, it enables the processor to perform timing control, camera synchronization triggering, image parameter calculation, and closed-loop adjustment of treatment parameters of the dynamic closed-loop fundus photobiological modulation system.

[0157] Specifically, when the processor executes the computer program, it generates treatment timing control instructions from T1 to T4, and controls the corresponding treatment light channel to output treatment light during the T1 start-up period, T2 activation period, T3 inhibition period, and T4 relaxation period according to the selected channel combination.

[0158] During the baseline acquisition phase, the closed-loop control device generates baseline acquisition control commands to illuminate at least one treatment light channel according to the baseline imaging illumination mode, and generates camera synchronization trigger commands to enable the fundus camera module to acquire baseline video sequences when the treatment light is used as imaging illumination light, in order to obtain the baseline vessel diameter D. baseline Compared with baseline blood flow velocity V baseline .

[0159] During the treatment sampling phase, the closed-loop control device generates treatment sampling control commands. During the T1 to T3 phases, when at least one treatment light channel is lit, a camera synchronization trigger command is generated, which enables the fundus camera module to perform synchronous exposure sampling when the treatment light is used as imaging illumination light, so as to obtain real-time blood vessel diameter D(t) and real-time blood flow velocity V(t).

[0160] The closed-loop control device calculates the vessel diameter change coefficient Kd(t), blood perfusion index PI(t), and average blood perfusion index PI_avg for the corresponding stage based on the acquired images.

[0161] Where Kd(t)=[D(t)- D baseline ] / D baseline ×100%; PI(t) = [V(t)·A(t)] / [V baseline ·A baseline ]; A(t) is an approximate value of the blood vessel cross-sectional area obtained from D(t), A(t) = π × (D(t) / 2) 2 ; A baseline For D baseline The approximate cross-sectional area of ​​the blood vessel obtained, A baseline =π×(D baseline / 2) 2 .

[0162] Closed-loop control device based on PI avg The comparison results with the preset target range are combined with Kd(t) to generate treatment parameter adjustment instructions for adjusting at least one of the peak power, pulse frequency and duty cycle of the treatment light channel in the corresponding stage, and / or adjusting the duration of the corresponding stage.

[0163] In this specific implementation, the preset target interval is 1.2 ≤ PI. avg ≤1.5, with a preset safety limit of 12%.

[0164] The closed-loop control device performs closed-loop determination in the following priority order: When PI avgWhen the value is greater than 1.5 or Kd(t) is greater than 12%, the closed-loop control device determines that the response is excessive and generates a treatment parameter adjustment command for reducing at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment optical channel, and / or shortening the duration of the corresponding treatment output stage, and / or extending the duration of the T4 relaxation period. When the over-response condition is not met, when PI avg When <1.2 or Kd(t)≤0, the closed-loop control device determines that the response is insufficient and generates a treatment parameter adjustment command for increasing at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment optical channel, and / or extending the duration of the corresponding treatment output stage; Without satisfying the over-response and under-response conditions, when 1.2 ≤ PI avg When ≤1.5 and 0<Kd(t)≤12%, the closed-loop control device generates control instructions to maintain the current treatment parameters.

[0165] In this specific embodiment, the closed-loop control device also includes a light source drive interface, a camera trigger interface, an image data input interface, and a parameter output interface.

[0166] Among them, the light source driver interface is used to output peak power, pulse frequency, duty cycle and lighting timing control signals to the light source module; The camera trigger interface is used to output an exposure trigger signal to the fundus camera module. The image data input interface is used to receive image frames or video sequences output by the fundus camera module. The parameter output interface is used to output Kd(t), PI(t), and PI. avg Treatment parameter adjustment records or treatment process records.

[0167] At the end of the treatment, the closed-loop control device shuts down each treatment light channel and saves the treatment sequence, image sampling data, feedback parameters, and treatment parameter adjustment records during the treatment process.

Claims

1. A dynamic closed-loop fundus photobiological modulation system, characterized in that, include: The light source module has at least two independently controllable therapeutic light channels; The fundus camera module is used to acquire images of fundus vessels when the therapeutic light is used as the imaging illumination light, so as to obtain parameters such as vessel diameter and blood flow velocity. The control module is connected to the light source module and the fundus camera module respectively, and is used to control the light source module to output therapeutic light cyclically according to the treatment cycle, and to execute the T1 initiation period, T2 activation period, T3 inhibition period and T4 relaxation period in each treatment cycle; wherein, there is therapeutic light output in the T1 to T3 stages, and no therapeutic light output in the T4 stage. The control module is also used in the baseline acquisition stage and the synchronous exposure sampling stage during the treatment process to use the treatment light output by the illuminated treatment light channel as the imaging illumination light of the fundus camera module, and to make the imaging field of view of the fundus camera module at least partially overlap with the treatment light irradiation area. The control module is also used to obtain baseline vascular parameters and real-time vascular parameters based on the fundus vascular image, determine fundus vascular response parameters based on the baseline vascular parameters and real-time vascular parameters, and perform closed-loop adjustment of at least one treatment parameter based on the fundus vascular response parameters. The treatment parameters include at least one of the peak power, pulse frequency, and duty cycle of the treatment optical channel at the corresponding stage, and / or the duration of the corresponding stage.

2. The system according to claim 1, characterized in that, It also includes optical path shaping components and optical path coupling components; The optical path shaping component is disposed on the light output path of the treatment light channel of the light source module, and is used to shape the treatment light into a light spot with a relatively uniform irradiation distribution and project it onto the target treatment area of ​​the fundus; the optical path shaping component adopts any one of the following: diffuse reflection homogenizer, diffuse reflection cavity, microlens array, compound eye lens and diffractive optical element; The optical path coupling component is located at the intersection of the treatment optical path and the imaging optical path, and is used to couple the treatment light to the imaging optical path, while allowing the fundus reflected light to enter the fundus camera module; the optical path coupling component adopts any one of the following: a semi-transparent mirror, a polarizing beam splitter, a non-polarizing beam splitter, and an adjustable beam splitter.

3. The dynamic closed-loop fundus photobiological modulation system according to claim 1 or 2, characterized in that, The at least two independently controllable therapeutic light channels include a channel combination consisting of at least two of the following: green light channel, yellow-orange light channel, red light channel, and near-infrared channel; The channel combinations include: a two-channel combination consisting of any two channels from the green light channel, yellow-orange light channel, red light channel, and near-infrared channel; a three-channel combination consisting of any three channels; or a four-channel combination consisting of all four channels.

4. The dynamic closed-loop fundus photobiological modulation system according to claim 3, characterized in that, Within one treatment cycle, the control module selects any one of the following preferred timing output modes based on the channel combination: When the channel combination is a two-channel combination consisting of a red light channel and a near-infrared channel, during the T1 start-up period, the red light channel outputs continuously or in pulse modulation mode; during the T2 activation period, the red light channel and the near-infrared channel output in a preset alternating time sequence; and during the effective output time slice of any treatment light channel, the treatment light channel outputs continuously or in pulse modulation mode; during the T3 inhibition period, the near-infrared channel outputs continuously or in pulse modulation mode; and during the T4 relaxation period, there is no light output at all. When the channel combination is a three-channel combination consisting of a yellow-orange light channel, a red light channel, and a near-infrared light channel, the yellow-orange light channel outputs continuously or in pulse modulation mode during the T1 start-up period, the red light channel and the near-infrared light channel output in a preset alternating time sequence during the T2 activation period, and the therapeutic light channel outputs continuously or in pulse modulation mode within the effective output time slice of any therapeutic light channel, the yellow-orange light channel outputs continuously or in pulse modulation mode during the T3 inhibition period, and the yellow-orange light channel outputs continuously or in pulse modulation mode during the T4 relaxation period, and there is no light output at all. When the channel combination is a four-channel combination consisting of a green light channel, a yellow-orange light channel, a red light channel, and a near-infrared light channel, the green light channel outputs continuously or in pulse modulation mode during the T1 start-up period. During the T2 activation period, the yellow-orange light channel and the near-infrared light channel output in a preset alternating time sequence. Within the effective output time slice of any treatment light channel, the treatment light channel outputs continuously or in pulse modulation mode. During the T3 inhibition period, the red light channel outputs continuously or in pulse modulation mode. During the T4 relaxation period, there is no light output at all.

5. The dynamic closed-loop fundus photobiological modulation system according to claim 3 or 4, characterized in that: The green light channel is located in the 500-560 nm green light band; The yellow-orange light channel is located in the 570-620 nm yellow-orange light band; The red light channel is located in the red light band of 620-700 nm; The near-infrared channel is located in the near-infrared band of 780-950 nm.

6. The dynamic closed-loop fundus photobiological modulation system according to claim 1, characterized in that, The control module is configured to execute the following closed-loop control process: a. Control the light source module to output therapeutic light cyclically according to the treatment cycle, and execute the T1 start-up period, T2 activation period, T3 inhibition period and T4 relaxation period in sequence within each treatment cycle; wherein, therapeutic light is output in the T1 to T3 stages, and no therapeutic light is output in the T4 stage, and the duration of each stage in the treatment cycle can be updated according to the closed-loop adjustment result. b. Before treatment begins, the light source module is controlled to illuminate at least one treatment light channel according to the baseline imaging illumination mode, and the fundus camera module is driven to acquire a baseline video sequence. The baseline vessel diameter D is obtained from the baseline video sequence. baseline Compared with baseline blood flow velocity V baseline The baseline imaging illumination mode is an illumination mode used for image acquisition rather than for treatment output, and its output power is lower than the peak power of the treatment light channel during the treatment output phase. c. During the treatment process, when at least one treatment light channel is lit during the T1 to T3 stages, the fundus camera module is controlled to perform synchronous exposure sampling, and the real-time blood vessel diameter D(t) and real-time blood flow velocity V(t) of the corresponding stage are extracted based on the sampled video. d. Based on D(t), V(t), and D baseline With V baseline The fundus vascular response parameters for the corresponding stage are calculated. These parameters include the vessel diameter variation coefficient Kd(t) and the blood perfusion index PI(t). The blood perfusion index PI(t) further undergoes time window averaging to obtain the average blood perfusion index PI for the corresponding stage. avg ; e. Using the average blood perfusion index (PI) avg The comparison result with the preset target interval is used as the main closed-loop discrimination criterion, and Kd(t) is used to adjust at least one treatment parameter in the closed loop. The treatment parameters include at least one of the peak power, pulse frequency, and duty cycle of the treatment optical channel at the corresponding stage, and / or the duration of the corresponding stage; the duration of the corresponding stage includes parameters used to obtain the PI. avg The duration of the corresponding therapeutic output phase in T1 to T3, and / or the duration of the T4 relaxation phase used for relaxation regulation.

7. The dynamic closed-loop fundus photobiological modulation system according to claim 6, characterized in that, The blood vessel diameter variation coefficient Kd(t) satisfies: Kd(t)=[D(t)- D baseline ] / D baseline ×100%; The blood perfusion index PI(t) satisfies: PI(t) = [V(t) · A(t)] / [V baseline ·HAS baseline ], Where A(t) is the approximate value of the blood vessel cross-sectional area obtained from D(t): A(t) = π × (D(t) / 2) 2 ; A baseline For D baseline The approximate value of the cross-sectional area of ​​the blood vessel is obtained, and A baseline =π×(D baseline / 2) 2 .

8. The dynamic closed-loop fundus photobiological modulation system according to claim 6 or 7, characterized in that, The control module obtains D baseline When dealing with D(t), the width of the blood vessel pixels is converted into the physical size based on preset calibration parameters to obtain the blood vessel diameter; The time window is at least two consecutive treatment cycles, and the treatment cycle includes the initial treatment cycle or the treatment cycle after closed-loop adjustment. The control module averages the blood perfusion index PI(t) obtained at corresponding stages within multiple treatment cycles to obtain the average blood perfusion index PI for each stage. avg .

9. The dynamic closed-loop fundus photobiological modulation system according to any one of claims 6 to 8, characterized in that, The control module performs closed-loop discrimination according to the following priority order: When PI avg When the value exceeds the upper limit of the preset target range, or when Kd(t) exceeds the preset safety limit, the control module determines that the response is excessive and reduces at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel, and / or shortens the duration of the corresponding treatment output stage, and / or extends the duration of the T4 relaxation period. When the over-response condition is not met, when PI avg When the value is lower than the lower limit of the preset target range, or when Kd(t)≤0, the control module determines that the response is insufficient and increases at least one of the peak power, pulse frequency and duty cycle of the corresponding treatment light channel, and / or extends the duration of the corresponding treatment output stage. When PI is not met, the conditions for over-response and under-response are not satisfied. avg When the treatment parameters are within the preset target range and 0 < Kd(t) ≤ the preset safety upper limit, the control module maintains the current treatment parameters.

10. A closed-loop control device for controlling the dynamic closed-loop fundus photobiological modulation system according to any one of claims 1-9, characterized in that, It includes a processor and a memory, wherein the memory stores a computer program, which, when executed by the processor, causes the processor to perform the following operations: Generate treatment timing control instructions from T1 to T4 based on the selected channel combination; During the baseline acquisition and treatment sampling phases, camera synchronization trigger commands are generated to enable the fundus camera module to acquire images when the treatment light is used as the imaging illumination light. Calculate Kd(t), PI(t), and PI based on the acquired images. avg ; According to PI avg The comparison results with the preset target range are combined with Kd(t) to generate treatment parameter adjustment instructions for adjusting at least one of the peak power, pulse frequency and duty cycle of the treatment light channel in the corresponding stage, and / or adjusting the duration of the corresponding stage.

Images