Visual training instrument with phototherapy function, control method and system thereof and storage medium

Abstract

The invention relates to a visual training instrument control method and system with a phototherapy function, a terminal and a medium, and relates to the technical field of phototherapy, and the method comprises the steps: obtaining the diopter information of a user; performing diopter compensation adjustment on the light source according to the diopter information to obtain a reference light path; controlling the light source modulation plate to carry out spatial modulation on the reference light path to obtain a light distribution image; generating a fixation target in the central area of the light distribution image, and fusing a fixation target light path with the reference light path through a reflective mirror and a semi-transparent and semi-reflective mirror to obtain a fused light path; controlling the fixation target to move back and forth along the visual axis direction of the fusion light path; correcting the position of the fixation target and the focusing parameter of the light source according to the eye image of the user; and based on the corrected focusing parameter, adjusting the output parameter of the light source in real time, so that the irradiation intensity output by the light source is synchronous with the eye adjusting state of the user. The visual adjustment capability can be improved, and the visual function recovery effect can be improved.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of light therapy, in particular to a vision training instrument with light therapy function, a control method and system thereof, and a storage medium. BACKGROUND

[0002] With the long-term use of electronic devices and the increase of close-range eye behavior, the problems of refractive abnormalities, visual fatigue and visual function degradation of the youth and adult population are increasingly prominent. A large number of users have symptoms such as continuous growth of the eye axis, decreased accommodation ability, and weakened binocular convergence function, which are manifested as blurred vision, double images, eye pain, and decreased attention.

[0003] In the prior art, the visual training device usually induces the accommodation and convergence response of the eyeball by displaying static images, flashing light sources or single-wavelength light to improve visual fatigue or refractive abnormalities. Some improved vision training instruments can achieve simple light intensity or frequency adjustment, but still generally use fixed optical path design, which cannot automatically focus compensation according to the refractive power of the user, the light therapy stimulation is disconnected from the eye adjustment process, lacks real-time feedback regulation based on eye images, and thus the training effect is limited, visual fatigue is prone to occur, and the effect of visual function recovery is low. SUMMARY

[0004] In order to improve the visual accommodation ability and enhance the effect of visual function recovery, the present application provides a vision training instrument with light therapy function and a control method, system and storage medium thereof.

[0005] In a first aspect, the present application provides a vision training instrument with light therapy function control method, which adopts the following technical solution: A vision training instrument with light therapy function control method, comprising: Obtaining the refractive information of the user; According to the refractive information, the refractive compensation adjustment is performed on the light source, so that the light output by the light source is focused on the retinal imaging plane after the light source modulation plate, and the reference light path after the refractive compensation is obtained; Controlling the light source modulation plate to spatially modulate the reference light path, so that the modulated light forms a light distribution image containing a central occlusion area and a peripheral partition stimulation spot on the retinal imaging plane; Generating a fixation target in the central region of the light distribution image, and fusing the fixation target light path and the reference light path through the mirror and the half-mirror to obtain the fusion light path; Controlling the fixation target to move forward and backward along the visual axis direction of the fusion light path; According to the eye image of the user, the position of the fixation target and the focusing parameter of the light source are corrected; Based on the corrected focusing parameter, the output parameter of the light source is adjusted in real time, so that the irradiation intensity output by the light source is synchronized with the eye adjustment state of the user.

[0006] By adopting the technical scheme, the light source focusing is adaptively matched with the user's diopter, the light is accurately focused on the retinal imaging plane, the fixation target light path and the reference light path are fused and synchronously controlled, the light therapy stimulation is consistent with the visual accommodation process, the clear imaging effect and the training comfort are improved, the visual accommodation ability is improved, and the visual function recovery effect is improved.

[0007] Optionally, the position of the fixation target and the focusing parameter of the light source are corrected according to the eye image of the user, including: real-time acquisition of the eye image of the user; extracting the pupil center position and the corneal reflection point coordinates according to the eye image; calculating the visual axis direction of the user according to the pupil center position and the corneal reflection point coordinates; obtaining the visual axis offset according to the included angle relationship between the visual axis direction and the fusion light path; determining whether the visual axis offset is greater than a preset offset threshold; if yes, calculating the light source focusing error of the light source focusing plane relative to the retinal imaging plane according to the visual axis offset and the optical path relationship between the light source and the eye of the user; correcting the focusing parameter of the light source according to the light source focusing error, so that the focusing plane output by the light source is re-coincident with the retinal imaging plane; calculating the imaging offset parameter of the fixation target according to the offset direction and the offset amplitude of the visual axis offset in the fusion light path; correcting the imaging position parameter of the fixation target according to the imaging offset parameter, so that the fixation target is imaged in the foveal region of the retina of the user.

[0008] By adopting the technical scheme, the visual axis offset and the focusing error of the user's eye are detected and dynamically corrected in real time, the light source focusing plane is always consistent with the retinal imaging plane, and the imaging position of the fixation target is stably ensured in the foveal region, so that the spatial precision of the light therapy stimulation and the focusing accuracy of the fixation training are improved, the visual fatigue caused by the imaging offset is avoided, and the stability and effectiveness of the visual function training are improved.

[0009] Optionally, the current irradiation intensity of the light source at the current time is obtained; determining the intensity upper threshold according to the preset prescription dose curve at the current time; determining whether the current irradiation intensity is greater than the intensity upper threshold; if yes, suspending the output of the light source; if no, obtaining an eye image sequence of the user; identifying a blink event and a gaze time according to the eye image sequence; An eye stability index is calculated according to the blink event and the gaze time; When the eye stability index is less than a preset gaze duration, the irradiance of the light source output and the moving speed of the fixation target are controlled to be synchronously reduced.

[0010] By adopting the technical solution, the light source output and the moving speed of the fixation target can be automatically paused or reduced when excessive light or eye instability is detected, so as to avoid excessive light stimulation and visual load, improve the safety and comfort of the training process, ensure a reasonable light therapy dose, and maintain a stable visual training effect.

[0011] Optionally, the baseline axial elongation rate and the choroidal thickness of the user are obtained; The baseline axial elongation rate and the choroidal thickness are input into a preset cloud model to obtain a multi-wavelength combination ratio, a pulse frequency, and a treatment interval, wherein the multi-wavelength combination ratio includes irradiation proportions of 620 nm wavelength, 660 nm wavelength, and 850 nm wavelength; According to the baseline axial elongation rate and the choroidal thickness, it is determined whether the user is a high progression risk person; In the case that the user is a high progression risk person, the irradiation proportion of the 660 nm wavelength in the multi-wavelength combination ratio is increased; According to the multi-wavelength combination ratio, the pulse frequency, and the treatment interval, a cross-deep stimulation sequence is generated, and the cross-deep stimulation sequence includes a ladder type pulse package structure of surface-deep-surface; The light source is controlled to irradiate according to the cross-deep stimulation sequence.

[0012] By adopting the technical solution, the irradiation proportion and the pulse frequency of the multi-wavelength light source can be adaptively adjusted, the 660 nm deep stimulation is strengthened for the high progression risk person, cross-type optical regulation of the surface and the deep is realized, so as to improve the targeting and physiological effectiveness of the light therapy, promote the recovery of choroidal metabolism and accommodation ability, and improve the individualized visual function correction effect.

[0013] Optionally, the process of controlling the fixation target to move forward and backward along the visual axis direction of the fusion light path further includes: A synchronous time sequence relationship between the position change of the fixation target in the fusion light path and the pulse output time of the light source is established; The light source is controlled to pulse output according to the synchronous time sequence relationship; A horizontal or vertical parallax signal is superimposed on the fixation target image.

[0014] By adopting the technical solution, the timing of the fixation target movement and the pulse output of the light source is synchronized, so that the light therapy stimulation and the visual fixation process are coordinated; at the same time, by superimposing the horizontal or vertical parallax signal on the fixation target image, the binocular vergence and fusion response can be induced, so as to enhance the stereoscopic visual training effect.

[0015] Optionally, the target refractive compensation lens in the magnetic refractive compensation lens case can be switched based on the refractive power information; Inspect the assembly status of the magnetic refractive compensation lens case; When the assembly status is "assembly complete", read the refractive power of the target refractive compensation lens; Determine whether the refractive power of the target refractive compensation lens matches the refractive power information; If so, the magnetic refractive compensation lens case will be locked and the light source will be activated for refractive compensation adjustment; If not, issue a prescription error alarm and disable the light source.

[0016] By adopting the above technical solution, the matching status of the magnetic refractive compensation lens can be intelligently switched and verified according to the user's refractive error information. After detecting that the lens is correctly assembled, the lens case is automatically locked and the light source adjustment is started, thereby avoiding prescription misuse and assembly errors, improving the accuracy of refractive compensation and training safety, and ensuring that the phototherapy process is carried out under the correct refractive conditions.

[0017] Optionally, obtain user identification information; The work mode is determined based on the user's identification information. The work modes include home mode and outpatient mode. When the work mode is home mode, set the daily training limit to the preset number of times and the maximum training time per session to the preset training time. When the work mode is outpatient mode, grant access to all parameter adjustments.

[0018] By adopting the above technical solution, a hierarchical management system based on user identity is achieved. It can automatically distinguish between home mode and outpatient mode. In home mode, the number of daily training sessions and the duration of each training session are limited to ensure safe use. In outpatient mode, all parameters are open for doctors to make professional adjustments, thereby improving the standardization and safety of equipment use and meeting the dual application needs of home rehabilitation and clinical treatment.

[0019] Secondly, this application provides a vision training instrument control system with phototherapy function, which adopts the following technical solution: A vision training device control system with phototherapy function includes: The acquisition module is used to acquire refractive power information; A memory for storing the program of the control method for the vision training instrument with phototherapy function; The processor and the program in the memory can be loaded and executed by the processor to implement the control method of the vision training instrument with phototherapy function.

[0020] By adopting the above technical solution, adaptive matching between light source focusing and user refractive power is achieved, so that light is accurately focused on the retinal imaging plane; at the same time, the fusion and synchronous control of the fixation target optical path and the reference optical path are realized, so that the phototherapy stimulation and visual accommodation process are consistent, thereby improving the clear imaging effect and training comfort, thereby improving visual accommodation ability and enhancing the visual function recovery effect.

[0021] Thirdly, this application provides a vision training device with phototherapy function, which adopts the following technical solution: A vision training device with phototherapy function includes a memory and a processor, wherein the memory stores a computer program that can be loaded by the processor and execute the method described in any one of the above.

[0022] Fourthly, this application provides a computer storage medium capable of storing corresponding programs, which facilitates the improvement of visual accommodation ability and enhances visual function recovery, and adopts the following technical solution: A computer-readable storage medium storing a computer program that can be loaded by a processor and executed any of the above-described methods for controlling a vision training instrument with phototherapy function.

[0023] In summary, this application includes at least one of the following beneficial technical effects: It achieves adaptive matching between light source focusing and user refractive power, enabling the light to be accurately focused on the retinal imaging plane; at the same time, it achieves the fusion and synchronous control of the fixation target optical path and the reference optical path, so that the phototherapy stimulation and visual accommodation process are consistent, thereby improving the clear imaging effect and training comfort, thereby improving visual accommodation ability and enhancing the visual function recovery effect; By real-time detection and dynamic correction of the user's visual axis deviation and focusing error, the focusing plane of the light source is always consistent with the imaging plane of the retina, and the imaging position of the fixation target is kept stable in the fovea region. This improves the spatial accuracy of phototherapy stimulation and the focusing accuracy of fixation training, avoids visual fatigue caused by imaging deviation, and enhances the stability and effectiveness of visual function training. It can automatically pause or reduce the output of the light source and the movement speed of the fixation target when it detects excessive light or eye instability, thereby avoiding excessive light stimulation and visual load, improving the safety and comfort of the training process, ensuring reasonable phototherapy dosage and maintaining stable visual training effect. Attached Figure Description

[0024] Figure 1 This is a flowchart illustrating a control method for a vision training instrument with phototherapy function according to an embodiment of this application.

[0025] Figure 2 This is a schematic diagram illustrating the process of correcting the position of the fixation target and the focusing parameters of the light source based on the user's eye image in an embodiment of this application.

[0026] Figure 3 This is a schematic flowchart of a closed-loop and safety control method for light irradiation dose in an embodiment of this application.

[0027] Figure 4 This is a flowchart illustrating a personalized multi-wavelength pulse control method in an embodiment of this application.

[0028] Figure 5 This is a flowchart illustrating a parallax overlay method in an embodiment of this application.

[0029] Figure 6 This is a schematic flowchart of a refractive compensation method in an embodiment of this application.

[0030] Figure 7 This is a flowchart illustrating a method for restricting home and medical care in an embodiment of this application. Detailed Implementation

[0031] To make the purpose, technical solution, and advantages of this application clearer, the following description is provided in conjunction with the appendix. Figure 1 - Appendix Figure 7 The present application will be further described in detail below with reference to 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 the application.

[0032] This application discloses a control method for a vision training device with phototherapy function. (Refer to...) Figure 1 The control methods for vision training devices with phototherapy functions include: Step S101: Obtain the user's refractive error information.

[0033] The vision training device with phototherapy function is an ophthalmic rehabilitation device that combines photobiological regulation with visual training. It emits multi-wavelength pulsed light to the eyes through a controllable light source, generating a movable fixation target while stimulating the eyes with light. This guides the user to complete refractive accommodation and binocular convergence training, so that the light stimulation and visual training process are carried out simultaneously, thereby improving the eye's accommodation ability and promoting the metabolic recovery of the retina and choroidal tissues.

[0034] Refractive power information refers to parameters that characterize the refractive state of the eye's optical system. It describes the deviation between the image position on the retina after parallel light rays enter the eye and the ideal focal point. It includes myopia, hyperopia, and astigmatism, etc., to reflect the refractive error of the user's eye.

[0035] In one feasible embodiment, the process of obtaining the user's refractive error information can be completed by an automated refractometer. After obtaining the refractive error information, it is uploaded to the server. If the user is a long-term training subject, the refractive error information in their previous training records can also be retrieved through the built-in database.

[0036] Step S102: Adjust the light source according to the refractive power information to compensate for the refractive power, so that the light output by the light source is focused on the retinal imaging plane after passing through the light source modulation plate, and the reference light path after refractive compensation is obtained.

[0037] Refractive power compensation refers to the correction of the optical path or divergence angle of light emitted from a light source based on the refractive state of the user's eye, so that the modulated light can be accurately focused on the retinal imaging plane.

[0038] A light source modulation board is an optical element located at the light-emitting end of a light source, used to modulate the spatial distribution or intensity pattern of the light output from the light source. Its structure consists of a central blocking area and a peripheral microlens array or honeycomb lens array. The central blocking area is used to control the energy distribution of light illuminating the macula of the retina, while the peripheral lens array is used to form multi-block or ring-shaped stimulation spots, so that different areas of the retina receive differentiated light stimulation.

[0039] The reference optical path refers to the standard imaging optical path formed after refractive compensation, which is used for subsequent visual training and phototherapy stimulation. Its focal point coincides with the fovea of ​​the retina.

[0040] Based on the refractive power information, the variable-focus optical components (such as a magnetic refractive compensation lens box with multiple refractive power lenses, an electric lens group, a liquid crystal lens, or a mechanically telescopic optical path structure) are controlled to compensate for the optical path of the light emitted from the light source. The compensated light is then modulated by the light source modulation plate to form a clear and accurate light spot distribution on the retinal imaging plane.

[0041] For example, refractive power compensation adjustment can be achieved through a scaled telescopic lens barrel driven by a stepper motor. When the refractive power of the user's right eye is detected to be -2.00D, the system calculates the required optical path adjustment amount ΔL and drives the telescopic lens barrel to move a corresponding distance along the optical axis, so that the focal point of the modulated light moves forward to the retinal plane.

[0042] Step S103: Control the light source modulation board to spatially modulate the reference light path, so that the modulated light forms a light distribution image on the retinal imaging plane that includes the central occlusion area and the peripheral partition stimulation spot.

[0043] Spatial modulation refers to adjusting the direction of light propagation, energy distribution, or focusing pattern to create a preset light intensity distribution on the target plane.

[0044] The light distribution image is a light spot image formed on the imaging plane of the retina after being modulated by the light source. It includes a central occlusion area (used to reduce the direct illumination energy of the macula) and peripheral zoned stimulation light spots (used to stimulate different areas of the retina).

[0045] By controlling the light source modulation board to spatially modulate the reference light path according to the set light field distribution parameters, the outgoing light rays form an illumination image with central suppression and peripheral zone enhancement on the retinal imaging plane, thereby achieving differentiated stimulation of different retinal regions within a safe range.

[0046] For example, by adjusting the incident angle and transmittance of the peripheral microlens array, the light flux in the central area is reduced to less than 20% of the total irradiance, while the peripheral area forms 4–6 ring-shaped light spots with varying intensities. After refractive compensation, the light passes through the modulation plate and forms a ring-shaped light distribution image on the retinal plane, which is used to induce metabolic responses and modulate stimulation in the peripheral retina.

[0047] Step S104: Generate a fixed target in the central region of the light distribution image, and fuse the fixed target light path with the reference light path through a reflector and a semi-transparent mirror to obtain a fused light path.

[0048] A fixation target is a visual target that a user focuses on during vision training to guide the eye's fixation, accommodation, and convergence movements.

[0049] Fusion optical path refers to the spatial superposition of the fixed target imaging optical path and the reference optical path, so that while the user is viewing the fixed target, the eyes can also receive phototherapy stimulation from the light source.

[0050] By generating a fixed target image in the central region of the light distribution image and controlling the angle of the reflector and the semi-transparent mirror, the imaging light path of the fixed target and the reference light path output by the light source modulation board are fused in space, ensuring that the two light rays are superimposed on the retinal plane, so that the user can receive phototherapy spot stimulation simultaneously when looking at the fixed target.

[0051] In one feasible embodiment, the fixed target is composed of a dynamic graphic generated by a liquid crystal display screen. The fixed target image is projected onto a semi-transparent mirror through an optical collimating lens. The reflector reflects the reference light path output from the light source into the same semi-transparent mirror. The two reflect each other on the optical axis, achieving partial transmission and partial reflection, thus obtaining a fused light path. By adjusting the brightness and position of the fixed target, the fixed target image is always located in the concave imaging region of the light distribution image.

[0052] Step S105: Control the fixed target to move back and forth along the visual axis direction of the fusion optical path.

[0053] The visual axis direction refers to the imaginary straight line from the center of the eyeball (node) to the object being viewed, and it is the reference direction for the focusing and accommodation of the visual system.

[0054] The forward and backward movement of the fixed target along the visual axis refers to the periodic movement of the image of the fixed target towards or away from the user's eye along the visual axis, controlled by the optical system. This causes the eye muscles to adjust, promoting the effective absorption of light by the retinal cells. The fixed target achieves continuous focusing within ±2.0 D through a programmable liquid crystal lens or an acousto-optic variable focus module.

[0055] Step S106: Correct the position of the fixation target and the focusing parameters of the light source based on the user's eye image.

[0056] An eye image refers to an image of the user's eye area, used to identify visual state parameters such as pupil position, corneal reflective point, and visual axis direction.

[0057] Focusing parameters are optical variables that control the imaging position of the light source, including the focal length of the light source, the optical path length, and the angle of the modulation plate, which are used to determine the imaging position and sharpness of the light on the retina.

[0058] The specific steps for correcting the position of the fixation target and the focusing parameters of the light source based on the user's eye image can be found in [reference needed]. Figure 2 The steps in the embodiments.

[0059] Step S107: Based on the corrected focusing parameters, adjust the output parameters of the light source in real time to keep the irradiance output by the light source synchronized with the user's eye accommodation state.

[0060] Output parameters refer to the variable parameters used to control the light emission characteristics of the light source, including irradiance, pulse frequency, duty cycle, and wavelength combination ratio.

[0061] Accommodation state refers to the change in lens curvature caused by the contraction or relaxation of the ciliary muscle when the user's eye is focused on a target. It is used to reflect the eye's focusing response to targets at different distances.

[0062] Based on the corrected focusing parameters, the system monitors the user's eye accommodation state in real time. By controlling the output parameters of the light source, the irradiance and pulse rhythm of the light are kept consistent with the eye's accommodation rhythm. When the user is detected to be in the accommodation contraction phase, the light source output intensity is increased to enhance the stimulation; when the user is in the relaxation phase, the light source irradiance is decreased to reduce the load, thereby establishing a dynamic matching relationship between light stimulation and physiological regulation.

[0063] In one feasible embodiment, when the fixation target being gazed at by the user moves closer to the eye, the system recognizes the tendency of accommodation contraction and controls the light source intensity to increase to 70% to enhance near-focus training stimulation; when the fixation target moves further away, the system detects the state of accommodation relaxation and automatically reduces the light source intensity to 40%, achieving dynamic synchronization between phototherapy output and eye accommodation while maintaining visual comfort.

[0064] The position of the fixation target and the focusing parameters of the light source are corrected based on the user's eye image, including: Step S201: Acquire the user's eye images in real time.

[0065] Images of the eye can be acquired in real time using imaging devices such as fundus cameras, optical coherence tomography, and infrared cameras.

[0066] Step S202: Extract the pupil center position and corneal reflection point coordinates based on the eye image.

[0067] The pupil center position refers to the coordinate point of the geometric center of the pupil area in an eye image, which can reflect changes in the orientation of the user's eyeball.

[0068] Corneal reflector coordinates refer to the spatial position of the bright reflector formed on the corneal surface when a light source shines on it. They are used as a reference point for the optical axis, and their relative position to the center of the pupil can be used to calculate the rotation angle of the eyeball and the direction of the visual axis.

[0069] In one feasible embodiment, the pupil outline is first identified by grayscale thresholding and edge detection, and its centroid coordinates are calculated as the pupil center position; then the bright area of ​​the light spot is detected and its geometric center is determined to obtain the coordinates of the corneal reflection point.

[0070] Step S203: Calculate the user's visual axis direction based on the pupil center position and the coordinates of the corneal reflector.

[0071] Based on the extracted pupil center position and corneal reflection point coordinates, an eyeball geometric model is established, and the angle between the line connecting the two points and the reference optical axis is calculated to determine the three-dimensional direction vector of the user's visual axis. This calculation result reflects the user's current gaze state, is used to determine whether the line of sight is aligned with the fused optical path, and provides a reference for subsequent light source focusing correction.

[0072] In one feasible embodiment, the pupil center position and corneal reflector coordinates are input into the eye-tracking geometry model, according to the formula... θ x =k x (x p -x r ), θ y =k y (y p -y r ) Calculate the horizontal deflection angle and the vertical deflection angle, where θ x θ is the horizontal deflection angle. y The vertical deflection angle is (x) p ,y p (x) represents the coordinates of the pupil center. r ,y r) represents the coordinates of the corneal reflector point, k x and k y As calibration coefficients, the final line-of-sight direction vector V=(θ) is obtained. x ,θ y ,1), this vector is used to update the eye gaze direction in real time. Here, 1 represents the scalar reference term of the normalized direction vector, which is used to represent the unit component in the optical axis direction.

[0073] For example, when the pupil center position is detected to be offset by 4 pixels in the horizontal direction and 2 pixels in the vertical direction relative to the corneal reflection point coordinates, the horizontal deflection angle is calculated to be about 1.5° and the vertical deflection angle is about 0.8° according to the calibration coefficient. Based on this, it is determined that the user's line of sight is slightly shifted to the lower right, triggering subsequent fixation target position fine-tuning and light source focus compensation operations.

[0074] Step S204: Obtain the line-of-sight offset based on the angle between the line-of-sight direction and the fused optical path.

[0075] Visual axis offset refers to the angle between the user's current visual axis direction and the fusion optical path, or its equivalent displacement on the retinal imaging plane, and is used to quantify the degree to which the gaze direction deviates from the target optical path.

[0076] In one feasible embodiment, the view axis direction vector V and the direction vector of the fused optical path are... Compare F(0, 0, 1) and calculate the angle between them using the formula.

[0077] The included angle α is obtained, and the angle deviation can be converted into the equivalent displacement of the retinal surface Δr≈f·tanα when needed, as the visual axis offset output, where f is the equivalent focal length of the eyeball.

[0078] Step S205: Determine whether the line-of-sight offset is greater than the preset offset threshold.

[0079] The preset offset threshold is a preset constant, a critical parameter set to determine the degree of deviation of the user's line of sight. It is expressed in angle (°) or retinal plane displacement (mm) and is used to distinguish between normal minor fluctuations in line of sight and significant deviations that need to be corrected.

[0080] If the view axis offset is greater than a preset offset threshold, then step S206 is executed; if the view axis offset is not greater than the preset offset threshold, then the process of this embodiment ends.

[0081] Step S206: If yes, then calculate the light source focusing error relative to the retinal imaging plane based on the visual axis offset and the optical path relationship between the light source and the user's eye.

[0082] Optical path relationship refers to the distance and refraction path of light emitted from a light source through various optical elements to reach the user's retina. It is used to describe the correspondence between the imaging position of the light and the focal plane of the eye.

[0083] Light source focusing error refers to the distance difference between the image plane of the light source after compensation and the image plane of the retina, reflecting the degree to which the light focus deviates from the retina.

[0084] Based on the current visual axis offset, the light source emission angle, and the optical path geometry between the light source and the eye, the offset distance of the light source focusing plane relative to the ideal retinal imaging plane is calculated to determine the error direction and magnitude of the focus shift forward or backward.

[0085] In a feasible embodiment, the light source focusing error is calculated using the fused optical path length L and the offset angle β as input parameters, according to the geometric relationship Δf=L×(1-cosβ), where Δf is the focal plane deviation and also the light source focusing error.

[0086] Step S207: Correct the focusing parameters of the light source according to the focusing error of the light source, so that the focusing plane output by the light source coincides with the retinal imaging plane again.

[0087] Based on the focusing error Δf of the light source, the parameters of the light source focusing assembly are adjusted, such as changing the lens spacing, adjusting the liquid crystal lens driving voltage, or moving the focusing lens group position, to correct the focal position of the light source. After adjustment, the focusing plane of the light source output coincides with the retinal imaging plane again, ensuring that the energy density distribution of the phototherapy spot completely corresponds to the visual training imaging area.

[0088] In one feasible embodiment, the light source focusing assembly employs a linear slide structure driven by a stepper motor. The control unit calculates the required displacement ΔL based on the focusing error Δf and converts it into a motor step command. For example, when Δf is 0.03mm, the control unit outputs a 600-step signal (0.05μm per step) to drive the lens group forward along the optical axis, thereby shifting the focal plane forward by 0.03mm and re-aligning the focusing surface with the retinal plane. If a liquid crystal variable focus lens structure is used, the equivalent focal length can be subtly changed within a range of ±0.5V by adjusting the driving voltage.

[0089] Step S208: Calculate the imaging offset parameters of the fixed target based on the offset direction and offset magnitude of the visual axis offset in the fusion optical path.

[0090] Imaging offset parameters refer to the amount and direction of displacement that the fixed target image should be adjusted in the fusion optical path. They are used to describe the deviation of the fixed target from the fovea region on the retinal imaging plane.

[0091] Based on the direction and magnitude of the visual axis offset, and combined with the spatial coordinate system of the fusion optical path, the imaging offset parameters that the fixed target image should be corrected in this optical path are calculated. If the visual axis is offset to the upper left, the vector displacement that the fixed target image should be slightly adjusted to the lower right is calculated so that the fixed target is reprojected onto the fovea region of the user's retina.

[0092] In a feasible embodiment, the optical channel consisting of the fixed target imaging module, the semi-transparent lens, and the retina in the fusion optical path is taken as the calculation object, and its equivalent focal length is denoted as f. c According to the line-of-sight offset angle (θ) x ,θ y Calculate the offset of the fixation target on the retinal imaging plane. Δx=f c ×tan(θ x ), Δy=f c ×tan(θ y ) Here, Δx and Δy represent the imaging offsets in the horizontal and vertical directions, respectively. Combining Δx and Δy forms the imaging offset parameter. Based on this offset parameter, the fixed target projection module is driven to move in the opposite direction, thereby realigning the optical path.

[0093] For example, when a 1.2° rightward and 0.8° upward deviation of the user's visual axis is detected, and the equivalent focal length f of the fused optical path is... c =17mm, and the calculated displacements of the fixation target on the retinal imaging plane are Δx=0.36 mm and Δy=0.24 mm. Based on this, the fixation target imaging position is adjusted slightly to the lower left to refocus the image on the fovea region of the retina.

[0094] Step S209: Correct the imaging position parameters of the fixation target according to the imaging offset parameters, so that the fixation target is imaged in the fovea region of the user's retina.

[0095] Imaging position parameters are used to describe the specific imaging coordinates of the fixed target in the fusion optical path.

[0096] In this process, after obtaining the imaging offset parameters, the projection position or optical path angle of the fixation target imaging module is adjusted so that the actual imaging position of the fixation target is corrected in the opposite direction of the imaging offset until the fixation target image falls back into the fovea region of the retina, thus achieving coaxial alignment between the phototherapy optical path and the visual fixation direction.

[0097] This application provides a closed-loop and safety control method for light irradiation dose, referring to... Figure 3 The method includes: Step S301: Obtain the current irradiance of the light source at the current moment.

[0098] Irradiance refers to the radiant power produced by a light source per unit area, used to characterize the light energy output level of the light source at a specific moment. Current irradiance is the actual irradiance output of the light source detected at the current moment.

[0099] The light signal output by the light source is collected in real time by a light power detection element (such as a photodiode or a photodetector) placed near the light output end of the light source, and the detected voltage or current signal is converted into the corresponding irradiance value.

[0100] In one feasible embodiment, the irradiance of the light source is positively correlated with the power of the light source, and the irradiance of the light source can be obtained by querying the power of the light source at the current moment.

[0101] Step S302: Determine the upper limit threshold of intensity based on the preset prescription dose curve at the current time.

[0102] The preset prescription dose curve is a light dose-time relationship curve established according to medical phototherapy standards. It is used to limit the range of the maximum allowable irradiation intensity during phototherapy as it changes over time.

[0103] The preset intensity upper limit threshold is the safe upper limit value corresponding to the curve at the current moment, which is used to prevent excessive light from causing excessive stimulation of the retina.

[0104] Obtain the current time point or treatment stage identifier of the training, find the corresponding intensity upper limit threshold in the preset prescription dose curve, and store the threshold in the running cache as a reference standard for real-time light source output control to adjust the safe range of phototherapy output.

[0105] In a feasible embodiment, the preset prescription dose curve is stored in the database in the form of a piecewise function or a fitting function, and its expression is:

[0106] I max f(t) represents the upper limit threshold of intensity at time t, f1(t), f2(t), and f3(t) are the intensity change functions at different stages, and T1, T2, and T3 are the time segment points of the preset prescription dose curve. The corresponding function is automatically selected and the upper limit threshold of intensity is calculated based on the current training time t.

[0107] Step S303: Determine whether the current irradiation intensity is greater than the upper limit threshold.

[0108] The current irradiance intensity is compared with the upper limit threshold. If the current irradiance intensity is greater than the upper limit threshold, step S304 is executed. If the current irradiance intensity is not greater than the upper limit threshold, step S305 is executed.

[0109] Step S304: If yes, then pause the light source output.

[0110] When the irradiance exceeds the preset upper limit threshold, a shutdown command is immediately sent to the light source driver module to cut off the light source current or reduce the drive duty cycle to zero, causing the light source to stop emitting light. Simultaneously, the abnormal state is recorded and a safety timing logic is initiated; the light source output is only allowed to restart after the light intensity returns to a safe range.

[0111] Step S305: If not, obtain the user's eye image sequence.

[0112] An eye image sequence refers to a collection of multiple consecutively acquired eye images within a preset time window. It is used to analyze the dynamic changes in a user's eyeballs, such as gaze stability, blink frequency, and visual axis drift. Compared to a single frame, an image sequence can reflect behavioral patterns over time. In this embodiment, the preset time window is from 3 seconds before the current moment to the current moment. The eye images are acquired in real time; only when the frontal irradiance does not exceed the upper limit threshold are the acquired eye images combined into an eye image sequence, with each 3-second time window serving as a separate window. Furthermore, eye images are acquired at a rate of 120 frames per second.

[0113] Step S306: Identify blinking events and gaze duration based on the eye image sequence.

[0114] A blink event is when a user closes their eyes.

[0115] Gaze duration refers to the length of time a user continuously focuses on the same target (fixation target) within a certain period of time, and is used to reflect eye stability and attention concentration.

[0116] By detecting the presence, shape changes, and grayscale gradient changes of the pupil region in consecutive frames of eye image sequences, the start and end frames of blinking events are identified; in the stable frame segments between blinking events, the length of time the user continuously fixates on the fixation target is calculated, thereby obtaining the gaze duration index.

[0117] In one feasible embodiment, pupil features are extracted frame by frame from the eye image sequence, and the pupil visibility parameter P is calculated for each frame. t When P in consecutive frames t Below the threshold P th When the duration is less than 500 ms, it is marked as a blink event; the number of frames in the interval between two adjacent blinks multiplied by the sampling period is the gaze time.

[0118] For example, in the acquired eye image sequence, the pupil was detected to disappear for about 0.4 seconds between frames 85 and 90, which was determined to be a blink event; then the pupil position remained stable continuously from frame 91 to frame 310, and the gaze time was calculated to be 2.2 seconds.

[0119] Step S307: Calculate the eye stability index based on blink events and gaze duration.

[0120] Eye stability index is a quantitative parameter used to assess the stability of a user's eye gaze during training, reflecting the user's eye movement control ability and visual focus.

[0121] Based on blink events and gaze duration, the average blink frequency and average gaze duration per unit time are calculated, and the two are weighted and summed to calculate the eye stability index. The higher the index, the more stable the user's gaze and the better the training status; conversely, it indicates eye fatigue or decreased attention, requiring automatic reduction of stimulus intensity or suspension of training.

[0122] In one feasible embodiment, an eye stability index S is defined. e for

[0123] Among them, T g To calculate the total gaze duration, N b T represents the number of blink events. t The current training duration is w1 and w2 are preset empirical weight coefficients.

[0124] Step S308: When the eye stability index is less than the preset gaze index, the irradiance of the light source output and the movement speed of the fixation target are reduced synchronously.

[0125] The preset gaze index is the minimum allowable value for eye stability set according to the safety standards for phototherapy training, used to determine whether the user's current gaze is stable.

[0126] Synchronous reduction refers to simultaneously reducing the output irradiance of the light source and the movement speed of the fixed target when the user's eye is detected to be in an unstable state, in order to reduce visual load and restore the user's eye accommodation balance.

[0127] The eye stability index S e Compared with the preset gaze index S th Compare; when S e th If the system detects that the user's gaze is unstable or their attention is declining, the control unit immediately implements a protection strategy: reducing the intensity of the light source to weaken the light stimulation, and slowing down the movement speed of the fixation target along the light path, giving the user sufficient time to refocus, thereby preventing visual fatigue caused by overstimulation.

[0128] In one feasible embodiment, a linear synchronous adjustment strategy is employed to dynamically adjust the output parameters based on the deviation ratio of the ocular stability index: ​I'=I0×(1-k1·ΔS), v'=v0×(1-k2·ΔS) Where I' is the adjusted irradiance of the light source, v' is the adjusted fixed target movement speed, I0 and v0 are the current irradiance of the light source and the fixed target movement speed, respectively, ΔS=(S th -S e ) / S th k1 and k2 are preset adjustment coefficients. The control unit refreshes the output parameters every 200ms to ensure a smooth decrease in the light source and motion speed.

[0129] On the other hand, if the eye stability index is not less than the preset gaze index, no action is taken.

[0130] This application provides a personalized multi-wavelength pulse control method, referring to... Figure 4 The method includes: Step S401: Obtain the user's baseline axial length growth rate and choroid thickness.

[0131] The baseline axial length growth rate refers to the average rate of increase in axial length (the distance from the cornea to the posterior wall of the retina) over a given period of time, used to assess the risk of myopia progression. Choroidal thickness refers to the thickness of the choroidal tissue beneath the retina, reflecting blood perfusion and metabolic status in the posterior segment of the eye, and its changes are closely related to the axial length growth trend.

[0132] During the initialization phase, the user's axial length and choroidal thickness data are collected using ocular physiological parameter detection devices (such as optical coherence tomography (OCT) or an axial length measuring instrument). Based on historical test records or continuous measurement results from medical databases, the axial length growth rate is calculated and the current choroidal thickness parameter is extracted.

[0133] In one feasible embodiment, the user's most recent and previous axial length measurements are obtained and denoted as axial lengths L1 and L0, respectively, with a measurement interval of Δt. The baseline axial growth rate G is then calculated. b =(L1-L0) / Δt, and simultaneously record the current choroid thickness C. t .

[0134] Step S402: Input the baseline axial growth rate and choroid thickness into the preset cloud model to obtain the multi-wavelength combination ratio, pulse frequency and treatment interval. The multi-wavelength combination ratio includes the irradiation proportions of 620nm, 660nm and 850nm wavelengths.

[0135] The preset cloud model is a phototherapy parameter intelligent generation algorithm model deployed on a remote server. Through learning from a large number of clinical samples and training data, it can automatically output personalized phototherapy plans based on individual physiological parameters.

[0136] Multi-wavelength combination ratio refers to the proportional relationship of irradiation energy distribution among multiple wavelength light sources to achieve a combined stimulation effect on tissue layers at different depths.

[0137] The pulse frequency and treatment interval correspond to the stimulation rhythm and treatment cycle control parameters of phototherapy, respectively.

[0138] The user's baseline axial length growth rate and choroid thickness parameters are uploaded to the cloud server. The cloud model matches similar individual samples in the database based on the input parameters, calls the neural network algorithm, and outputs the optimal phototherapy configuration parameters, including the irradiation ratio of different wavelengths (620 nm, 660 nm, 850 nm), pulse modulation frequency, and treatment interval.

[0139] In one feasible embodiment, the cloud model is constructed based on a gradient boosting decision tree algorithm, and the input vector includes [G]. b C t The output vector is [R]. 620 ,R 660 ,R 850 ,f p ,T c ], where R 620 +R 660 +R 850 =1, f p T is the pulse frequency. c This is the interval between treatment sessions. The results are synchronized to the local device, and the parameter configuration of the light source is automatically updated to ensure that the duty cycle of each wavelength light source corresponds to the ratio sent from the cloud.

[0140] For example, when a user's baseline axial growth rate is high and the choroid thickness is relatively thin, the phototherapy parameters output by the cloud model will increase the proportion of mid-band (660nm) irradiation, while appropriately extending the treatment interval and pulse cycle; if the user's axial growth rate is low, the model will output a combination scheme mainly based on the superficial stimulation band (620 nm).

[0141] Step S403: Determine whether the user is at high risk of progression based on the baseline axial length growth rate and choroidal thickness.

[0142] High-risk individuals are those whose physiological parameters and monitoring results show a rapid progression of myopia, characterized by a higher axial length growth rate and a thinner choroid thickness.

[0143] In obtaining the user's baseline axial length growth rate G b and choroid thickness C t Then, the two are compared with the critical threshold set in the database. If G b Higher than the physiological growth reference value and C tIf the progress is below the lower limit of the normal range, the user is judged as a high-risk individual; otherwise, they are judged as a normal or low-risk individual.

[0144] Step S404: If the user is at high risk of progression, increase the proportion of 660nm wavelength irradiation in the multi-wavelength combination ratio.

[0145] On the other hand, no action is taken if the user is not considered a high-risk individual.

[0146] Once a user is identified as having a high risk of progression, the irradiation ratio of the 660 nm band in the multi-wavelength combination is increased, while the ratios of the 620 nm and 850 nm bands are correspondingly reduced. By increasing the energy distribution of mid-wavelength light, targeted stimulation of the choroid layer is achieved, thereby slowing down the rate of axial elongation.

[0147] In one feasible embodiment, a basic combination ratio [R] is received from a preset cloud model. 620 ,R 660 ,R 850 When the user is at high risk of progress, a proportional correction factor β is applied. 660 >1. Calculate the adjusted energy allocation:

[0148] in, This represents the irradiance percentage adjusted for a wavelength of 660 nm. This represents the irradiance percentage after adjusting for a wavelength of 620nm. The irradiance percentage after adjusting for a wavelength of 850mm.

[0149] Step S405: Generate a cross-deep stimulation sequence based on the multi-wavelength combination ratio, pulse frequency and treatment interval. The cross-deep stimulation sequence includes a stepped pulse packet structure of surface-deep-surface.

[0150] Cross-deep stimulation sequence refers to a dynamic illumination control sequence formed by combining different wavelengths of light in a specific order according to the differences in tissue penetration depth, so that light stimulation alternates between the surface of the retina and the deep layer of the choroid.

[0151] The stepped pulse packet structure is a light pulse output mode, which refers to the output of pulse packets in which the intensity or wavelength of the light source changes in stages, in order to achieve continuous photophysiological stimulation from the surface to the deep layer and back to the surface.

[0152] Based on the preset multi-wavelength combination ratios, pulse frequencies, and treatment interval parameters output by the cloud model, a cross-deep stimulation sequence is generated. This sequence first outputs short-wavelength light (e.g., 620 nm) to dominate surface stimulation, then switches to mid-wavelength light (e.g., 660 nm) to dominate deep stimulation, and finally returns to the surface stimulation band, achieving a "surface-deep-surface" cyclical structure. By organizing illumination in pulse packets along the time axis, the alternating regulation of the retinal neural layer and the choroidal vascular layer is achieved, thus achieving balanced stimulation.

[0153] Step S406: Control the light source to irradiate according to the cross-deep stimulation sequence.

[0154] After receiving the cross-deep stimulation sequence, the wavelength of the light source is adjusted according to the wavelength allocation, pulse frequency and duration in the cross-deep stimulation sequence, so that the light sources of each band are lit or turned off sequentially within a specified time slice.

[0155] Reference Figure 5 The process of controlling the fixed target to move back and forth along the visual axis of the fusion optical path also includes: Step S501: Establish the synchronous timing relationship between the position change of the fixed target in the fusion optical path and the pulse output time of the light source.

[0156] Synchronous timing relationship refers to establishing a correspondence between the positional change of the fixed target and the pulse output of the light source in the time dimension, so that the pulse timing of the light source is synchronized with the movement state (position, speed or acceleration) of the fixed target.

[0157] First, the real-time position information of the fixation target along the fusion optical path is acquired, and the movement time points of the fixation target at different positions are recorded. Then, these time points are mapped with the pulse triggering time of the light source, so that each pulse output of the light source corresponds to a specific spatial position of the fixation target, thereby achieving dynamic synchronization between phototherapy stimulation and visual fixation.

[0158] In a feasible embodiment, the displacement x(t) of the fixed target is represented as a periodic motion function, for example: x(t) = Asin(2πf m t) Where A is the amplitude of the fixed target's movement, f m Let t be the moving frequency and t be the time. The light source is controlled to output pulses, making the pulse phase Φ... p (t) phase Φ with fixed target motion m (t) satisfies the synchronous timing relationship: Φ p (t)=g(Φ m (t))=2πf p t+Φ0 Among them, f p Φ0 represents the output frequency of the light source pulse, and Φ0 represents the phase offset. The phase of the light source pulse Φ0 is controlled by a phase-locked loop (PLL) mechanism. p (t) phase Φ with fixed target motion m (t) satisfies the synchronization condition: |Φ p (t)-Φ m (t)|≤ΔΦ lim Where, ΔΦ lim This indicates the maximum permissible phase deviation. Under this constraint, the light source outputs pulses only when the fixation target passes through a specific spatial region (e.g., near the retinal focal point or accommodation pole), achieving real-time coupling between phototherapy and eye accommodation.

[0159] Step S502: Control the light source to output pulses according to the synchronization timing relationship.

[0160] Using the real-time position x(t) of the fixed target as a trigger signal, when the fixed target moves to a set key position (such as the motion pole), the light source is controlled to emit pulse light.

[0161] For example, based on the motion trajectory of the fixed target, the motion period of the fixed target is set to T. m When the fixed target moves forward to the peak point x=+A or back to the trough point x=-A, and at the phase point Φ of each cycle... m =0 (forward peak value) and Φ m =π (backward peak value) triggers light source pulses, with pulse width controlled between 10–30ms. The pulse output timing is adjusted according to the synchronization timing relationship so that the light source emits light only at the moment the fixed target reaches the adjustment pole. For example, when the fixed target moves back and forth along the fused optical path at a frequency of 1Hz, the light source is triggered to emit narrow pulses at a frequency of 1Hz, with each pulse corresponding to the forward or backward peak pole of the fixed target movement.

[0162] Step S503: Superimpose horizontal or vertical parallax signals onto the fixed target image.

[0163] Parallax signals are artificially introduced image displacement differences to create binocular stereoscopic visual stimulation, used to induce convergence or divergence responses in both eyes. Horizontal parallax is used to train binocular convergence and divergence abilities; vertical parallax is used to balance the vertical registration of the visual axes of both eyes.

[0164] By superimposing a parallax signal onto the fixed target image, it is indicated that during the fixed target display process, images with a certain pixel offset are generated for the left and right eye channels respectively, thereby achieving binocular parallax stimulation.

[0165] When generating a fixed target image, the deflection angles of the mirrors in the left and right eye optical paths are adjusted to cause a small angular shift in the horizontal or vertical direction in the fusion optical path. This angular shift is the amplitude of the disparity signal. The difference in the imaging positions of the left and right eyes will induce convergence or separation of the two eyes, thus achieving stereoscopic vision training. In this embodiment, in one feasible embodiment, an angular shift of ±Δθ is set in the left and right eye optical paths in the fixed target imaging path, where Δθ is the amplitude of the disparity signal, ranging from 0.3° to 1.5°. When Δθ is positive, the disparity signal direction is relatively convergent, used to train convergence ability; when Δθ is negative, the direction is relatively divergent, used to train convergence and accommodation ability.

[0166] This application provides a refractive compensation method, referring to... Figure 6 The method includes: Step S601: Switch the target refractive compensation lens in the magnetic refractive compensation lens case according to the refractive power information.

[0167] The magnetic refractive compensation lens case is an optical component used to install multiple sets of refractive compensation lenses. Each lens corresponds to a different refractive power range. The magnetic refractive compensation lens case achieves rapid adsorption and replacement of refractive compensation lenses through a magnetic positioning mechanism.

[0168] Targeted refractive compensation lenses are lenses that are matched according to the user's refractive error information and can accurately focus incident light onto the retinal imaging plane.

[0169] In one feasible embodiment, the magnetic refractive compensation lens case contains several refractive compensation lenses covering a range of ±10D. These lenses are mounted on a rotatable rotating ring, and each lens has a magnetic positioning ring on its edge. Based on the user's refractive power information (e.g., -3.00D), lens number M3 is selected. The magnetic attraction of the current refractive compensation lens is released via an electrically controlled magnetic attraction mechanism. Rotating the rotating ring activates the magnetic positioning ring of M3, causing the lens to adhere to the front of the light source modulation plate, thus achieving automatic switching of the refractive compensation lens.

[0170] In some other embodiments, the refractive compensation lens can be manually attached to the front of the light source adjustment plate.

[0171] Step S602: Detect the assembly status of the magnetic refractive compensation lens case.

[0172] Assembly status refers to the positioning and adsorption of the magnetic refractive compensation lens case and its internal refractive compensation lenses during the assembly process, including whether they are fully adsorbed, whether they are coaxial with the optical path, and whether they are stably fixed. If the refractive compensation lenses are not fully adsorbed but are coaxial with the optical path, then the assembly is complete; otherwise, the assembly is incomplete.

[0173] The assembly status of the magnetic refractive compensation lens case can be detected by an electromagnetic sensor to identify whether the case is correctly aligned and adsorbed into place.

[0174] Step S603: When the assembly status is "assembly complete", read the refractive power of the target refractive compensation lens.

[0175] The purpose of reading the refractive power of the target refractive compensation lens is to verify whether the refractive compensation lens actually installed in the optical path is consistent with the target refractive compensation lens determined based on the user's refractive power information. This is to avoid situations where the refractive power does not match the refractive power information when switching the target refractive compensation lens, thereby ensuring the accuracy of refractive compensation and the safety of phototherapy output.

[0176] In one feasible embodiment, an RFID chip is embedded in the edge of each refractive compensation lens, and the refractive power parameters of the lens (such as -2.00D, +1.50D, etc.) are written inside the chip. When the lens case is attached to the ground, the RFID reader module in the vision training device automatically scans the lens label and reads the corresponding refractive power value. If the RFID data is successfully read and the signal strength is stable, the read refractive power is temporarily stored in the buffer area, awaiting the matching judgment command.

[0177] Step S604: Determine whether the refractive power of the target refractive compensation lens matches the refractive power corresponding to the refractive power information.

[0178] By comparing the refractive power of the target refractive compensation lens with the refractive power information corresponding to it, a secondary verification effect is achieved, avoiding situations where the refractive power of the target refractive compensation lens does not match the refractive power information corresponding to it.

[0179] Step S605: If yes, lock the magnetic refractive compensation lens case and start the light source to adjust the refractive compensation.

[0180] A locking magnetic refractive compensation lens case refers to a lens case that, after the refractive power of the refractive compensation lens has been matched and verified, is fixed to the optical main path by an electronically controlled magnetic suction device to prevent the magnetic refractive compensation lens case from shifting during training.

[0181] Activating the light source for refractive compensation adjustment means that the light source outputs light that has been corrected by the refractive compensation lens, so that it is accurately focused on the imaging plane of the user's retina.

[0182] Step S606: If not, issue a prescription error alarm and disable the light source.

[0183] Prescription error alarm is a safety warning signal that is automatically triggered when the refractive power of the actually fitted refractive compensation lens does not match the refractive power information, in order to remind the user that the current refractive compensation lens is installed incorrectly.

[0184] Disabling light source activation means blocking the light source drive circuit or light emission command through control logic to prevent the emission of training light under incorrect refractive state, thereby avoiding misfocusing of the user's retina.

[0185] This application provides a home and medical restriction method, referring to... Figure 7 The method includes: Step S701: Obtain user identification information.

[0186] User identification information refers to digital authentication data used to identify user identity and permission categories, including identity information collected through NFC identity rings, parent mobile apps, or doctor login credentials. This identification information may include user type, unique identifier, and mode authorization level, used to determine the control mode of device operation.

[0187] In one feasible embodiment, the visual training device has a built-in NFC identification module. When the user's identification ring approaches a designated area of ​​the device, the encrypted authentication data within the ring is automatically read. If the user connects to the device via a parent's mobile app, the Bluetooth communication module parses the user's identification information bound to the app to identify whether the user is a "family user" or a "doctor's user." Both types of identification information are standardized into identification codes and temporarily stored in a cache for later retrieval.

[0188] Step S702: Confirm the working mode based on the user's identity information. The working mode includes home mode and outpatient mode.

[0189] The working mode refers to the configuration status of the vision training device's operating permissions under different user identities, including "home mode" and "outpatient mode". Home mode is used by ordinary users or children for routine training in a home environment, and its operating parameters are limited; outpatient mode is used by doctors or professionals in medical institutions, allowing comprehensive adjustment of parameters such as light source, treatment course, and refractive compensation.

[0190] After obtaining user identification information, the system compares the user type field (such as UID_H or UID_C) within the identification information. When the identification result is a home user, it switches to home mode and loads the corresponding training frequency and duration limit parameters; when the identification result is a doctor or medical institution user, it switches to outpatient mode, removes usage restrictions, and loads the adjustable parameter table. The mode switching process is completed during the visual training device's startup phase, and the current operating mode is displayed in real time on the device's interface.

[0191] Step S703: When the work mode is home mode, set the daily training limit to a preset number of times and the training time limit per session to a preset training time.

[0192] The preset number of sessions refers to the maximum number of training sessions allowed per day in home mode, designed to prevent eye strain or excessive light exposure caused by overuse. The preset training time refers to the maximum duration of each training session; the system will automatically end the training process after this time. Both are safety parameters, set by the medical institution or the device at the factory.

[0193] In one feasible embodiment, the preset number of training sessions in home mode is 2 times per day, and the preset training time is 3 minutes. Timing begins when the user starts training. When the training duration reaches 180 seconds, the system automatically interrupts the light source output and records one training session as complete. If the user has already accumulated 2 training sessions for the day, when the user attempts to start training again, a message "Today's training session limit has been reached" will pop up, and the light source will be prevented from restarting.

[0194] Furthermore, if the mode at the end of the last session of the visual training device was home mode, it needs to be unlocked via NFC identity ring or parent's mobile app when the device is started again.

[0195] Step S704: When the working mode is outpatient mode, grant all parameter adjustment permissions.

[0196] Parameter adjustment permissions refer to the user's operational authority to modify parameters related to phototherapy training (such as light source irradiance, wavelength combination ratio, pulse frequency, refractive compensation range, and treatment duration). Granting all parameter adjustment permissions means removing restrictions on the number of training sessions, duration, and light source output parameters in outpatient mode, allowing doctors to freely configure and adjust parameters in real time according to individual patient conditions.

[0197] Based on the same inventive concept, embodiments of this application provide a vision training device control system with phototherapy function, including: The acquisition module is used to acquire refractive power information; A memory for storing the program of the control method for the vision training instrument with phototherapy function; The processor and the program in the memory can be loaded and executed by the processor to implement the control method of the vision training instrument with phototherapy function.

[0198] Those skilled in the art will clearly understand that, for the sake of convenience and brevity, the above-described division of functional modules is used as an example. In practical applications, the above functions can be assigned to different functional modules as needed, that is, the internal structure of the device can be divided into different functional modules to complete all or part of the functions described above. The specific working process of the system, device, and unit described above can be referred to the corresponding process in the foregoing method embodiments, and will not be repeated here.

[0199] This application provides a computer-readable storage medium storing a computer program that can be loaded by a processor and executed as a method for controlling a vision training instrument with phototherapy function.

[0200] Computer storage media include, for example, USB flash drives, portable hard drives, read-only memory (ROM), random access memory (RAM), magnetic disks, optical disks, and other media that can store program code.

[0201] Based on the same inventive concept, embodiments of this application provide a smart terminal, including a memory and a processor, wherein the memory stores a computer program that can be loaded by the processor and executed as a vision training instrument control method with phototherapy function.

[0202] Those skilled in the art will clearly understand that, for the sake of convenience and brevity, the above-described division of functional modules is used as an example. In practical applications, the above functions can be assigned to different functional modules as needed, that is, the internal structure of the device can be divided into different functional modules to complete all or part of the functions described above. The specific working process of the system, device, and unit described above can be referred to the corresponding process in the foregoing method embodiments, and will not be repeated here.

[0203] The above are all preferred embodiments of this application and are not intended to limit the scope of protection of this application. Any feature disclosed in this specification (including the abstract and drawings) may be replaced by other equivalent or similar features unless specifically stated otherwise. That is, unless specifically stated otherwise, each feature is only one example of a series of equivalent or similar features.

Claims

1. A control method for a vision training instrument with phototherapy function, characterized in that, include: Obtain the user's refractive error information; The light source is adjusted to compensate for refractive error based on the refractive error information, so that the light output from the light source is focused on the retinal imaging plane after passing through the light source modulation plate, thus obtaining the reference optical path after refractive compensation. The control light source modulation board spatially modulates the reference light path, so that the modulated light forms a light distribution image on the retinal imaging plane that includes the central occlusion area and the peripheral partitioned stimulation light spots; A fixed target is generated in the central region of the light distribution image, and the fixed target optical path is fused with the reference optical path through a mirror and a semi-transparent mirror to obtain the fused optical path. Control the fixed target to move back and forth along the visual axis of the fused optical path; The position of the fixation target and the focusing parameters of the light source are corrected based on the user's eye image; Based on the corrected focusing parameters, the output parameters of the light source are adjusted in real time to keep the irradiance output by the light source synchronized with the user's eye accommodation state.

2. The control method for a vision training instrument with phototherapy function according to claim 1, characterized in that, The step of correcting the position of the fixation target and the focusing parameters of the light source based on the user's eye image includes: Real-time acquisition of user's eye images; Extract the pupil center position and corneal reflection point coordinates from the eye image; Calculate the user's visual axis direction based on the pupil center position and the coordinates of the corneal reflector point; The line-of-sight offset is obtained based on the angle between the line-of-sight direction and the fused optical path. Determine if the view axis offset is greater than a preset offset threshold; If so, then calculate the light source focusing error relative to the retinal imaging plane based on the visual axis offset and the optical path relationship between the light source and the user's eye; Correct the focusing parameters of the light source based on the focusing error, so that the focusing plane output by the light source coincides with the retinal imaging plane again; Based on the offset direction and offset magnitude of the line-of-sight offset in the fusion optical path, the imaging offset parameters of the fixed target are calculated. The imaging position parameters of the fixation target are corrected based on the imaging offset parameters, so that the fixation target is imaged in the fovea region of the user's retina.

3. The control method for a vision training instrument with phototherapy function according to claim 1, characterized in that, The method further includes: Obtain the current irradiance of the light source at the current moment; The upper limit threshold of intensity is determined based on the preset prescription dose curve at the current time. Determine whether the current irradiance intensity is greater than the upper limit threshold. If so, then pause the light source output; If not, then obtain the user's eye image sequence; Identify blink events and gaze duration based on eye image sequences; Eye stability indexes are calculated based on blink events and gaze duration; When the eye stability index is less than the preset gaze duration, the irradiance of the light source output and the movement speed of the fixation target are reduced synchronously.

4. The control method for a vision training instrument with phototherapy function according to claim 1, characterized in that, The method further includes: Obtain the user's baseline axial length growth rate and choroidal thickness; The baseline axial growth rate and choroid thickness are input into a preset cloud model to obtain the multi-wavelength combination ratio, pulse frequency and treatment interval. The multi-wavelength combination ratio includes the irradiation proportions of 620nm, 660nm and 850nm wavelengths. Determine whether a user is at high risk of progression based on baseline axial length growth rate and choroidal thickness; In cases where the user is at high risk of development, increase the proportion of 660nm wavelength irradiation in the multi-wavelength combination ratio; Based on the multi-wavelength combination ratio, pulse frequency and treatment interval, a cross-deep stimulation sequence is generated. The cross-deep stimulation sequence includes a step-like pulse packet structure of surface-deep-surface. The light source is controlled to irradiate according to a cross-deep stimulation sequence.

5. The control method for a vision training instrument with phototherapy function according to claim 1, characterized in that, The process of controlling the fixed target to move back and forth along the visual axis of the fused optical path also includes: Establish the synchronous timing relationship between the position change of the fixed target in the fused optical path and the pulse output time of the light source; The light source is controlled to output pulses based on the synchronous timing relationship; Parallax signals in the horizontal or vertical direction are superimposed on a fixed target image.

6. The control method for a vision training instrument with phototherapy function according to claim 1, characterized in that, The method further includes: Switch the target refractive compensation lens in the magnetic refractive compensation lens case according to the refractive power information; Inspect the assembly status of the magnetic refractive compensation lens case; When the assembly status is "assembly complete", read the refractive power of the target refractive compensation lens; Determine whether the refractive power of the target refractive compensation lens matches the refractive power information; If so, the magnetic refractive compensation lens case will be locked and the light source will be activated for refractive compensation adjustment; If not, issue a prescription error alarm and disable the light source.

7. The control method for a vision training instrument with phototherapy function according to claim 6, characterized in that, The method further includes: Obtain user identification information; The work mode is determined based on the user's identification information. The work modes include home mode and outpatient mode. When the work mode is home mode, set the daily training limit to the preset number of times and the maximum training time per session to the preset training time. When the work mode is outpatient mode, grant access to all parameter adjustments.

8. A control system for a vision training instrument with phototherapy function, characterized in that, The system is used to execute the control method for a vision training instrument with phototherapy function as described in any one of claims 1 to 7, comprising: The acquisition module is used to acquire refractive power information; A memory for storing the program of the control method for the vision training instrument with phototherapy function; The processor and the program in the memory can be loaded and executed by the processor to implement the control method of the vision training instrument with phototherapy function.

9. A vision training device with phototherapy function, characterized in that, It includes a memory and a processor, wherein the memory stores a computer program that can be loaded by the processor and executed as described in any one of claims 1 to 7.

10. A computer-readable storage medium, characterized in that, The computer program is stored that can be loaded by a processor and execute the method as described in any one of claims 1 to 7.

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