An ocular illumination device

Abstract

The application discloses an eye irradiation device, which comprises a visual stimulation module, a signal acquisition module, a control module and a light source module; the visual stimulation module is used for providing visual stimulation to a first user to induce a visual evoked potential signal; the signal acquisition module is used for acquiring the visual evoked potential signal of the first user; the control module is connected with the signal acquisition module and the visual stimulation module, and is used for determining an irradiation opportunity and generating an irradiation control signal according to the visual evoked potential signal of the first user; and the light source module is connected with the control module, and is used for emitting irradiation light to the eyes of the first user at the irradiation opportunity according to the irradiation control signal.

Description

Technical Field

[0001] This application belongs to the field of optical technology, specifically relating to an eye illumination device. Background Technology

[0002] In recent years, the application potential of photobiomodulation (PBM) technology in ophthalmology has attracted attention. However, ocular lighting devices in related technologies typically use preset, fixed irradiation times, which can easily induce cellular tolerance, affecting the improvement of vision and the stability of light exposure. Therefore, how to develop an ocular lighting device that can dynamically and intelligently adjust the irradiation timing has become a technical problem that urgently needs to be solved by those skilled in the art. Summary of the Invention

[0003] The purpose of this application is to provide an eye illumination device that can dynamically adjust and individually match the timing of illumination, avoiding the adaptive tolerance problem caused by fixed illumination timing, and improving the accuracy and stability of illumination.

[0004] According to a first aspect of the embodiments of this application, an eye illumination device is provided, the device comprising: The visual stimulation module is used to provide visual stimulation to the first user in order to induce visual evoked potential signals. The signal acquisition module is used to acquire the visual evoked potential signal of the first user; The control module, connected to the signal acquisition module and the visual stimulation module, is used to determine the irradiation timing based on the visual evoked potential signal of the first user and generate an irradiation control signal. The light source module, connected to the control module, is used to emit illumination light to the eyes of the first user at the illumination timing according to the illumination control signal.

[0005] Optionally, as an embodiment, the control module is specifically used to determine the irradiation timing based on the time-domain or frequency-domain characteristics of the visual evoked potential signal of the first user.

[0006] Optionally, as an embodiment, when the control module determines the irradiation timing based on the temporal characteristics of the visual evoked potential signal, the visual stimulation module is specifically used to provide the first user with low-frequency graphic flipping stimulation to induce transient visual evoked potential signals. When the control module determines the irradiation timing based on the frequency domain characteristics of the visual evoked potential signal, the visual stimulation module is specifically used to provide high-frequency flickering stimulation to the first user to induce a steady-state visual evoked potential signal.

[0007] Optionally, as an embodiment, when the visual stimulation module provides low-frequency pattern flipping stimulation to induce transient visual evoked potential signals, the control module is specifically used for: The transient visual evoked potential signal of the first user is matched with the individualized P100 waveform template of the first user to detect the P100 component; Based on the peak occurrence time of the detected i-th P100 component and the occurrence period of the first user's P100 component, predict the peak occurrence time of the (i+1)-th P100 component; i is a positive integer; The irradiation timing is determined based on the peak occurrence time of the (i+1)th P100 component and a preset time offset after the P100 peak of the first user; wherein, the irradiation timing is the peak occurrence time of the (i+1)th P100 component plus the preset time offset.

[0008] Optionally, as an embodiment, during the preprocessing stage, the visual stimulation module is also used to provide graphic flipping stimulation to the first user at a low frequency; The signal acquisition module is also used to acquire the baseline visual evoked potential signal of the first user; The control module is further configured to: create an individualized P100 waveform template for the first user based on the baseline visual evoked potential signal; determine the occurrence period of the P100 components of the first user based on the peak occurrence times of multiple recently detected P100 components of the first user; control the light source module to emit test light at multiple candidate time offsets after the peak of the P100 components of the first user; detect the physiological response parameters of the first user after each emission of test light; and select one from the multiple candidate time offsets as the preset time offset after the peak of the P100 components of the first user based on the physiological response parameters.

[0009] Optionally, as an embodiment, the control module is further configured to: Monitor the amplitude of the P100 component in the transient visual evoked potential signal of the first user; When the amplitude exceeds a first preset threshold, the output power of the light source module is reduced; When the amplitude is lower than the second preset threshold, the light source module is controlled to stop emitting illumination light; Wherein, the first preset threshold is N times the baseline amplitude of the P100 component of the first user, where N is a positive number, and the baseline amplitude of the P100 component of the first user is determined by acquiring the baseline visual evoked potential signal of the first user during the preprocessing stage.

[0010] Optionally, as an embodiment, the control module is specifically used for: The phase error is calculated based on the difference between the actual peak occurrence time and the predicted peak occurrence time of the i-th P100 component. Based on the phase error, an adjustment amount is generated through proportional-integral control; Based on the actual peak occurrence time of the i-th P100 component, the P100 component occurrence cycle of the first user, and the adjustment amount, the peak occurrence time of the (i+1)-th P100 component is predicted.

[0011] Optionally, as an embodiment, the control module is specifically used for: The irradiation timing is determined based on the peak occurrence time of the (i+1)th P100 component, the preset time offset after the P100 peak of the first user, and the system delay duration. Wherein, the system delay duration is the time interval from the generation of the illumination control signal to the emission of illumination light by the light source module; the illumination timing is the peak occurrence time of the (i+1)th P100 component plus the preset time offset and then minus the system delay duration.

[0012] Optionally, as an embodiment, the control module is further configured to: If no P100 component is detected within a preset time after the peak occurrence time of the (i+1)th P100 component, the system enters hold mode. In the holding mode, the peak occurrence time of the subsequent P100 component is predicted according to the occurrence cycle of the P100 component of the first user, and the light source module is controlled to emit irradiation light at the determined irradiation time. If the P100 component is not detected for several consecutive cycles in the hold mode, the light source module is controlled to pause the emission of illumination light and initiate recalibration.

[0013] Optionally, as an embodiment, when the visual stimulation module provides high-frequency flickering stimulation to induce steady-state visual evoked potential signals, the control module is specifically used to determine the preset phase window of the steady-state visual evoked potential signal of the first user as the irradiation timing; wherein, the preset phase window is near the rising zero point of the steady-state visual evoked potential signal period.

[0014] Optionally, as an embodiment, the control module is further configured to control the pulse frequency of the illumination light emitted by the light source module to be synchronized with the main frequency of the steady-state visual evoked potential signal.

[0015] Optionally, as an embodiment, the control module is further configured to: During the preprocessing stage, the visual stimulation module is controlled to sequentially provide high-frequency flashing stimulation at multiple different frequencies; Based on the response amplitude of the collected visual evoked potential signals, the frequency with the largest response amplitude is determined as the frequency of the high-frequency flickering stimulus.

[0016] Optionally, as an embodiment, the control module is further configured to: Monitor the amplitude of the steady-state visual evoked potential signal of the first user; When the amplitude exceeds a preset third threshold, the output power of the light source module is reduced; When the amplitude is lower than a preset fourth threshold, the light source module is controlled to stop emitting illumination light. The preset third threshold is M times the baseline amplitude of the steady-state visual evoked potential signal of the first user, where M is a positive number. The baseline amplitude of the steady-state visual evoked potential signal of the first user is determined by collecting the baseline visual evoked potential signal of the first user during the preprocessing stage.

[0017] Optionally, as an embodiment, the signal acquisition module is further configured to acquire auxiliary physiological signals of the first user; wherein, the auxiliary physiological signals include: electroretinography signals and / or visual cortical blood oxygenation signals; The control module is specifically used to determine the irradiation timing based on the visual evoked potential signal of the first user when the auxiliary physiological signal meets the preset conditions. The preset conditions include at least one of the following: the amplitude of the auxiliary physiological signal is within a preset amplitude range, the waveform of the auxiliary physiological signal matches a preset waveform template, and the auxiliary physiological signal indicates that the eye tissue is in an optimal state.

[0018] According to a second aspect of the embodiments of this application, a computer-readable storage medium is provided, which stores a computer program that, when executed by a processor, implements the function of the control module in the eye illumination device of the first aspect.

[0019] In this embodiment, the eye illumination device includes: a visual stimulation module, a signal acquisition module, a control module, and a light source module; wherein, the visual stimulation module is used to provide visual stimulation to a first user to induce visual evoked potential signals; the signal acquisition module is used to acquire the visual evoked potential signals of the first user; the control module is used to determine the irradiation timing based on the visual evoked potential signals of the first user and generate an irradiation control signal; and the light source module is used to emit irradiation light to the eyes of the first user at the irradiation timing according to the irradiation control signal.

[0020] As can be seen, in this embodiment of the application, by referring to the user's visual evoked potential signal to determine the irradiation timing in real time, and delivering light at the time window when the user's visual cortex is most excited, dynamic adjustment and individualized matching of the irradiation timing are achieved, avoiding the adaptive tolerance problem caused by fixed irradiation timing, and improving the accuracy and stability of light irradiation. Attached Figure Description

[0021] Figure 1 These are schematic diagrams of the structure of an eye-illuminating device provided in some embodiments of this application; Figure 2 This is a flowchart of an eye illumination device control method provided in some embodiments of this application. Detailed Implementation

[0022] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of this application. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0023] It should be understood that the terms "comprising" and "including" used in the specification and claims of this application indicate the presence of the described features, integrals, steps, operations, elements and / or components, but do not exclude the presence or addition of one or more other features, integrals, steps, operations, elements, components and / or collections thereof.

[0024] It should also be understood that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the application. As used in this specification and claims, the singular forms “a,” “an,” and “the” are intended to include the plural forms unless the context clearly indicates otherwise. It should also be understood that the term “and / or” as used in this specification and claims refers to any combination and all possible combinations of one or more of the associated listed items, and includes such combinations.

[0025] As used in this specification and claims, the term "if" may be interpreted, depending on the context, as "when," "once," "in response to determination," or "in response to detection." Similarly, the phrase "if determined" or "if the described condition or event is detected" may be interpreted, depending on the context, as meaning "once determined."

[0026] To facilitate understanding, the relevant concepts and application scenarios involved in the embodiments of this application will be introduced below.

[0027] I. Related Concepts Photobiomodulation (PBM) refers to a non-invasive intervention method that uses light of specific wavelengths (usually in the red to near-infrared range, such as 630nm to 680nm or 810nm to 850nm) to irradiate biological tissues. Through intracellular photobiomodulation effects, it promotes mitochondrial function, improves cell metabolism, and regulates local blood perfusion, thereby influencing tissue function. In ophthalmology, PBM is mainly used for myopia control and retinal function maintenance.

[0028] Visual evoked potentials (VEPs) refer to the electrical activity generated in the visual cortex by visual stimuli. They are recorded using scalp electrodes and reflect the functional state of the entire visual pathway from the retina to the visual cortex. Depending on the stimulation frequency, VEPs can be divided into transient VEPs (evoked by low-frequency stimuli, with waveform separation) and steady-state VEPs (evoked by high-frequency stimuli, with continuous waveform oscillation).

[0029] The P100 component refers to the positive wave that appears about 100ms after stimulation in the visual evoked potential signal. It is a core indicator for assessing the conduction function of the visual pathway. Its latency reflects the nerve conduction velocity, and its amplitude reflects the number of neurons involved in the response.

[0030] Electroretinogram (ERG) refers to the electrical activity generated in the retina by light stimulation, which is recorded by corneal or periocular electrodes and reflects the functional state of the inner retina, including photoreceptor cells and bipolar cells.

[0031] Visual cortical blood oxygenation signal refers to the change in blood oxygen concentration in the visual cortex region detected by functional near-infrared spectroscopy (fNIRS), reflecting the level of blood perfusion and metabolic activity in local brain tissue.

[0032] II. Application Scenarios The ocular illumination device provided in this application embodiment can be applied to visual function intervention in ophthalmic clinical and home settings.

[0033] In myopia prevention and control scenarios, eye illumination devices deliver light during the optimal time window for visual cortex excitability by dynamically adjusting the timing of illumination, thereby enhancing the neuromodulation effect of the visual pathway and slowing down the growth of the axial length of the eye.

[0034] In retinal function maintenance scenarios, eye illumination devices can combine electroretinography signals to judge the retinal state in real time, enabling coordinated intervention across the entire pathway from the retina to the visual cortex.

[0035] In amblyopia rehabilitation training scenarios, eye illumination devices can be synchronized with visual stimulation, providing light intervention during the time window when the cortex has high plasticity, thereby promoting the recovery of visual function.

[0036] The eye illumination device provided in this application 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 this application.

[0037] Considering that fixed-timing light stimulation can easily lead to adaptive tolerance in biological tissues and mismatch with the intrinsic physiological rhythms of tissues such as retinal blood vessels, this is a key factor limiting the long-term efficacy of photobiological beam irradiation (PBM). Therefore, in this embodiment, the irradiation timing is determined in real-time by referring to visual evoked potential signals, delivering light during the optimal time window for visual cortex excitability. This avoids the adaptive tolerance problem caused by fixed irradiation timing and synchronizes with the intrinsic physiological rhythms of tissues such as retinal blood vessels, thereby enhancing the effect of photobiological modulation on improving the user's vision.

[0038] Figure 1 This is one of the structural schematic diagrams of an eye-illuminating device provided in some embodiments of this application, such as... Figure 1 As shown, the eye illumination device 100 may include: a visual stimulation module 101, a signal acquisition module 102, a control module 103, and a light source module 104.

[0039] The visual stimulation module 101 is used to provide visual stimulation to the first user in order to induce visual evoked potential signals.

[0040] In this embodiment of the application, the first user refers to the user who receives eye light irradiation and photobiological modulation intervention.

[0041] In this embodiment, the visual stimulation module can select transient or steady-state mode to operate according to the instructions of the control module, and output graphic stimulation or flash stimulation with different frequencies, contrasts, and spatial frequencies.

[0042] In this embodiment, in transient mode, the visual stimulation module outputs graphic flipping stimuli at a low frequency (1-3Hz), with each stimulus interval greater than the duration of the visual cortex response (approximately 300-500ms). This ensures that the waveforms evoked by each stimulus do not overlap in time, forming separate, independent waveform sequences (including N75, P100, N135, etc.). This mode is suitable for individualized parameter calibration during initial use, establishing an individualized profile by acquiring the P100 latency and amplitude of the first user.

[0043] For example, in transient mode, the visual stimulation module outputs a black and white checkerboard flipping stimulus at a frequency of 2Hz, with the size of each checkerboard square set to a viewing angle of 0.5° to 2° and the stimulation contrast being 100%.

[0044] In this embodiment, under steady-state mode, the visual stimulation module outputs flashing stimuli at a high frequency (8-15Hz), with the stimulation interval being shorter than the duration of the visual cortical response (approximately 100-125ms). This allows the cortical responses induced by each stimulus to be superimposed and fused over time, forming a continuous steady-state oscillation waveform with the same frequency as the stimulus. This mode is suitable for long-term use scenarios, utilizing the resonant characteristics of cortical oscillations to achieve high-frequency continuous triggering.

[0045] For example, in steady-state mode, the visual stimulation module outputs uniform flashing stimulation across the entire field of vision or high-frequency flipping checkerboard stimulation at a frequency of 10Hz, and the stimulation frequency can be calibrated according to the individual optimal resonant frequency of the first user.

[0046] In this embodiment, by providing adjustable transient and steady-state stimulation modes, flexible selection can be made according to different application scenarios: the transient mode is used for individualized parameter calibration and conduction function assessment, while the steady-state mode is used for efficient continuous illumination. The combination of the two modes achieves complete coverage from parameter establishment to long-term intervention.

[0047] The signal acquisition module 102 is used to acquire the visual evoked potential signal of the first user.

[0048] In this embodiment, the signal acquisition module may include: scalp electrodes, a signal amplifier, and an analog-to-digital conversion unit. The scalp electrodes are placed in the occipital region (Oz site) as recording electrodes according to the international 10-20 system, and in the frontal region (Fz site) as reference electrodes, to detect weak electrical activity generated by the visual cortex.

[0049] The signal amplifier amplifies the weak electrical activity signals acquired by the scalp electrodes. Visual evoked potential signals typically have amplitudes of only 0.5 μV to 20 μV, far lower than the amplitudes of environmental noise and the body's own electrical activity (such as electromyography and electrocardiography). The signal amplifier amplifies the acquired raw signal by 10,000 to 100,000 times, bringing it into the voltage range recognizable by the analog-to-digital converter. Simultaneously, common-mode rejection technology eliminates common-mode interference introduced by the electrode-skin interface, improving the signal-to-noise ratio.

[0050] The analog-to-digital converter (ADC) unit converts the analog voltage signal output from the amplifier into a digital signal for digital signal processing by the control module. The ADC unit samples the amplified signal at a sampling rate of 1000Hz, i.e., one data point is acquired every 1ms, ensuring the capture of subtle temporal characteristics of the P100 component. The conversion accuracy is 24 bits, capable of resolving voltage changes at the μV level, meeting the accuracy requirements for visual evoked potential signal processing. The converted digital signal is transmitted to the control module via a communication interface.

[0051] For example, the signal acquisition module can use Ag / AgCl dry electrodes with an electrode impedance controlled below 5kΩ to ensure signal quality. The acquired raw EEG signals are processed by a 0.5-100Hz bandpass filter and then converted from analog to digital at a sampling rate of 1000Hz and a resolution of 24 bits to ensure accurate capture of the P100 component with an amplitude of 3-25μV.

[0052] In this embodiment, high-precision, low-noise signal acquisition enables the real-time acquisition of high-quality visual evoked potential signals, providing a reliable data foundation for subsequent signal processing and determination of illumination timing.

[0053] The control module 103 is connected to the signal acquisition module 102 and the visual stimulation module 101, and is used to determine the irradiation timing and generate an irradiation control signal based on the visual evoked potential signal of the first user.

[0054] In this embodiment, the control module is the core processing unit of the eye illumination device. In transient mode, the control module matches the real-time acquired transient visual evoked potential signal with the individualized P100 waveform template of the first user, detects the peak occurrence time of the P100 component, and calculates the illumination timing by combining it with a preset time offset. In steady-state mode, the control module extracts the phase of the steady-state visual evoked potential signal and uses a preset phase window (such as rising to near zero) as the illumination timing. For specific processing procedures, please refer to subsequent embodiments.

[0055] In this embodiment, by referring to the visual evoked potential signal to determine the irradiation timing in real time, it is possible to achieve a precise match between the irradiation timing and the excitability state of the visual cortex, thus avoiding the adaptive tolerance problem caused by fixed-timing irradiation. The light source module 104 is connected to the control module 103 and is used to emit illumination light to the eyes of the first user at the illumination time according to the illumination control signal. The light source module includes a light source driving circuit and a light-emitting element, and can output red light or near-infrared light of a specific wavelength.

[0056] In some embodiments, the light source module may include at least one light-emitting unit, implemented using a light-emitting diode or a laser diode, which projects the emitted light uniformly onto the user's eye through an optical lens group. The light source module supports multiple operating modes, including continuous illumination mode and pulse illumination mode, and the pulse frequency can be adjusted within a certain range.

[0057] In some embodiments, the light source module may employ red light of 630nm to 680nm and / or near-infrared light of 810nm to 850nm, with an output power density ranging from 8mW / cm² to 50mW / cm² and a pulse width that can be set from 5ms to 20ms.

[0058] In this embodiment, in transient mode, the light source module outputs a single light pulse at the irradiation timing determined by the control module; in steady-state mode, the light source module continuously outputs a pulse sequence synchronized with the main frequency of the steady-state visual evoked potential signal within the phase window.

[0059] In this embodiment, by precisely controlling the timing of irradiation and light output parameters, light is delivered during the time window when the visual cortex is most excitable, which can improve the efficiency of photobiological regulation.

[0060] As can be seen from the above embodiments, in this embodiment, by referring to the user's visual evoked potential signal to determine the irradiation timing in real time, and delivering light during the time window when the visual cortex is most excitable, dynamic adjustment and individualized matching of the irradiation timing are achieved, avoiding the adaptive tolerance problem caused by fixed irradiation timing, and improving the accuracy and stability of light irradiation.

[0061] In some embodiments provided in this application, the control module is specifically used to determine the irradiation timing based on the time-domain or frequency-domain characteristics of the visual evoked potential signal of the first user.

[0062] In this embodiment, the time-domain features correspond to the transient mode, and the frequency-domain features correspond to the steady-state mode.

[0063] In this embodiment, in transient mode, the visual evoked potential signal manifests as independent waveforms separated after each stimulus, and its temporal characteristics include the latency and amplitude of components such as N75, P100, and N135. The control module calculates the irradiation timing by detecting the peak occurrence time of the P100 component and combining it with a preset time offset.

[0064] In this embodiment, under steady-state mode, high-frequency stimulation causes the visual evoked potential signals to superimpose into continuous steady-state oscillations, the frequency domain characteristics of which are characterized by significant energy distribution at the stimulation frequency and its harmonics. The control module extracts the oscillation phase and uses a preset phase window as the irradiation timing.

[0065] For example, during initial use, the control module employs time-domain feature processing to detect the peak occurrence time of the P100 component through template matching, and uses the sum of the peak occurrence time and a preset time offset as the irradiation timing. In subsequent long-term use, the control module switches to frequency-domain feature processing, extracts the phase of the 10Hz steady-state oscillation, and uses the period near the zero point (0° to 45°) as the irradiation timing, achieving continuous triggering for each oscillation cycle.

[0066] As can be seen, in this embodiment of the application, by selecting the time domain or frequency domain processing path according to the signal characteristics, it is possible to obtain individualized parameters (P100 latency, amplitude) when using it for the first time, and to achieve high-frequency continuous triggering when using it for a long time, thus taking into account both the accuracy of parameter calibration and the efficiency of long-term intervention.

[0067] In some embodiments provided in this application, the visual stimulation module can provide corresponding low-frequency pattern flipping stimulation or high-frequency flashing stimulation according to the time domain or frequency domain processing path selected by the control module, so as to induce visual evoked potential signals of the corresponding pattern.

[0068] In this embodiment, when the control module determines the irradiation timing based on the temporal characteristics of the visual evoked potential signal, the visual stimulation module is specifically used to provide low-frequency pattern flipping stimulation to the first user to induce transient visual evoked potential signals. At this time, the stimulation frequency is typically 1Hz to 3Hz, and the interval between each stimulation is greater than the duration of the visual cortex response, ensuring that the waveforms evoked by each stimulation do not overlap in time, forming separate independent waveform sequences such as N75, P100, and N135.

[0069] In this embodiment, when the control module determines the irradiation timing based on the frequency domain characteristics of the visual evoked potential signal, the visual stimulation module is specifically used to provide high-frequency flickering stimulation to the first user to induce a steady-state visual evoked potential signal. At this time, the stimulation frequency is typically 8Hz to 15Hz, and the stimulation interval is less than the duration of the visual cortical response, allowing the cortical responses induced by each stimulus to be superimposed and fused in time, forming a continuous steady-state oscillation waveform with the same stimulation frequency.

[0070] For example, during the initial use phase, the control module selects the time-domain processing path, and the visual stimulation module outputs a black and white checkerboard flipping stimulus at a frequency of 2Hz. Each square of the checkerboard is set with a viewing angle of 0.5° to 2°, and the stimulation contrast is 100%, inducing a clear transient visual evoked potential waveform. In the subsequent long-term use phase, the control module switches to the frequency-domain processing path, and the visual stimulation module outputs a uniform flashing stimulus across the entire field of view or a high-frequency flipping checkerboard stimulus at a frequency of 10Hz, inducing stable steady-state visual evoked potential oscillations.

[0071] As can be seen, in this embodiment, by switching the visual stimulation mode according to the processing path of the control module, the characteristics of the visual evoked potential signal are ensured to match the analysis method of the control module: low-frequency stimulation produces separate time-domain waveforms, which facilitates the extraction of P100 latency and amplitude; high-frequency stimulation produces continuous frequency-domain oscillations, which facilitates phase locking and high-frequency triggering. The switching between the two modes achieves complete coverage from individualized parameter calibration to efficient continuous use.

[0072] In some embodiments provided in this application, corresponding to the transient mode, when the visual stimulation module provides low-frequency graphic flipping stimulation to induce transient visual evoked potential signals, the control module is specifically used for: The transient visual evoked potential signal of the first user is matched with the individualized P100 waveform template of the first user to detect the P100 component; Based on the peak occurrence time of the detected i-th P100 component and the occurrence period of the first user's P100 component, predict the peak occurrence time of the (i+1)-th P100 component; i is a positive integer; The irradiation timing is determined based on the peak occurrence time of the (i+1)th P100 component and the preset time offset after the P100 peak of the first user; wherein, the irradiation timing is the peak occurrence time of the (i+1)th P100 component plus the preset time offset.

[0073] In this embodiment, the individualized P100 waveform template refers to a reference waveform sequence established based on the baseline visual evoked potential signal of the first user, reflecting the unique P100 waveform morphology of that first user. Since different users exhibit individual differences in latency, amplitude, rise edge steepness, and waveform width of their P100 waveforms, a universal template is difficult to accurately match all users. Therefore, it is necessary to establish a unique individualized P100 waveform template for each user.

[0074] During operation, the control module performs sliding cross-correlation matching between the real-time acquired transient visual evoked potential signals and the individualized P100 waveform template. When the similarity exceeds a preset threshold, the P100 component is detected. The use of individualized P100 waveform templates can effectively avoid missed or false detections caused by differences in waveform morphology, thus improving the accuracy of P100 component detection.

[0075] During the preprocessing stage, the visual stimulation module is also used to provide low-frequency graphic flipping stimulation to the first user; the signal acquisition module is also used to acquire the baseline visual evoked potential signal of the first user; and the control module is also used to create an individualized P100 waveform template for the first user based on the baseline visual evoked potential signal. Specifically, the control module filters out high-quality responses without blinking or electromyographic interference from the recorded signals, and averages the selected responses point by point to obtain the average waveform as the individualized P100 waveform template for the first user.

[0076] In this embodiment, the P100 component occurrence period refers to the time interval between two consecutive peak occurrences of the P100 component. Under low-frequency pattern flip stimulation conditions, the stimulation interval is fixed (e.g., 2Hz stimulation corresponds to a 500ms interval), but due to physiological fluctuations in nerve conduction, the actual occurrence time of the P100 component will fluctuate within a certain range, and the period is not a constant value. The control module calculates the current period based on the peak occurrence times of multiple recently detected P100 components, and predicts the peak occurrence time of the next P100 component based on this, providing a time reference for phase-locked loop synchronization and irradiation timing calculation.

[0077] The control module maintains the peak occurrence times of multiple recently detected P100 components. Based on the peak occurrence times of multiple P100 components of the first user, it determines the occurrence period of the first user's P100 components. Specifically, it calculates the time interval between adjacent peaks to obtain multiple inter-peak interval values. After removing outliers that deviate from the median by more than two standard deviations, it takes the truncated mean of the remaining intervals as the period estimate. Each time a new P100 component is detected, the period is updated using exponential smoothing, for example, with a smoothing coefficient of 0.15, so that the period estimate can smoothly track the slow changes in physiological rhythm.

[0078] In this embodiment, the preset time offset refers to the time interval between the peak of the P100 component and the optimal light delivery time. Clinical studies have shown that the visual cortex exhibits the highest excitability within a certain time window after the P100 peak, but the specific optimal offset varies depending on individual user differences.

[0079] When determining the irradiation timing, the control module adds a preset time offset to the predicted peak time of the P100 component, so that the light delivery falls precisely within the time window of the highest excitability of the visual cortex, maximizing the neuroplasticity effect of photobiological regulation.

[0080] During the preprocessing stage, the control module controls the light source module to emit test light at multiple candidate time offsets (such as 30ms, 40ms, 50ms, 60ms, 70ms, 80ms, 90ms, 100ms, 110ms, and 120ms) after the peak value of the P100 component of the first user. The control module detects the physiological response parameters of the first user after each emission of test light and selects one of the multiple candidate time offsets as the preset time offset after the peak value of the P100 component of the first user based on the physiological response parameters.

[0081] As can be seen, in the embodiments of this application, in transient mode, the control module detects the P100 component by matching individualized P100 waveform templates, uses a periodic prediction mechanism to predict the peak time of the next P100, and determines the irradiation timing by combining a preset time offset, thereby achieving precise synchronization based on the rhythm of visual cortical electrical activity.

[0082] In some embodiments provided in this application, corresponding to the transient mode, the control module is also used to monitor the amplitude of the P100 component in the transient visual evoked potential signal of the first user; when the amplitude exceeds a first preset threshold, the output power of the light source module is reduced; when the amplitude is lower than a second preset threshold, the light source module is controlled to stop emitting illumination light.

[0083] In this embodiment, the amplitude of the P100 component can reflect the number of visual cortical neurons involved in the response. This amplitude changes dynamically with the functional state of the visual pathway and the process of use, and is an important indicator reflecting the excitability of the cortex and the effect of photobiological regulation.

[0084] In this embodiment, the first preset threshold is N times the baseline amplitude of the P100 component of the first user, where N is a positive number. The baseline amplitude is determined by acquiring the baseline visual evoked potential signal of the first user during the preprocessing stage, reflecting the user's normal response level at rest. The value of N can be set based on clinical experience, for example, 1.5, meaning that power reduction is triggered when the amplitude exceeds 1.5 times the baseline amplitude. The second preset threshold is a preset safety threshold, for example, 0.7 times the baseline amplitude, meaning that stop is triggered when the amplitude is lower than 70% of the baseline amplitude.

[0085] In this embodiment, when the detected amplitude exceeds a first preset threshold, it indicates that the visual cortex is responding too strongly to the current light stimulus, which may pose a risk of over-excitation. The control module reduces the output power of the light source module to avoid over-stimulation. When the detected amplitude is below a second preset threshold, it indicates an abnormal signal (such as poor electrode contact or patient blinking) or a weak cortical response. The control module then controls the light source module to stop emitting illumination light and triggers a safety mechanism.

[0086] For example, in the preprocessing stage, the baseline visual evoked potential signal of the first user is acquired, and the baseline amplitude of the P100 component is measured to be 8.2 μV. The first preset threshold is set to 12.3 μV (1.5 times the baseline), and the second preset threshold is set to 5.7 μV (0.7 times the baseline). During use, the control module monitors the changes in the amplitude of the P100 component in real time. When the amplitude rises to 13 μV, exceeding the first preset threshold, the control module reduces the output power of the light source module by 10%. If the amplitude subsequently falls back to the normal range, the current power is maintained; if the amplitude continues to drop to 5 μV, below the second preset threshold, the control module controls the light source module to stop emitting illumination light and prompts to check the electrode contact or signal quality.

[0087] As can be seen, in this embodiment, by monitoring the amplitude of the P100 component in real time and dynamically adjusting the output power, the power is automatically reduced when the cortical response is too strong, avoiding adaptive tolerance or potential risks caused by overstimulation; when the signal is abnormal, illumination is stopped in time to ensure safe use. Simultaneously, based on individualized baseline threshold settings, it adapts to the physiological differences of different users, achieving individualized safety control. This allows the eye illumination device to automatically adjust the output according to the user's real-time physiological state, maintaining a reasonable stimulation intensity and improving the long-term effectiveness and safety of photobiological regulation.

[0088] In some embodiments provided in this application, corresponding to the transient mode, the control module is specifically used to calculate the phase error based on the difference between the actual peak occurrence time and the predicted peak occurrence time of the detected i-th P100 component; generate an adjustment amount through proportional-integral control based on the phase error; and predict the peak occurrence time of the (i+1)-th P100 component based on the actual peak occurrence time of the i-th P100 component, the P100 component occurrence period of the first user, and the adjustment amount.

[0089] In this embodiment, the control module maintains the synchronization between the P100 component occurrence rhythm and the illumination triggering sequence through a phase-locked loop mechanism. It dynamically corrects the prediction of the next P100 component peak occurrence time by utilizing the deviation between the actual peak occurrence time and the predicted peak occurrence time, thereby achieving accurate periodic tracking.

[0090] In this embodiment, the control module compares the actual peak occurrence time of the detected i-th P100 component with the predicted peak occurrence time, and calculates the difference between the two as the phase error. This error reflects the degree of deviation between the current prediction and the actual occurrence; a positive value indicates that the actual occurrence is later than the prediction, and a negative value indicates that the actual occurrence is earlier than the prediction.

[0091] In this embodiment, the control module processes the phase error using a proportional-integral controller to generate an adjustment amount. The proportional part responds instantly to the current error, while the integral part compensates for historical accumulated errors. The combination of the two allows the adjustment amount to both quickly respond to instantaneous fluctuations and eliminate long-term accumulated deviations.

[0092] In this embodiment, the control module predicts the peak occurrence time of the (i+1)th P100 component based on the actual peak occurrence time of the i-th P100 component, the P100 component occurrence period of the first user, and the generated adjustment amount. This predicted value equals the actual peak occurrence time plus the period plus the adjustment amount, enabling the prediction to be dynamically corrected based on error feedback.

[0093] For example, the current occurrence period of P100 component is 500ms, and the predicted peak occurrence time of the (i+1)th P100 component is 1500ms. The actual detected peak occurrence time of the (i+1)th P100 component is 1498ms, with a phase error of -2ms (actually earlier than predicted). The proportional-integral controller generates an adjustment of -0.5ms based on this error. When predicting the peak occurrence time of the (i+2)th P100 component, the control module uses the actual peak occurrence time of the (i+1)th P100 component (1498ms) as a reference, adds the period of 500ms, and adds the adjustment of -0.5ms, obtaining a predicted value of 1997.5ms. After 5 to 8 iterations, the prediction error gradually converges to within 3ms, achieving steady-state phase-locked loop.

[0094] As can be seen, in this embodiment, the prediction of the peak occurrence time of the P100 component is corrected in real time through a phase-locked loop mechanism, enabling the predicted value to dynamically track the fluctuations of the user's physiological rhythm and avoid synchronization deviations caused by physiological variations in nerve conduction time. The introduction of proportional-integral control balances response speed and steady-state accuracy, eliminating accumulated errors while ensuring rapid tracking, achieving precise periodic synchronization, and providing a reliable time reference for accurate calculation of irradiation timing.

[0095] In some embodiments provided in this application, corresponding to the transient mode, the control module is specifically used to determine the irradiation timing based on the peak occurrence time of the (i+1)th P100 component, the preset time offset after the P100 peak of the first user, and the system delay duration; wherein, the system delay duration is the time interval from the generation of the irradiation control signal to the emission of irradiation light by the light source module; the irradiation timing is the peak occurrence time of the (i+1)th P100 component plus the preset time offset and then minus the system delay duration.

[0096] In this embodiment, when determining the irradiation timing, the control module incorporates the inherent hardware delay of the system into the calculation and compensates for the time difference between the generation of the irradiation control signal and the actual emission of irradiation light by the light source module by triggering in advance, so as to ensure that the light delivery time is precisely aligned with the preset time offset after the P100 peak.

[0097] In this embodiment, the system delay refers to the time interval between the generation of the illumination control signal by the control module and the actual emission of illumination light by the light source module, mainly including the digital-to-analog conversion delay and the light source drive response delay. This delay is determined by hardware characteristics and can be measured before the device leaves the factory or calibrated during use.

[0098] In this embodiment, the control module determines the irradiation timing based on the predicted peak occurrence time of the (i+1)th P100 component, the preset time offset after the P100 peak of the first user, and the system delay duration. The irradiation timing is equal to the peak occurrence time of the (i+1)th P100 component plus the preset time offset minus the system delay duration. That is, the control module sends a trigger signal in advance before the predicted peak occurrence time of the P100 component, so that the light source module emits irradiation light at the expected time after compensating for hardware delay.

[0099] For example, the predicted peak occurrence time of the (i+1)th P100 component is 1500ms, the preset time offset after the first user's P100 peak is 60ms, and the system delay is 0.3ms. Without delay compensation, the control module generates the illumination control signal at 1500ms plus 60ms, i.e., 1560ms, and the light source module actually emits the illumination light at 1560.3ms, which is 0.3ms later than the expected 1560ms. After delay compensation, the control module calculates the illumination timing as 1500ms plus 60ms minus 0.3ms, i.e., 1559.7ms, and generates the illumination control signal at this time. The light source module actually emits the illumination light at 1559.7ms plus 0.3ms, i.e., 1560ms, precisely aligned with the expected time.

[0100] As can be seen, in this embodiment of the application, by compensating for the system hardware delay, the time deviation between the trigger command and the actual light output is eliminated, so that the light delivery time is precisely aligned with the preset time offset after the P100 peak, ensuring that the synchronization accuracy is not affected by the hardware response speed. In the millisecond-level precision photobiological regulation application, the consistency between the theoretical design time and the actual light output time is achieved, and the accuracy of synchronization control is improved.

[0101] In some embodiments provided in this application, corresponding to the transient mode, the control module is also configured to enter the hold mode when no P100 component is detected within a preset time after the peak occurrence time of the (i+1)th P100 component. In hold mode, the peak occurrence time of subsequent P100 components is predicted according to the occurrence cycle of the first user's P100 components, and the light source module is controlled to emit irradiation light at the determined irradiation time. If the P100 component is not detected for several consecutive cycles in hold mode, the control light source module pauses the emission of illumination light and initiates recalibration.

[0102] In this embodiment, in transient mode, the control module can perform fault-tolerant processing for signal loss. When the predicted P100 component does not appear within the expected time, it enters hold mode to maintain continuous illumination based on periodic prediction. If it does not recover for a long time, it automatically pauses and recalibrates to ensure stable operation of the eye illumination device when the signal is abnormal.

[0103] In this embodiment, after the control module predicts the peak occurrence time of the (i+1)th P100 component, it continuously detects for a preset duration (e.g., 1.5 times the cycle) after that time. If the P100 component is not detected within this duration, it is determined to be a signal loss, which may be caused by the patient blinking, poor electrode contact, head movement, or external interference.

[0104] In this embodiment, after entering the hold mode, the control module no longer relies on real-time signal detection. Instead, it continues to predict the peak occurrence time of subsequent P100 components according to the occurrence cycle of the first user's P100 components. Based on this prediction value, combined with a preset time offset and system delay duration, it determines the irradiation timing and controls the light source module to continue emitting irradiation light. In hold mode, the illumination is uninterrupted, maintaining the continuity of illumination.

[0105] In this embodiment, if the P100 component is not detected for several consecutive cycles (e.g., 5 cycles) in hold mode, it indicates that the signal loss problem has not been resolved automatically. The control module controls the light source module to pause the emission of illumination light and initiates a recalibration process, prompting the user to check the electrode contact or signal quality. If the signal is restored in hold mode, the control module automatically exits hold mode and resumes normal operation based on real-time signal detection.

[0106] For example, the predicted peak occurrence time of the (i+1)th P100 component is 1500ms, with a preset duration of 750ms (1.5 times the period of 500ms). If the P100 component is not detected within 1500ms to 2250ms, the control module determines that the signal has been lost and enters hold mode. In hold mode, the control module continues to predict the subsequent peak occurrence time at a period of 500ms, predicting the P100 component peak at 2000ms, 2500ms, etc., and calculates the illumination timing accordingly to control the light source module to emit illumination light. If the P100 component is still not detected after 5 consecutive periods (i.e., 5 predictions), the control module pauses illumination and initiates a recalibration process, prompting for electrode inspection. If the signal recovers in the 3rd period and the P100 component is detected, the control module automatically exits hold mode and resumes normal operation.

[0107] As can be seen, in this embodiment, the maintain-mode mechanism preserves light output during brief signal loss (such as blinking), avoiding light interruption due to occasional interference and ensuring continuous illumination. By limiting the preset number of cycles, ineffective illumination caused by blind prediction during prolonged signal loss is avoided. Automatic recalibration quickly rebuilds synchronization after signal recovery and promptly pauses and prompts the user to check when the signal remains abnormal, balancing the continuity of illumination with the safety of use.

[0108] In some embodiments provided in this application, corresponding to the steady-state mode, when the visual stimulation module provides high-frequency flickering stimulation to induce steady-state visual evoked potential signals, the control module is specifically used to determine the preset phase window of the steady-state visual evoked potential signal of the first user as the irradiation timing; wherein, the preset phase window is near the rising zero point of the steady-state visual evoked potential signal cycle.

[0109] In this embodiment of the application, in steady-state mode, the control module directly determines the preset phase window as the illumination time. When the phase of the steady-state visual evoked potential signal enters the window, the light source module emits illumination light to achieve continuous triggering based on the oscillation phase.

[0110] In this embodiment, the preset phase window refers to a specific phase interval within the steady-state visual evoked potential signal cycle, which is determined as the triggering condition for illumination delivery. According to clinical studies, the visual cortex exhibits the highest excitability near the rising zero-crossing point of steady-state oscillations; therefore, this window is typically set near the rising zero-crossing point of the cycle. The rising zero-crossing point refers to the region where the oscillation waveform crosses zero from a negative value to a positive value and enters the rising segment, corresponding to a phase of 0° to 45° (i.e., 0 to π / 4 radians).

[0111] In this embodiment, the control module extracts the instantaneous phase of the steady-state visual evoked potential signal in real time and compares this phase with a preset phase window. When the phase falls within the preset phase window, the control module controls the light source module to emit illumination light; when the phase leaves the preset phase window, the control module controls the light source module to stop emitting illumination light. Since the steady-state oscillation is continuous, the control module continuously triggers within the window during each oscillation cycle, forming periodic continuous illumination.

[0112] For example, the steady-state visual evoked potential signal frequency of the first user is set to 10Hz, the period is 100ms, and the preset phase window is 0° to 45° (corresponding to 0ms to 12.5ms). The control module extracts the instantaneous phase of the steady-state oscillation in real time. Within the time frame of 0ms to 12.5ms, when the phase is between 0° and 45°, the control module controls the light source module to emit illumination light; within the time frame of 12.5ms to 100ms, when the phase is between 45° and 360°, the control module controls the light source module to stop emitting. In the next cycle, from 100ms to 112.5ms, the phase re-enters the window, and the light source module emits again. This cycle repeats, delivering illumination near the zero-crossing point in each cycle, with the trigger frequency consistent with the steady-state oscillation frequency.

[0113] As can be seen, in this embodiment, by using a preset phase window as the illumination timing, phase synchronization between light delivery and steady-state oscillations of the visual cortex is achieved. Light is delivered near the zero-crossing point where cortical excitability is highest within each oscillation cycle, with a trigger frequency reaching 10Hz, significantly higher than the transient mode (approximately 2Hz), thus increasing the number of light deliveries per unit time. Simultaneously, the phase synchronization mechanism does not rely on the detection and periodic prediction of a single P100 component, simplifying the control logic and making it suitable for long-term, high-efficiency use scenarios.

[0114] In some embodiments provided in this application, corresponding to the steady-state mode, the control module is also used to control the pulse frequency of the illumination light emitted by the light source module to synchronize with the main frequency of the steady-state visual evoked potential signal.

[0115] In this embodiment, the control module controls the pulse frequency of the illumination light emitted by the light source module to be consistent with the main frequency of the steady-state visual evoked potential signal in steady-state mode, so that the rhythm of the illumination pulse and the rhythm of the cortical oscillation form a frequency resonance.

[0116] In this embodiment, the dominant frequency of the steady-state visual evoked potential signal is equal to the frequency of the high-frequency flickering stimulus provided by the visual stimulation module. When the visual stimulation module outputs flickering stimulus at a specific frequency (e.g., 10Hz), the visual cortex generates steady-state oscillations at the same frequency, which is the dominant frequency of the steady-state visual evoked potential signal.

[0117] In this embodiment, the control module sets the pulse emission frequency of the light source module according to the dominant frequency of the steady-state visual evoked potential signal, ensuring consistency between the two. In steady-state mode, the emission frequency of the illumination pulse is equal to the dominant frequency, meaning that a light pulse is emitted once per oscillation cycle, and the timing of the pulse emission is determined by a preset phase window.

[0118] For example, in the preprocessing stage, the optimal resonant frequency for the first user is determined to be 10Hz through frequency scanning. The visual stimulation module outputs high-frequency flickering stimulation at 10Hz to induce a steady-state visual evoked potential signal in the first user, with a dominant frequency of 10Hz. The control module controls the light source module to emit illumination light pulses at a frequency of 10Hz, i.e., one pulse every 100ms, with a pulse width that can be set from 5ms to 20ms. The timing of pulse emission is locked near the rising zero-crossing point of the steady-state oscillation (0° to 45° phase window), ensuring that the frequency and phase of the illumination pulse are synchronized with the cortical oscillation.

[0119] As can be seen, in this embodiment, by synchronizing the light pulse frequency with the dominant frequency of the steady-state visual evoked potential signal, frequency resonance between the light rhythm and the cortical oscillation rhythm is achieved. Frequency synchronization enhances the synergistic effect between photobiological regulation and visual cortical electrical activity, enabling positive coupling between light intervention and the cortical's own rhythm, thereby improving neural regulation efficiency. Simultaneously, frequency synchronization ensures that the light pulse is evenly distributed within each cycle of the steady-state oscillation, avoiding rhythmic interference that may result from frequency mismatch and ensuring stability and consistency over long-term use.

[0120] In some embodiments provided in this application, corresponding to the steady-state mode, the control module is also used to control the visual stimulation module to sequentially provide high-frequency flickering stimulation at multiple different frequencies during the preprocessing stage; and to determine the frequency with the largest response amplitude as the frequency of the high-frequency flickering stimulation based on the response amplitude of the acquired visual evoked potential signal.

[0121] In this embodiment, the control module determines the optimal resonant frequency for the first user through frequency scanning during the preprocessing stage, so that the visual stimulation module provides high-frequency flickering stimulation at this frequency, thereby maximizing the amplitude of the steady-state visual evoked potential signal and establishing individualized visual stimulation parameters for subsequent steady-state mode use.

[0122] In this embodiment, the control module controls the visual stimulation module to sequentially output high-frequency flashing stimuli at multiple different frequencies, typically ranging from 8Hz to 15Hz, covering the frequency band where the visual cortex is sensitive to high-frequency stimuli. Each frequency lasts for a certain duration (e.g., 5 to 10 seconds), allowing the visual cortex sufficient time to establish stable steady-state oscillations. During each frequency stimulation period, the signal acquisition module acquires the visual evoked potential signal of the first user, and the control module calculates the steady-state visual evoked potential signal response amplitude at that frequency.

[0123] In this embodiment, the control module compares the response amplitudes at different frequencies and determines the frequency with the largest response amplitude as the optimal resonant frequency for the first user. This frequency reflects the frequency point at which the first user's visual cortex is most sensitive to high-frequency flickering stimuli, at which the cortical oscillation amplitude is the largest and the resonance effect is the strongest.

[0124] For example, in the preprocessing stage, the control module controls the visual stimulation module to output high-frequency flickering stimuli sequentially at 8Hz, 9Hz, 10Hz, 11Hz, 12Hz, 13Hz, 14Hz, and 15Hz, each frequency lasting 5 seconds. Under 8Hz stimulation, the amplitude of the acquired steady-state visual evoked potential signal is 10μV; at 9Hz, it is 12μV; at 10Hz, it is 18μV; at 11Hz, it is 15μV; at 12Hz, it is 13μV; at 13Hz, it is 11μV; at 14Hz, it is 9μV; and at 15Hz, it is 8μV. The control module determines the 10Hz frequency, which has the largest response amplitude, as the frequency of the high-frequency flickering stimulus. In subsequent steady-state mode use, the visual stimulation module outputs high-frequency flickering stimuli at 10Hz.

[0125] As can be seen, in this embodiment, the optimal resonance frequency is determined through frequency scanning to match the visual stimulus frequency with the inherent oscillation characteristics of the first user's visual cortex, maximizing the amplitude of the steady-state visual evoked potential signal and enhancing the cortical resonance effect. Individualized frequency calibration adapts to the physiological differences of different users, avoiding the problem of poor response in some users due to the use of a fixed frequency, establishing optimal stimulation parameters for steady-state mode use, and improving the efficiency and specificity of photobiological modulation.

[0126] In some embodiments provided in this application, corresponding to the steady-state mode, the control module is also used to monitor the amplitude of the steady-state visual evoked potential signal in the visual evoked potential signal of the first user; when the amplitude exceeds a preset third threshold, the output power of the light source module is reduced; when the amplitude is lower than a preset fourth threshold, the light source module is controlled to stop emitting illumination light.

[0127] In this embodiment, the control module monitors the amplitude of the steady-state visual evoked potential signal of the first user in real time in steady-state mode, and dynamically adjusts the output power of the light source module or executes a safe stop based on the amplitude change.

[0128] In this embodiment, the amplitude of the steady-state visual evoked potential signal, i.e., the peak-to-peak amplitude of the continuous steady-state oscillation induced by high-frequency flickering stimulation, reflects the intensity of the visual cortex's response to high-frequency stimulation. This amplitude changes dynamically with the excitation state of the visual cortex and the progress of use, and is an important indicator reflecting the cortical resonance effect and photobiological modulation effect.

[0129] In this embodiment, the preset third threshold is M times the baseline amplitude of the steady-state visual evoked potential signal of the first user, where M is a positive number. The baseline amplitude is determined by acquiring the baseline visual evoked potential signal of the first user during the preprocessing stage, reflecting the user's normal response level in a resting state. The value of M can be set based on clinical experience, for example, 1.5, meaning that power reduction is triggered when the amplitude exceeds 1.5 times the baseline amplitude. The preset fourth threshold is a preset safety threshold, for example, 0.7 times the baseline amplitude, meaning that stop is triggered when the amplitude is lower than 70% of the baseline amplitude.

[0130] In this embodiment, when the monitored amplitude exceeds a preset third threshold, it indicates that the visual cortex is responding too strongly to the current light stimulus, which may pose a risk of over-excitation. The control module reduces the output power of the light source module to avoid over-stimulation. When the monitored amplitude is below a preset fourth threshold, it indicates an abnormal signal (such as poor electrode contact or patient distraction) or a weak cortical response. The control module then controls the light source module to stop emitting illumination light and triggers a safety mechanism.

[0131] For example, in the preprocessing stage, the baseline visual evoked potential signal of the first user is acquired, and the measured steady-state visual evoked potential signal baseline amplitude is 15 μV. A preset third threshold is set to 22.5 μV (1.5 times the baseline), and a preset fourth threshold is set to 10.5 μV (0.7 times the baseline). During use, the visual stimulation module outputs high-frequency flickering stimulation at 10 Hz, and the control module monitors the steady-state visual evoked potential signal amplitude in real time. When the amplitude rises to 24 μV, exceeding the preset third threshold, the control module reduces the output power of the light source module by 10%. If the amplitude subsequently falls back to the normal range, the current power is maintained; if the amplitude continues to drop to 9 μV, below the preset fourth threshold, the control module controls the light source module to stop emitting illumination light and prompts for checking electrode contact or signal quality.

[0132] As can be seen, in this embodiment, the amplitude of steady-state visual evoked potential signals can be monitored in real time and the output power can be dynamically adjusted. When the cortical response is too strong, the power is automatically reduced to avoid adaptive tolerance or potential risks caused by overstimulation. When the signal is abnormal, illumination is stopped in time to ensure safe use. At the same time, thresholds are set based on individualized baselines to adapt to the physiological differences of different users, realize individualized safety control, and improve the long-term effectiveness and safety of photobiological regulation.

[0133] In some embodiments provided in this application, the signal acquisition module is also used to acquire auxiliary physiological signals of the first user; The control module is specifically used to determine the irradiation timing based on the visual evoked potential signal of the first user, provided that the auxiliary physiological signal meets the preset conditions.

[0134] In this embodiment, the signal acquisition module can acquire auxiliary physiological signals of the first user in addition to acquiring visual evoked potential signals; the control module uses the auxiliary physiological signals as the underlying gating condition, and only determines the irradiation timing based on the visual evoked potential signals when the auxiliary physiological signals meet the preset conditions, thereby realizing two-level collaborative control from the retina to the visual cortex.

[0135] In this embodiment, the auxiliary physiological signals include electroretinography (ERG) signals and / or visual cortical oxygenation signals. ERG signals, acquired via periocular electrodes, reflect the functional state of retinal photoreceptor cells and bipolar cells, and are an important indicator for assessing the quality of signal input at the retinal level. Visual cortical oxygenation signals, acquired via functional near-infrared spectroscopy, reflect the blood perfusion and metabolic activity levels in the visual cortex region, and are an auxiliary indicator for assessing the energy state at the cortical level.

[0136] In this embodiment, preset conditions are used to determine whether the auxiliary physiological signal is in a suitable state for photobiological regulation, including at least one of the following: the amplitude of the auxiliary physiological signal is within a preset amplitude range, indicating normal signal strength; the waveform of the auxiliary physiological signal matches a preset waveform template, indicating normal waveform morphology; the auxiliary physiological signal indicates that the ocular tissue is in an optimal state, indicating that the retina or cortex is in a functional state suitable for receiving light. Both the preset amplitude range and the preset waveform template can be determined by acquiring the baseline auxiliary physiological signal of the first user during the preprocessing stage.

[0137] In this embodiment, the control module first determines whether the auxiliary physiological signal meets preset conditions. If it does, it indicates that the retina or cortex is in a suitable state. The control module then determines the irradiation timing based on the visual evoked potential signal (calculated according to transient or steady-state modes). If the conditions are not met, the control module postpones or pauses irradiation until the auxiliary physiological signal recovers to a state that meets the conditions. The auxiliary physiological signal serves as the bottom-level gating, and the visual evoked potential signal serves as the top-level synchronization, forming a two-level collaborative control system.

[0138] For example, during use, the signal acquisition module acquires the first user's electroretinogram (ERG) signal and visual cortical oxygenation signal in real time. The control module monitors that the ERG signal amplitude is within a preset range and the waveform matches a preset template, indicating normal retinal function. Simultaneously, the visual cortical oxygenation signal amplitude is also within a preset range, indicating sufficient cortical blood perfusion. At this point, the auxiliary physiological signals meet the preset conditions, and the control module determines the irradiation timing based on the visual evoked potential (VAP) signal, controlling the light source module to emit irradiation light. If the first user blinks during use, causing waveform distortion of the ERG signal and exceeding the preset range, the auxiliary physiological signals no longer meet the preset conditions. The control module then pauses determining the irradiation timing based on the VAP signal and resumes only after the signal returns to normal.

[0139] As can be seen, in this embodiment, by introducing auxiliary physiological signals as the underlying gating condition, illumination is temporarily suspended when the retina or cortex is in poor condition, avoiding ineffective or inefficient illumination intervention when the signal input quality is poor or the tissue energy state is insufficient. The dual-level gating achieves end-to-end monitoring of the pathway from the retina to the visual cortex, ensuring that illumination delivery only occurs when retinal function is normal, cortical blood flow is sufficient, and the visual evoked potential signal is within the optimal phase window, thus improving the effectiveness and safety of illumination intervention.

[0140] Corresponding to the ocular illumination devices in the foregoing embodiments, this application also provides a corresponding ocular illumination device control method. This method includes control steps executed by a control module to implement the corresponding functions of the visual stimulation module, signal acquisition module, and light source module in any of the foregoing embodiments.

[0141] Figure 2 This is a flowchart illustrating a method for controlling an eye-illuminating device according to some embodiments of this application, such as... Figure 2 As shown, the method includes the following steps: step 201, step 202, step 203 and step 204.

[0142] In step 201, the visual stimulation module is controlled to provide visual stimulation to the first user in order to induce visual evoked potential signals.

[0143] In step 202, the control signal acquisition module acquires the visual evoked potential signal of the first user.

[0144] In step 203, the irradiation timing is determined based on the visual evoked potential signal of the first user, and an irradiation control signal is generated.

[0145] In step 204, the control light source module emits illumination light to the eyes of the first user at the illumination timing according to the illumination control signal.

[0146] As can be seen from the above embodiments, in this embodiment, by referring to the user's visual evoked potential signal to determine the irradiation timing in real time, and delivering light during the time window when the user's visual cortex is at its most excitable, dynamic adjustment and individualized matching of the irradiation timing are achieved, avoiding the adaptive tolerance problem caused by fixed irradiation timing, and improving the accuracy and stability of light irradiation.

[0147] Optionally, in some embodiments, step 203 above may specifically include: determining the irradiation timing based on the time-domain or frequency-domain characteristics of the visual evoked potential signal of the first user.

[0148] Optionally, in some embodiments, step 203 may specifically include: when the irradiation timing is determined based on the temporal characteristics of the visual evoked potential signal, controlling the visual stimulation module to provide a low-frequency graphic flipping stimulus to the first user to induce a transient visual evoked potential signal; when the irradiation timing is determined based on the frequency domain characteristics of the visual evoked potential signal, controlling the visual stimulation module to provide a high-frequency flashing stimulus to the first user to induce a steady-state visual evoked potential signal.

[0149] Optionally, in some embodiments, step 203 may specifically include: matching the transient visual evoked potential signal of the first user with the individualized P100 waveform template of the first user to detect P100 components; predicting the peak occurrence time of the (i+1)th P100 component based on the peak occurrence time of the detected i-th P100 component and the occurrence period of the P100 component of the first user; determining the irradiation timing based on the peak occurrence time of the (i+1)th P100 component and a preset time offset after the peak of the P100 component of the first user; wherein the irradiation timing is the peak occurrence time of the (i+1)th P100 component plus the preset time offset.

[0150] Optionally, in some embodiments, the method further includes a transient preprocessing step: controlling the visual stimulation module to provide a graphic flipping stimulus to the first user at a low frequency; controlling the signal acquisition module to acquire the baseline visual evoked potential signal of the first user; creating an individualized P100 waveform template for the first user based on the baseline visual evoked potential signal; determining the occurrence period of the P100 components of the first user according to the peak occurrence times of multiple recently detected P100 components of the first user; controlling the light source module to emit test light at multiple candidate time offsets after the peak of the P100 components of the first user, detecting the physiological response parameters of the first user after each emission of test light, and selecting one from the multiple candidate time offsets as the preset time offset after the peak of the P100 components of the first user according to the physiological response parameters.

[0151] Optionally, in some embodiments, step 203 may specifically include: monitoring the amplitude of the P100 component in the transient visual evoked potential signal of the first user; reducing the output power of the light source module when the amplitude exceeds a first preset threshold; and controlling the light source module to stop emitting illumination light when the amplitude is lower than a second preset threshold; wherein the first preset threshold is N times the baseline amplitude of the P100 component of the first user, where N is a positive number, and the baseline amplitude of the P100 component of the first user is determined by acquiring the baseline visual evoked potential signal of the first user during the preprocessing stage.

[0152] Optionally, in some embodiments, step 203 above may specifically include: calculating a phase error based on the difference between the actual peak occurrence time and the predicted peak occurrence time of the detected i-th P100 component; generating an adjustment amount through proportional-integral control based on the phase error; and predicting the peak occurrence time of the (i+1)-th P100 component based on the actual peak occurrence time of the i-th P100 component, the P100 component occurrence period of the first user, and the adjustment amount.

[0153] Optionally, in some embodiments, step 203 above may specifically include: determining the irradiation timing based on the peak occurrence time of the (i+1)th P100 component, the preset time offset after the P100 peak of the first user, and the system delay duration; wherein, the system delay duration is the time interval from the generation of the irradiation control signal to the emission of irradiation light by the light source module; the irradiation timing is the peak occurrence time of the (i+1)th P100 component plus the preset time offset and then minus the system delay duration.

[0154] Optionally, in some embodiments, step 203 may specifically include: when no P100 component is detected within a preset time after the peak occurrence time of the (i+1)th P100 component, entering a hold mode; in the hold mode, continuing to predict the peak occurrence time of subsequent P100 components according to the P100 component occurrence cycle of the first user, and controlling the light source module to emit illumination light at the determined illumination time; when no P100 component is detected for several consecutive cycles in the hold mode, controlling the light source module to pause the emission of illumination light and start recalibration.

[0155] Optionally, in some embodiments, step 203 above may specifically include: when determining the irradiation timing based on the frequency domain characteristics of the visual evoked potential signal, determining a preset phase window of the steady-state visual evoked potential signal of the first user as the irradiation timing; wherein, the preset phase window is near the rising zero-crossing point of the steady-state visual evoked potential signal period.

[0156] Optionally, in some embodiments, step 203 may specifically include: controlling the pulse frequency of the illumination light emitted by the light source module to synchronize with the main frequency of the steady-state visual evoked potential signal.

[0157] Optionally, in some embodiments, the method further includes a steady-state preprocessing step: controlling the visual stimulation module to sequentially provide high-frequency flickering stimulation at multiple different frequencies; and determining the frequency with the largest response amplitude as the frequency of the high-frequency flickering stimulation based on the response amplitude of the acquired visual evoked potential signal.

[0158] Optionally, in some embodiments, step 203 may specifically include: monitoring the amplitude of the steady-state visual evoked potential signal of the first user; reducing the output power of the light source module when the amplitude exceeds a preset third threshold; and controlling the light source module to stop emitting illumination light when the amplitude is lower than a preset fourth threshold; wherein the preset third threshold is M times the baseline amplitude of the steady-state visual evoked potential signal of the first user, M is a positive number, and the baseline amplitude of the steady-state visual evoked potential signal of the first user is determined by acquiring the baseline visual evoked potential signal of the first user during the preprocessing stage.

[0159] Optionally, in some embodiments, step 203 above may specifically include: acquiring auxiliary physiological signals of the first user; wherein the auxiliary physiological signals include: electroretinography signals and / or visual cortical blood oxygenation signals; and, when the auxiliary physiological signals meet preset conditions, determining the irradiation timing based on the visual evoked potential signals of the first user; wherein the preset conditions include at least one of the following: the amplitude of the auxiliary physiological signals is within a preset amplitude range, the waveform of the auxiliary physiological signals matches a preset waveform template, and the auxiliary physiological signals indicate that the ocular tissue is in an optimal state.

[0160] Since the method embodiments and the device embodiments correspond in technical concept and implementation principle, their specific steps, technical features, and beneficial effects can be directly and clearly derived from the understanding of the aforementioned device embodiments. Therefore, the content of the method embodiments will not be repeated here. After reading the device embodiments of this application, those skilled in the art will be able to understand and implement the corresponding control methods without any doubt.

[0161] Additionally or optionally, embodiments of this application can also be implemented as a computer-readable storage medium storing a computer program thereon, which, when executed by a processor, causes the processor to perform some or all of the steps in the above-described method embodiments of this application. The computer-readable storage medium can be any tangible medium containing or storing a program, such as a hard disk, solid-state drive, random access memory, read-only memory, flash memory or other optical disk storage, magnetic disk storage or other magnetic storage devices, or any other medium that can be used to store the required program code and is accessible by a computer.

[0162] While numerous embodiments of this application have been shown and described herein, it will be apparent to those skilled in the art that such embodiments are provided by way of example only. Many modifications, alterations, and alternatives will arise for those skilled in the art without departing from the spirit and intent of this application. It should be understood that various alternatives to the embodiments of this application described herein may be employed in the practice of this application. The appended claims are intended to define the scope of protection of this application and therefore cover equivalents or alternatives within the scope of these claims.

Claims

1. An eye illumination device, characterized in that, The device includes: The visual stimulation module is used to provide visual stimulation to the first user in order to induce visual evoked potential signals. The signal acquisition module is used to acquire the visual evoked potential signal of the first user; The control module, connected to the signal acquisition module and the visual stimulation module, is used to determine the irradiation timing based on the visual evoked potential signal of the first user and generate an irradiation control signal. The light source module, connected to the control module, is used to emit illumination light to the eyes of the first user at the illumination timing according to the illumination control signal.

2. The eye illumination device according to claim 1, characterized in that, The control module is specifically used to determine the irradiation timing based on the time-domain or frequency-domain characteristics of the visual evoked potential signal of the first user.

3. The eye illumination device according to claim 2, characterized in that, When the control module determines the irradiation timing based on the temporal characteristics of the visual evoked potential signal, the visual stimulation module is specifically used to provide the first user with low-frequency graphic flipping stimulation to induce transient visual evoked potential signals. When the control module determines the irradiation timing based on the frequency domain characteristics of the visual evoked potential signal, the visual stimulation module is specifically used to provide high-frequency flickering stimulation to the first user to induce a steady-state visual evoked potential signal.

4. The eye illumination device according to claim 3, characterized in that, When the visual stimulation module provides low-frequency pattern flipping stimulation to induce transient visual evoked potential signals, the control module is specifically used for: The transient visual evoked potential signal of the first user is matched with the individualized P100 waveform template of the first user to detect the P100 component; Based on the peak occurrence time of the detected i-th P100 component and the occurrence period of the first user's P100 component, predict the peak occurrence time of the (i+1)-th P100 component; i is a positive integer; The irradiation timing is determined based on the peak occurrence time of the (i+1)th P100 component and a preset time offset after the P100 peak of the first user; wherein, the irradiation timing is the peak occurrence time of the (i+1)th P100 component plus the preset time offset.

5. The eye illumination device according to claim 4, characterized in that, During the preprocessing stage, the visual stimulation module is also used to provide graphic flipping stimulation to the first user at a low frequency; The signal acquisition module is also used to acquire the baseline visual evoked potential signal of the first user; The control module is also used to create an individualized P100 waveform template for the first user based on the baseline visual evoked potential signal. Based on the peak occurrence times of multiple P100 components of the first user recently detected, the occurrence period of the P100 components of the first user is determined; the light source module is controlled to emit test light at multiple candidate time offsets after the peak of the P100 components of the first user, and the physiological response parameters of the first user are detected after each emission of test light. Based on the physiological response parameters, one of the multiple candidate time offsets is selected as the preset time offset after the peak of the P100 components of the first user.

6. The eye illumination device according to claim 4, characterized in that, The control module is also used for: Monitor the amplitude of the P100 component in the transient visual evoked potential signal of the first user; When the amplitude exceeds a first preset threshold, the output power of the light source module is reduced; When the amplitude is lower than the second preset threshold, the light source module is controlled to stop emitting illumination light; Wherein, the first preset threshold is N times the baseline amplitude of the P100 component of the first user, where N is a positive number, and the baseline amplitude of the P100 component of the first user is determined by acquiring the baseline visual evoked potential signal of the first user during the preprocessing stage.

7. The eye illumination device according to claim 4, characterized in that, The control module is specifically used for: The phase error is calculated based on the difference between the actual peak occurrence time and the predicted peak occurrence time of the i-th P100 component. Based on the phase error, an adjustment amount is generated through proportional-integral control; Based on the actual peak occurrence time of the i-th P100 component, the P100 component occurrence cycle of the first user, and the adjustment amount, the peak occurrence time of the (i+1)-th P100 component is predicted.

8. The eye illumination device according to claim 4, characterized in that, The control module is specifically used for: The irradiation timing is determined based on the peak occurrence time of the (i+1)th P100 component, the preset time offset after the P100 peak of the first user, and the system delay duration. Wherein, the system delay duration is the time interval from the generation of the illumination control signal to the emission of illumination light by the light source module; the illumination timing is the peak occurrence time of the (i+1)th P100 component plus the preset time offset and then minus the system delay duration.

9. The eye illumination device according to claim 4, characterized in that, The control module is also used for: If no P100 component is detected within a preset time after the peak occurrence time of the (i+1)th P100 component, the system enters hold mode. In the holding mode, the peak occurrence time of the subsequent P100 component is predicted according to the occurrence cycle of the P100 component of the first user, and the light source module is controlled to emit irradiation light at the determined irradiation time. If the P100 component is not detected for several consecutive cycles in the hold mode, the light source module is controlled to pause the emission of illumination light and initiate recalibration.

10. The eye illumination device according to claim 3, characterized in that, When the visual stimulation module provides high-frequency flickering stimulation to induce steady-state visual evoked potential signals, the control module is specifically used to determine the irradiation timing as a preset phase window of the steady-state visual evoked potential signal of the first user; wherein, the preset phase window is near the rising zero-crossing point of the steady-state visual evoked potential signal period.

11. The eye illumination device according to claim 10, characterized in that, The control module is also used to control the pulse frequency of the illumination light emitted by the light source module to be synchronized with the main frequency of the steady-state visual evoked potential signal.

12. The eye illumination device according to claim 10, characterized in that, The control module is also used for: During the preprocessing stage, the visual stimulation module is controlled to sequentially provide high-frequency flashing stimulation at multiple different frequencies; Based on the response amplitude of the collected visual evoked potential signals, the frequency with the largest response amplitude is determined as the frequency of the high-frequency flickering stimulus.

13. The eye illumination device according to claim 10, characterized in that, The control module is also used for: Monitor the amplitude of the steady-state visual evoked potential signal of the first user; When the amplitude exceeds a preset third threshold, the output power of the light source module is reduced; When the amplitude is lower than a preset fourth threshold, the light source module is controlled to stop emitting illumination light. The preset third threshold is M times the baseline amplitude of the steady-state visual evoked potential signal of the first user, where M is a positive number. The baseline amplitude of the steady-state visual evoked potential signal of the first user is determined by collecting the baseline visual evoked potential signal of the first user during the preprocessing stage.

14. The eye illumination device according to claim 1, characterized in that, The signal acquisition module is also used to acquire auxiliary physiological signals of the first user; wherein, the auxiliary physiological signals include: electroretinography signals and / or visual cortical blood oxygenation signals; The control module is specifically used to determine the irradiation timing based on the visual evoked potential signal of the first user when the auxiliary physiological signal meets the preset conditions. The preset conditions include at least one of the following: the amplitude of the auxiliary physiological signal is within a preset amplitude range, the waveform of the auxiliary physiological signal matches a preset waveform template, and the auxiliary physiological signal indicates that the eye tissue is in an optimal state.

15. A computer-readable storage medium storing a computer program, characterized in that, When the computer program is executed by the processor, it implements the function of the control module in the eye illumination device according to any one of claims 1 to 14.

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