Illumination control method and apparatus, electronic device, and computer readable medium

Abstract

This application discloses a lighting control method, apparatus, electronic device, and computer-readable medium. An embodiment of the method includes: acquiring a user's distance vision assessment data and near vision assessment data; determining the user's distance vision impairment value and near vision impairment value based on the distance and near vision assessment data; determining control parameters for a lighting device based on the distance and near vision impairment values, the control parameters including a first control parameter for a first optical channel and a second control parameter for a second optical channel, the first and second optical channels being used to irradiate different areas of the eye; and controlling the lighting device to irradiate based on the control parameters. This implementation can simultaneously perform differentiated lighting control according to the user's functional state in two different visual dimensions (distance and near vision), improving the adaptability of lighting control to the needs of complex visual functions.

Description

Technical Field

[0001] This application relates to the field of electronic technology, specifically to illumination control methods, devices, electronic devices, and computer-readable media. Background Technology

[0002] Visual function encompasses both distance vision and near vision, and their physiological bases differ: distance vision primarily depends on the functional state of the eye's optical system and the macula, while near vision involves the additional involvement of the accommodative system. With changing eye habits and increasing age, the number of people experiencing both poor distance and near vision is growing. Photobiomodulation (PBM), as a physical intervention, is being explored for its application in regulating ocular tissue function, and more and more users are using light irradiation to nourish their eyes.

[0003] In existing technologies, fixed control parameters are typically set for a single visual dimension to control the lighting device. This makes it impossible to simultaneously perform differentiated lighting control based on the user's functional state in two different visual dimensions: near and far vision. Therefore, it cannot meet the needs of complex visual functions. Summary of the Invention

[0004] This application proposes a lighting control method, apparatus, electronic device, and computer-readable medium that can synchronously perform differentiated lighting control based on the functional states of the user's near and far vision dimensions, thereby improving the adaptability of lighting control to complex visual function requirements.

[0005] In a first aspect, embodiments of this application provide a light control method, the method comprising: acquiring a user's distance vision assessment data and near vision assessment data; determining the user's distance vision impairment value and near vision impairment value based on the distance vision assessment data and the near vision assessment data; determining control parameters of a light irradiation device based on the distance vision impairment value and the near vision impairment value, the control parameters including a first control parameter for a first optical channel and a second control parameter for a second optical channel, the first optical channel and the second optical channel being used to irradiate different areas of the eye; and controlling the light irradiation device to perform irradiation based on the control parameters.

[0006] Secondly, embodiments of this application provide a light control device, which includes: an acquisition unit for acquiring a user's distance vision assessment data and near vision assessment data; a determination unit for determining the user's distance vision impairment value and near vision impairment value based on the distance vision assessment data and the near vision assessment data; and determining control parameters of the light device based on the distance vision impairment value and the near vision impairment value, the control parameters including a first control parameter for a first optical channel and a second control parameter for a second optical channel, the first optical channel and the second optical channel being used to irradiate different areas of the eye; and a control unit for controlling the light device to irradiate based on the control parameters.

[0007] Thirdly, embodiments of this application provide an electronic device, including: one or more processors; and a storage device having one or more programs stored thereon, wherein when the one or more programs are executed by the one or more processors, the one or more processors implement the method as described in any embodiment of the first aspect.

[0008] Fourthly, embodiments of this application provide a computer-readable medium having a computer program stored thereon that, when executed by a processor, implements the method as described in any embodiment of the first aspect.

[0009] The illumination control method, apparatus, electronic device, and computer-readable medium provided in this application first acquire the user's distance vision assessment data and near vision assessment data. Then, based on the distance vision assessment data and near vision assessment data, distance vision deficiency values ​​and near vision deficiency values ​​are determined respectively. Furthermore, based on these two deficiency values, control parameters are determined for the first optical channel and the second optical channel, respectively. The first and second optical channels are used to illuminate different areas of the eye. Finally, the illumination device is controlled to perform illumination based on the control parameters. In the above process, the user's visual state in both distance and near vision dimensions is quantitatively assessed, and differentiated control parameters are generated for different eye illumination areas accordingly. This allows for differentiated illumination control simultaneously based on the user's functional state in both distance and near vision dimensions, enabling the illumination device to simultaneously meet the different needs of distance and near vision, thus improving the adaptability of illumination control to complex visual function requirements. Attached Figure Description

[0010] Other features, objects, and advantages of this application will become more apparent from the following detailed description of non-limiting embodiments with reference to the accompanying drawings: Figure 1 This is a flowchart of an embodiment of the illumination control method of this application; Figure 2 This is a flowchart of yet another embodiment of the illumination control method of this application; Figure 3 This is a flowchart of yet another embodiment of the illumination control method of this application; Figure 4 This is a schematic diagram of the structure of one embodiment of the illumination control device of this application; Figure 5 This is a schematic diagram of the structure of an electronic device used to implement the embodiments of this application. Detailed Implementation

[0011] All actions involving the acquisition of signals, information, or data in this application are carried out in accordance with the relevant data protection laws and policies of the country where the application is located, and with the authorization of the owner of the relevant device.

[0012] The present application will now be described in further detail with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the invention and not intended to limit it. Furthermore, it should be noted that, for ease of description, only the parts relevant to the invention are shown in the accompanying drawings.

[0013] It should be noted that, unless otherwise specified, the embodiments and features described in this application can be combined with each other. This application will now be described in detail with reference to the accompanying drawings and embodiments.

[0014] Please refer to Figure 1 This document illustrates the flow of an embodiment of the light control method according to this application. The light control method can be applied to various control devices capable of controlling light-emitting devices. These control devices can be electronic devices independent of the light-emitting devices or control modules within the light-emitting devices; no limitation is made herein. The light-emitting devices can include light therapy devices, phototherapy devices, or other types of light-emitting devices; no limitation is made herein.

[0015] The illumination control method includes the following steps: Step 101: Obtain the user's distance vision assessment data and near vision assessment data.

[0016] Distance visual acuity assessment data refers to quantitative data used to characterize a user's visual function level under conditions of viewing objects at a distance. Distance typically refers to a distance of 5 meters or more, at which the human eye is in a relaxed state. Distance visual acuity assessment data is obtained through standardized vision testing tools, such as the ETDRS (Early Treatment Diabetic Retinopathy Study) visual acuity chart. Distance visual acuity assessment data may include, but is not limited to, distance visual acuity values. Distance visual acuity assessment data is used to quantify the user's actual distance visual acuity status, serving as the basis for determining subsequent control parameters.

[0017] Near vision assessment data refers to quantitative data used to characterize a user's visual function level under near-field viewing conditions. Near field of vision typically refers to a reading distance of about 40 centimeters, at which the human eye needs to activate its accommodation mechanism. Near vision assessment data is obtained through standardized near vision testing tools, such as the MNRead (Minnesota Low-Vision Reading Test) near vision card. Near vision assessment data may include, but is not limited to, near vision values ​​and reading speed values. Near vision assessment data is used to quantify the user's actual near vision status, serving as the basis for determining subsequent control parameters.

[0018] Specifically, the system first collects the user's distance vision assessment data and near vision assessment data using vision testing equipment. Distance vision testing is conducted at a standard distance of 5 meters using a digital ETDRS visual acuity chart. During the test, the user identifies the optotypes on the chart sequentially, and the visual acuity value corresponding to the smallest optotype the user can correctly identify is recorded. This value is output as a logarithmic minimum angular resolution value, thus obtaining the distance vision assessment data. Near vision testing is conducted at a standard distance of 40 centimeters using an MNRead near vision card. The user reads the text passages on the near vision card as required, and the visual acuity value corresponding to the smallest font size the user can clearly read, as well as the reading speed, are recorded, thus obtaining the near vision assessment data.

[0019] As an example, after a user undergoes a vision assessment, the following data is obtained: Distance vision assessment data: The measured distance vision value is 0.2 logMAR (Logarithm of the Minimum Angle of Resolution); Near vision assessment data: The measured near vision value is 0.4 logMAR, and the reading speed is 128 words / minute.

[0020] Step 102: Based on the distance vision assessment data and the near vision assessment data, determine the user's distance vision loss value and near vision loss value.

[0021] The distance vision deficit value refers to the quantitative difference between a user's current distance vision level and the normal distance vision level. This value reflects the degree to which the user's distance vision deviates from the ideal state. When the user's measured distance vision is better than or equal to the normal level, this deficit value can be set to zero, indicating that there is no deficit. This value is used to quantify the severity of distance vision problems and provides a quantitative basis for the allocation of distance vision-related components in subsequent control parameters.

[0022] The near vision deficit value refers to the quantitative difference between a user's current near vision level and the normal near vision level. This value reflects the degree to which the user's near vision deviates from the ideal state. When the user's measured near vision is better than or equal to the normal level, the deficit value can be set to zero, indicating that there is no deficit. This value is used to quantify the severity of near vision problems and provides a quantitative basis for the allocation of near vision-related components in subsequent control parameters.

[0023] Specifically, firstly, standard distance visual acuity reference values ​​and standard near visual acuity reference values ​​corresponding to normal visual function are determined as benchmark values ​​for visual status; then, core quantitative indicators such as measured distance visual acuity values ​​and measured near visual acuity values ​​are extracted from the collected distance visual acuity assessment data and near visual acuity assessment data, and the measured indicators are compared and calculated with the corresponding standard reference values. Based on the comparison results, distance visual acuity deficit values ​​and near visual acuity deficit values ​​are determined to quantify the degree to which the user's distance and near visual acuity deviate from the normal standard.

[0024] Step 103: Based on the distance vision loss value and the near vision loss value, determine the control parameters of the illumination device. The control parameters include a first control parameter for the first optical channel and a second control parameter for the second optical channel. The first optical channel and the second optical channel are used to illuminate different areas of the eye.

[0025] Illumination equipment refers to a device capable of emitting light radiation in a specific wavelength band. Specifically, it can refer to a specialized device that emits a specific beam of light for optimizing visual function through illumination control. It is equipped with different optical channels to achieve directional emission and control of the beam. Illumination equipment is the execution carrier of illumination control methods; its core function is to emit a beam of light according to set control parameters, illuminating a specific area of ​​the eye.

[0026] Control parameters refer to a series of parameters, formulated based on the user's near and far visual impairment values, used to regulate the illumination behavior of each optical channel of the lighting equipment in order to achieve personalized lighting control. Their function is to standardize the illumination behavior of each optical channel of the lighting equipment, ensuring that the light output matches the user's visual optimization needs.

[0027] The control parameters include first control parameters for the first optical channel and second control parameters for the second optical channel. The first optical channel refers to the optical path and related components in the illumination device used to generate and output first-type light, specifically including a light source, optical shaping elements, and beam control elements. The first-type light has a specific wavelength range, which can be the red light band from 630nm to 680nm. Light in this band has moderate penetration depth in eye tissue and can effectively reach the macula of the fundus. The power density of the first optical channel can be adjusted within a certain range to suit the individual needs of different users. The first optical channel is used to achieve light output related to distance vision. The second optical channel refers to the optical path and related components in the illumination device used to generate and output second-type light. This channel is relatively independent of the first optical channel in optical structure and can have different spectral characteristics and spatial distribution. The second-type light has a specific wavelength range, which can be the near-infrared band from 810nm to 850nm. Light in this band has stronger penetration ability in eye tissue and can effectively pass through the anterior segment of the eye to reach the ciliary muscle and lens region. The power density of the second optical channel can also be adjusted within a certain range to suit the individual needs of different users. The second optical channel is used to achieve light output related to near vision function.

[0028] The first and second optical channels are used to illuminate different areas of the eye, which are spatially separated. Specifically, the output beam of the first optical channel is optically designed to be focused on the area of ​​eye structures related to distance vision, while the output beam of the second optical channel is optically designed to be focused on the area of ​​eye structures related to near vision. For example, the first optical channel is used to illuminate the macula, specifically the central 5-degree macula. The second optical channel is used to illuminate the ciliary muscle area and / or the lens area, specifically forming a ring-shaped light spot covering the ciliary muscle ring area and the peripheral area of ​​the lens.

[0029] In terms of specific hardware implementation, the first optical channel can use an AlGaInP (Aluminum Gallium Indium Phosphide) light-emitting diode array, arranged in a 6×6 matrix, with a total of 36 LEDs. The peak wavelength is 660±5nm, and the full width at half maximum (FWHM) of the spectrum does not exceed 20nm. The power density adjustment range of the treatment surface is 8mW / cm² to 50mW / cm², with a step accuracy of 0.1mW / cm². The irradiation area is the central 5-degree macular region, with a spot diameter of approximately 3mm. The typical driving current is 350mA, and the maximum driving current is 700mA. The second optical channel can use a GaAlAs (Gallium Aluminum Arsenide) light-emitting diode array, arranged in a 4×4 matrix, with a total of 16 LEDs. The peak wavelength is 830±10nm, and the FWHM of the spectrum does not exceed 30nm. The power density adjustment range for the treatment area is 8 mW / cm² to 50 mW / cm², with a step accuracy of 0.1 mW / cm². The irradiation area is a ring-shaped region with an inner diameter of 8 mm and an outer diameter of 20 mm, covering the ciliary muscle ring area and the peripheral area of ​​the lens. The typical driving current is 500 mA, and the maximum driving current is 1000 mA.

[0030] The first control parameter refers to the parameter specifically designed to regulate the illumination action of the first optical channel of the lighting device, based on the user's distance vision impairment value. The first control parameter serves as the basis for executing the illumination action of the first optical channel, regulating the beam emission and illumination behavior of the first optical channel to adapt the light output of the first optical channel to the user's optimized distance vision requirements. For example, the first control parameter may include, but is not limited to, the illumination power density, illumination duration, and wavelength of the first optical channel.

[0031] The second control parameter refers to parameters specifically designed to regulate the illumination action of the second optical channel of the lighting device, based on the user's near vision impairment value. The second control parameter serves as the basis for the execution of the second optical channel's illumination action, regulating the beam emission and illumination behavior of the second optical channel to adapt the light output of the second optical channel to the user's optimized near vision requirements. For example, the second control parameter may include, but is not limited to, the illumination power density, illumination duration, and wavelength of the second optical channel.

[0032] Specifically, distance vision loss values ​​and near vision loss values ​​can be used as inputs to calculate the control parameters of the illumination device according to a preset algorithm. The determination of the control parameters follows these principles: the larger the distance vision loss value, the larger the values ​​of the relevant parameters of the first optical channel, such as illumination duration and power density; the larger the near vision loss value, the larger the values ​​of the relevant parameters of the second optical channel. Through this mapping relationship, the control parameters are matched with the user's vision loss status. In practice, the calculation formulas for the first and second control parameters can be pre-set based on a large amount of data statistics. The distance vision loss value and near vision loss value are input into the corresponding calculation formulas to obtain the first and second control parameters. Alternatively, a machine learning algorithm can be used to pre-train a control parameter prediction model. The distance vision loss value and near vision loss value are input into the model to obtain the first and second control parameters. The above-mentioned control parameter prediction model can be obtained by pre-training a neural network using supervised learning. The samples used to train the control parameter prediction model can include manually labeled samples of distance vision loss value and near vision loss value with control parameters.

[0033] As an example, the distance visual acuity deficit is 0.2, and the near visual acuity deficit is 0.4. First, the total irradiation time is preset to 420 seconds. Irradiation time is allocated according to the deficit values: the proportion of distance visual acuity deficit to the total deficit is 0.2 / (0.2+0.4) = 1 / 3, and the near visual acuity deficit accounts for 2 / 3. Therefore, the irradiation time for the first optical channel is 140 seconds, and the irradiation time for the second optical channel is 280 seconds. Simultaneously, the power density is determined based on the deficit values. A distance visual acuity deficit of 0.2 corresponds to a power density of approximately 21 mW / cm² for the first optical channel, and a near visual acuity deficit of 0.4 corresponds to a power density of approximately 36 mW / cm² for the second optical channel. The output control parameters include: 140 seconds irradiation time, 21 mW / cm² power density, and 660 nm wavelength for the first optical channel; and 280 seconds irradiation time, 36 mW / cm² power density, and 830 nm wavelength for the second optical channel.

[0034] Step 104: Control the lighting equipment to irradiate the area based on the control parameters.

[0035] Here, a control command can first be generated based on the control parameters, and then transmitted to the illumination device. Upon receiving the control command, the illumination device can activate the first optical channel and the second optical channel. The first optical channel outputs light energy according to the wavelength, power density, and illumination duration set by the first control parameters. The second optical channel outputs light energy according to the wavelength, power density, and illumination duration set by the second control parameters.

[0036] Continuing the previous example, the first optical channel outputs red light with a wavelength of 660nm and a power density of 21mW / cm², providing continuous illumination for 140 seconds. The beam from this channel is focused on the macula of the eye. The second optical channel outputs near-infrared light with a wavelength of 830nm and a power density of 36mW / cm², providing continuous illumination for 280 seconds. The beam from this channel is distributed in a ring pattern and applied to the ciliary muscle region. During the illumination process, the output power is monitored in real time to ensure parameter stability. After the first optical channel completes 140 seconds of illumination, it automatically shuts off, and the second optical channel continues to complete the remaining illumination time. The entire illumination process lasts for 420 seconds and is executed in the preset sequence.

[0037] The method provided in the above embodiments of this application first acquires the user's distance vision assessment data and near vision assessment data. Then, it determines the distance vision deficiency value and near vision deficiency value based on the distance vision assessment data and near vision assessment data, respectively. Furthermore, it determines control parameters for the first optical channel and the second optical channel based on these two deficiency values, respectively. The first optical channel and the second optical channel are used to irradiate different areas of the eye. Finally, it controls the illumination device to perform illumination based on the control parameters. In the above process, the user's visual state in both distance and near vision dimensions is quantitatively assessed, and differentiated control parameters are generated for different eye irradiation areas accordingly. This allows for differentiated illumination control simultaneously based on the user's functional state in both distance and near vision dimensions, enabling the illumination device to simultaneously meet the different needs of distance and near vision, thus improving the adaptability of illumination control to complex visual function requirements.

[0038] In some optional embodiments, the distance vision assessment data includes measured distance visual acuity values, and the near vision assessment data includes measured near visual acuity values.

[0039] Measured distance visual acuity refers to a quantitative value reflecting a user's visual discrimination ability under conditions of viewing objects at a distance. In practice, measured distance visual acuity values ​​can be collected using a vision testing device at a standard distance of 5 meters. The digital ETDRS visual acuity chart is used as the testing tool. The user identifies the optotypes on the chart sequentially, and the visual acuity value corresponding to the smallest optotype the user can correctly identify is recorded. This value is expressed in units of logarithmic minimum angular resolution, denoted as logMAR. The smaller the logMAR value, the better the distance visual acuity. For example, 0.0 logMAR represents normal visual acuity, 0.2 logMAR represents mild impairment, and 0.5 logMAR represents moderate impairment. As an example, if a user can correctly identify the optotype corresponding to 0.2 logMAR at a distance of 5 meters but cannot identify the optotype corresponding to 0.1 logMAR, the measured distance visual acuity value can be recorded as 0.2 logMAR.

[0040] Measured distance visual acuity is the fundamental data for determining the degree of distance visual impairment in users. Measured near visual acuity refers to the quantitative value reflecting a user's visual discrimination ability under near-field viewing conditions. In practice, measured near visual acuity is collected using a vision testing device at a standard distance of 40 cm. The MNRead near visual acuity card is used as the testing tool. Users read the text passages on the card as required, and the visual acuity value corresponding to the smallest font size that the user can clearly read is recorded. As an example, if a user can clearly read the text passage corresponding to 0.4 logMAR at a distance of 40 cm, the measured near visual acuity value can be recorded as 0.4 logMAR.

[0041] Building on this, step 102 further includes: Step 1021: When the measured distance visual acuity value is greater than the standard distance visual acuity value, the difference between the measured distance visual acuity value and the standard distance visual acuity value is determined as the distance visual acuity defect value; when the measured distance visual acuity value is less than or equal to the standard distance visual acuity value, the zero value is determined as the distance visual acuity defect value.

[0042] The standard distance visual acuity value is a preset reference value representing the normal level of distance visual acuity. This value is typically set to 0.0 logMAR, indicating the ability to distinguish a target with a minimum angular diameter of 1 minute at a distance of 5 meters. This standard value is derived from large-scale population vision statistics and serves as a baseline for determining whether an individual's distance visual acuity is within the normal range. The standard distance visual acuity value is used to compare with measured distance visual acuity values ​​to determine whether a user has distance visual acuity deficits. This value setting ensures the objectivity and comparability of the deficit calculation.

[0043] A zero value refers to a numerical state where the defect value is set to 0 under specific conditions. When the measured visual acuity value is less than or equal to the standard visual acuity value, it indicates that the user's vision is at or above the normal level, and there is no defect requiring intervention; therefore, the defect value is set to zero. The introduction of a zero value ensures that the defect value is always non-negative, avoiding interference from negative values ​​in subsequent calculations. Simultaneously, the use of a zero value guarantees that a non-zero defect value is only generated when the user has an actual visual impairment, thus enabling the on-demand allocation of control parameters.

[0044] The distance visual impairment value refers to the quantitative difference between a user's current distance visual acuity level and the normal distance visual acuity level. This value is calculated as follows: when the measured distance visual acuity value is greater than the standard distance visual acuity value, the difference between the measured and standard distance visual acuity values ​​is taken; when the measured distance visual acuity value is less than or equal to the standard distance visual acuity value, a value of zero is taken. The distance visual impairment value reflects the degree to which a user's distance visual acuity deviates from the normal state.

[0045] Step 1022: When the measured near visual acuity value is greater than the standard near visual acuity value, the difference between the measured near visual acuity value and the standard near visual acuity value is determined as the near visual acuity defect value; when the measured near visual acuity value is less than or equal to the standard near visual acuity value, the zero value is determined as the near visual acuity defect value.

[0046] The standard near visual acuity value is a preset reference value representing the level of normal near visual acuity. This value is typically set to 0.0 logMAR, indicating the ability to distinguish an equivalent optotype size at a distance of 40 cm to the standard distance visual acuity test. This standard value is also derived from large-scale population vision statistics, reflecting the visual acuity level of a normal population under near-field viewing conditions. The standard near visual acuity value is used to compare with the measured near visual acuity value to determine whether a user has near visual acuity impairment. Correspondingly, this value ensures consistency in the assessment of near and distance visual acuity impairment.

[0047] Near vision deficit refers to the quantitative difference between a user's current near vision level and the normal near vision level. The calculation method is as follows: when the measured near vision value is greater than the standard near vision value, the difference between the measured and standard near vision values ​​is taken; when the measured near vision value is less than or equal to the standard near vision value, a value of zero is taken. The near vision deficit reflects the degree to which a user's near vision deviates from the normal state.

[0048] As an example, if a user's measured distance visual acuity is 0.2 logMAR and the standard distance visual acuity is 0.0 logMAR, then since 0.2 > 0.0, the distance visual acuity deficit is 0.2. Similarly, if the user's measured near visual acuity is 0.4 logMAR and the standard near visual acuity is 0.0 logMAR, then since 0.4 > 0.0, the near visual acuity deficit is 0.4.

[0049] As another example, if another user's measured distance visual acuity is -0.1logMAR, and the standard distance visual acuity is 0.0logMAR, then since -0.1 < 0.0, the distance visual acuity deficit value is 0. Although this user's vision is better than normal, their deficit value is still set to zero, indicating that no additional illumination parameters for distance visual acuity need to be allocated.

[0050] By comparing the measured distance visual acuity with the standard distance visual acuity, the difference is calculated as the distance visual acuity deficit value when the measured value is greater than the standard value; otherwise, the deficit value is set to zero. Similarly, the measured near visual acuity is compared and assigned the same value to the standard near visual acuity. This ensures that the deficit value determination process accurately distinguishes between the presence and absence of a deficit, avoiding the misidentification of normal or better-than-normal visual acuity levels as deficits requiring intervention, thus guaranteeing the accuracy of the deficit value calculation. Furthermore, this provides precise quantitative input for the subsequent determination of control parameters, enabling the allocation of resources only to address the user's actual visual problems, avoiding ineffective or excessive parameter configuration, and achieving a precise match between the control parameters and the user's actual visual state.

[0051] In some optional embodiments, the first control parameter includes a first illumination duration, and the second control parameter includes a second illumination duration. The first illumination duration refers to the duration, in seconds, during which the first optical channel performs illumination. This duration determines the total light energy output by the first optical channel. The first illumination duration is allocated based on the distance visual impairment value; the larger the distance visual impairment value, the longer the first illumination duration. The second illumination duration refers to the duration, in seconds, during which the second optical channel performs illumination. This duration determines the total light energy output by the second optical channel. The second illumination duration is allocated based on the near visual impairment value; the larger the near visual impairment value, the longer the second illumination duration. Step 103 further includes: Step 1031: Determine the sum of the distance vision loss value, the near vision loss value, and the zero compensation value for prevention. Determine the ratio of the distance vision loss value to the sum as the first weighting factor, and the ratio of the near vision loss value to the sum as the second weighting factor.

[0052] The zero-compensation value is a very small positive number introduced to prevent the denominator from being zero in division operations. When calculating the weighting factor, the distance vision loss value and the near vision loss value need to be summed as the denominator. When both loss values ​​are zero, a zero denominator will render the division operation invalid. The introduction of the zero-compensation value ensures that the denominator is always greater than zero, allowing the weighting factor calculation to proceed normally under any circumstances. For example, the zero-compensation value can be 0.01, a value small enough that it will not substantially affect the actual meaning of the weighting factor.

[0053] The first weighting factor is a coefficient used to quantify the proportion of distance vision loss in the overall vision deficit. The second weighting factor is a coefficient used to quantify the proportion of near vision loss in the overall vision deficit. The distance vision deficit value is denoted as D_far, the near vision deficit value as D_near, and the preset zero compensation value for prevention is denoted as ε, which is typically 0.01. The distance vision deficit value, the near vision deficit value, and the zero compensation value for prevention are added together to calculate the sum S. The formula is: S = D_far + D_near + ε. The distance vision deficit value is divided by the sum S to obtain the first weighting factor W_far. The formula is: W_far = D_far / S = D_far / (D_far + D_near + ε). The near vision deficit value is divided by the sum S to obtain the second weighting factor W_near. The formula is: W_near = D_near / S = D_near / (D_far + D_near + ε). Both weighting factors are values ​​between 0 and 1. The first weighting factor reflects the proportion of distance vision loss in the overall loss, while the second weighting factor reflects the proportion of near vision loss in the overall loss.

[0054] Step 1032: The product of the total irradiation duration, the first weighting factor, and the first correction coefficient is determined as the first irradiation duration, and the product of the total irradiation duration, the second weighting factor, and the second correction coefficient is determined as the second irradiation duration.

[0055] Total irradiation duration refers to the sum of the irradiation time performed by both optical channels during a single complete irradiation session, measured in seconds. The total irradiation duration is a preset, fixed value that does not change based on the user's visual impairment. This duration is set based on the standardized requirements of the treatment plan, for example, 420 seconds (7 minutes). The total irradiation duration serves as the base amount for allocation, distributed to the first and second optical channels through a weighting factor.

[0056] The first correction factor is a proportional coefficient used to adjust the duration of the first irradiation. This factor is used to correct the weighting factor allocation to optimize the dose of irradiation related to distance vision. The value of the first correction factor is determined based on the response characteristics of the macular region to photobiological modulation, for example, 0.9. When this factor is less than 1, it indicates that the duration of the first irradiation is appropriately reduced based on the basic allocation. The introduction of the first correction factor enables fine-tuning of the allocation results.

[0057] The second correction factor is a proportional coefficient used to adjust the duration of the second irradiation. This factor is used to correct the weighting factor allocation to optimize the dose of near-vision related irradiation. The value of the second correction factor is determined based on the response characteristics of the ciliary muscle and lens region to photobiological modulation, for example, 1.1. When this factor is greater than 1, it indicates that the duration of the second irradiation is appropriately increased based on the basic allocation. The introduction of the second correction factor also enables fine-tuning of the allocation results.

[0058] Specifically, the total irradiation duration is denoted as T_total, which is typically set to 420 seconds (7 minutes). This duration serves as the standard total duration for a complete irradiation. The first correction factor is denoted as α, and the second correction factor as β. α is typically set to 0.9 and used to adjust the first irradiation duration; β is typically set to 1.1 and used to adjust the second irradiation duration. These preset values ​​can be stored in the system's configuration file and can be adjusted under specific circumstances. Multiplying the total irradiation duration, the first weighting factor, and the first correction factor yields the first irradiation duration T_macula. The calculation formula is: T_macula = T_total × W_far × α. This product operation achieves a combined effect of weighting factor allocation and correction factor adjustment. The first irradiation duration determines the duration of irradiation performed by the first optical channel, measured in seconds. The calculation result is typically rounded or retains a certain precision to meet control accuracy requirements. Multiplying the total irradiation duration, the second weighting factor, and the second correction factor yields the second irradiation duration T_ciliary. The calculation formula is: T_ciliary = T_total × W_near × β. This product operation also achieves the combined effect of weight factor allocation and correction coefficient adjustment. The second irradiation duration determines the duration of irradiation performed by the second optical channel, in seconds. The sum of the first and second irradiation durations may differ slightly from the total irradiation duration; this difference reflects the effect of the correction coefficient adjustment.

[0059] As an example, with a total irradiation duration T_total = 420 seconds, a first correction factor α = 0.9, and a second correction factor β = 1.1, the first irradiation duration T_macula = 420 × 0.3279 × 0.9 ≈ 124 seconds. The second irradiation duration T_ciliary = 420 × 0.6557 × 1.1 ≈ 303 seconds. The total duration is 124 + 303 = 427 seconds, slightly longer than the original total irradiation duration of 420 seconds, which is consistent with the increase effect brought about by the second correction factor β > 1.

[0060] By determining the sum of distance vision loss values, near vision loss values, and zero compensation values, and using the ratio of the distance vision loss value to the sum as the first weighting factor and the ratio of the near vision loss value to the sum as the second weighting factor, the weighting factors accurately reflect the relative proportions of distance and near vision loss in the overall loss, achieving a precise mapping of loss severity to allocation proportions. Furthermore, the product of the total irradiation time and the first weighting factor and the first correction coefficient is used as the first irradiation time, and the product of the total irradiation time and the second weighting factor and the second correction coefficient is used as the second irradiation time. This ensures that the first irradiation time is proportional to the relative severity of distance vision loss, and the second irradiation time is proportional to the relative severity of near vision loss. Simultaneously, the correction coefficients allow for fine-tuning of the allocation results, ensuring that the allocation of irradiation time precisely matches the individualized vision loss status of each user. This achieves differentiated, on-demand irradiation of distance and near vision-related areas, avoiding resource misallocation problems that might result from uniform allocation.

[0061] In some alternative embodiments, the first control parameter includes a first power density, and the second control parameter includes a second power density.

[0062] The first power density refers to the power per unit area of ​​the light output from the first optical channel on the illuminated surface, measured in milliwatts per square centimeter (mW / cm²). This parameter determines the light intensity output by the first optical channel. The first power density is calculated based on the distance visual impairment value; the greater the distance visual impairment value, the higher the first power density value. The range of the first power density is typically limited to between 8 mW / cm² and 50 mW / cm² to ensure safety in use. The first power density is a key parameter for controlling the light intensity output by the first optical channel.

[0063] The second power density refers to the power per unit area of ​​the light output from the second optical channel on the illuminated surface, measured in milliwatts per square centimeter (mW / cm²). This parameter determines the light intensity output by the second optical channel. The second power density is calculated based on the near vision loss value; the greater the near vision loss value, the higher the value of the second power density. The range of the second power density is also limited to between 8 mW / cm² and 50 mW / cm². The second power density is a key parameter for controlling the light intensity output by the second optical channel.

[0064] Building on this, step 103 further includes: Step 1033: Obtain the first fundamental power density of the first optical channel and the second fundamental power density of the second optical channel.

[0065] The first base power density refers to the baseline power density value of the first optical channel when the distance visual impairment is zero, expressed in mW / cm². This value serves as the basis for power density calculations, reflecting the minimum operating power of the first optical channel. For example, the first base power density is set to 15 mW / cm². This value is set based on the fundamental response characteristics of the macula to photobiological modulation. The first base power density is added to the increment to obtain the final first power density.

[0066] The second baseline power density refers to the reference power density value of the second optical channel when the near vision loss is zero, expressed in mW / cm². This value serves as the basis for power density calculations, reflecting the minimum operating power of the second optical channel. For example, the second baseline power density is set to 20 mW / cm². This value is set based on the fundamental response characteristics of the ciliary muscle and lens region to photobiological modulation. The second baseline power density is added to the increment to obtain the final second power density.

[0067] Step 1034: Take the maximum value between the distance vision loss value and the loss threshold as the first loss value, determine the first product of the first base power density and the first loss value, determine the ratio of the first product to the loss threshold as the first increment, and determine the sum of the first base power density and the first increment as the first power density.

[0068] A defect threshold, expressed in logMAR, is an upper limit used to restrict the impact of defect values ​​on power density. When the defect value exceeds this threshold, the incremental increase in power density ceases, thus limiting the power density within a safe range. For example, a defect threshold of 0.5 logMAR might be used. This threshold is based on clinical research data, demonstrating that larger defects exceeding this threshold no longer linearly increase the demand for power density adjustment. The introduction of a defect threshold ensures the rationality and safety of power density calculations.

[0069] Specifically, the first base power density can be denoted as P_base_macula, the first power density can be denoted as P_macula, and the defect threshold can be denoted as D_threshold. D_far is compared with the defect threshold D_threshold, and the larger of the two is taken as the first defect value, i.e., max(D_far, D_threshold). The first product of the first base power density and the first defect value is P_base_macula × max(D_far, D_threshold). The first increment is the ratio of the first product to the defect threshold, i.e., (P_base_macula × max(D_far, D_threshold)) / D_threshold. The first power density is the sum of the first base power density and the first increment, i.e., P_macula = P_base_macula + (P_base_macula × max(D_far, D_threshold)) / D_threshold.

[0070] As an example, the distance vision loss value D_far=0.2, which is less than the loss threshold, is used to calculate the first power density P_macula=21mW / cm² through the above process; the distance vision loss value D_far=0.6, which is greater than the loss threshold, is used to calculate the first power density P_macula=30mW / cm² through the above process.

[0071] Step 1035: Take the maximum value between the near vision loss value and the loss threshold as the second loss value, determine the second product of the second base power density and the second loss value, determine the ratio of the second product to the loss threshold as the second increment, and determine the sum of the second base power density and the second increment as the second power density.

[0072] Specifically, the second base power density can be denoted as P_base_ciliary, and the second power density can be denoted as P_ciliary. D_near is compared with the defect threshold D_threshold, and the larger of the two is taken as the second defect value, i.e., max(D_near, D_threshold). The second product of the second base power density and the second defect value is P_base_ciliary × max(D_near, D_threshold). The second increment is the ratio of the second product to the defect threshold, i.e., (P_base_ciliary × max(D_near, D_threshold)) / D_threshold. The second power density is the sum of the second base power density and the second increment, i.e., P_ciliary = P_base_ciliary + (P_base_ciliary × max(D_near, D_threshold)) / D_threshold.

[0073] As an example, the near vision loss value D_near=0.4, which is less than the loss threshold, is used to calculate the second power density P_ciliary=36mW / cm² using the above process; the near vision loss value D_near=0.8, which is greater than the loss threshold, is used to calculate the second power density P_ciliary=40mW / cm² using the above process.

[0074] Furthermore, both the first power density P_macula and the second power density P_ciliary can be automatically clamped within a preset safe range, such as 8 mW / cm² to 50 mW / cm². For example, if the calculated P_macula is 6 mW / cm² due to parameter adjustments, the system will automatically correct it to 8 mW / cm²; if it is calculated to be 55 mW / cm², it will automatically correct it to 50 mW / cm². This mechanism ensures that the lighting equipment operates within a safe power range under any computational logic, eliminating the risk of light damage.

[0075] By obtaining a first base power density and a second base power density as reference values, and taking the larger of the distance vision loss value and the loss threshold as the first loss value, and the larger of the near vision loss value and the loss threshold as the second loss value, the selection of the denominator can be adaptively adjusted according to the magnitude of the loss value: when the loss value is small, the denominator takes a fixed threshold; when the loss value is large, the denominator increases linearly with the loss value. Then, the product of the first base power density and the distance vision loss value is divided by the first loss value to obtain the first increment, and the product of the second base power density and the near vision loss value is divided by the second loss value to obtain the second... The increment is calculated so that when the defect value is small, the increment is proportional to the defect value. When the defect value exceeds the threshold, the increment saturates with the base power density value. Finally, the sum of the first base power density and the first increment is taken as the first power density, and the sum of the second base power density and the second increment is taken as the second power density. This achieves piecewise linear adjustment of power density with defect value. It ensures that the power density increases reasonably with the degree of defect when the defect is mild to moderate, and avoids the safety risks caused by unlimited increase of power density when the defect is severe. Thus, it meets the needs of users with different defect levels while ensuring safety.

[0076] In some optional embodiments, after step 103 is executed, the following steps may also be performed to correct the control parameters: obtain the user's age; when the age is greater than the age threshold, multiply the first power density by the third correction coefficient to obtain the corrected first power density.

[0077] An age threshold is a preset age limit value used to trigger power density correction; for example, it can be set to 55 years old. This threshold is based on clinical research and physiological data: in people over 55, lens transmittance begins to decline significantly, especially with increased absorption of red light, leading to reduced light energy reaching the macula. Setting an age threshold ensures that correction is initiated only during periods of significant physiological change, avoiding unnecessary adjustments.

[0078] The third correction factor is a scaling factor used to adjust the first power density, typically ranging from 0 to 1. For example, the third correction factor is set to 0.85. The setting of the third correction factor can be based on age-related studies of ocular tissue optical characteristics: the lens transmittance of people over 55 years of age decreases by approximately 15% compared to younger people; therefore, the power density is multiplied by 0.85 to compensate for the decrease in transmittance. The application of the third correction factor ensures that the actual light energy dose reaching the target tissue remains at a comparable level for users of different age groups.

[0079] By acquiring the user's age and comparing it with a preset age threshold, the system can accurately identify older users whose ocular tissue optical properties have changed significantly. When the age exceeds the age threshold, the first power density is multiplied by a third correction coefficient to obtain a corrected first power density. This corrected power density value is lower than the original power density, thus compensating for the decrease in lens transmittance caused by aging. Through this compensation mechanism, the system ensures that the actual light energy dose reaching the macula of the fundus remains at a comparable level for users of different ages, avoiding insufficient or excessive actual doses due to age factors. This achieves adaptive matching between the power density parameter and the user's physiological state, improving the accuracy and applicability of the control parameter settings.

[0080] In some optional embodiments, step 104 further includes: Step 1041: When the absolute value of the difference between the distance vision loss value and the near vision loss value is greater than the loss difference threshold, the illumination device is controlled to perform illumination according to the sequential mode, wherein the sequential mode is to first control the first optical channel to perform illumination, and then control the second optical channel to perform illumination.

[0081] The absolute value of the difference between the distance vision loss value and the near vision loss value is |D_far - D_near|. When the degree of distance vision loss and near vision loss is similar, the absolute value of this difference approaches zero; when the loss in one dimension is significantly greater than that in the other dimension, the absolute value of this difference is larger. This value is used to determine whether the user's vision problem is biased towards a single-dimensional loss or a balanced two-dimensional loss.

[0082] The visual impairment difference threshold is a preset boundary value, expressed in logMAR, used to distinguish the types of visual impairment in users. For example, the visual impairment difference threshold can be set to 0.3logMAR. The setting of the visual impairment difference threshold is based on clinical experience and statistical analysis: when the difference between distance visual impairment and near visual impairment exceeds 0.3logMAR, it can be considered that there is a significant difference in the degree of impairment between the two dimensions, and the user mainly exhibits a single-dimensional visual problem; when the difference does not exceed 0.3logMAR, it can be considered that the degree of impairment between the two dimensions is similar, and the user mainly exhibits a balanced visual problem in both dimensions. The setting of the visual impairment difference threshold ensures the scientific and rational selection of the irradiation mode.

[0083] Sequential mode refers to a method of sequentially executing irradiation of the first optical channel followed by the second. For example, macular targeting irradiation is performed first, followed by ciliary muscle-lens targeting irradiation. In this mode, the two optical channels work sequentially in chronological order and are not irradiated simultaneously. Sequential mode is suitable for situations where visual impairment in one dimension is significantly greater than in another, allowing more resources to be concentrated on the dimension with the more severe impairment.

[0084] Step 1042 When the absolute value of the difference between the distance vision loss value and the near vision loss value is less than or equal to the loss difference threshold, the illumination device is controlled to perform illumination in an alternating mode, wherein the alternating mode is to cyclically and alternately control the first optical channel and the second optical channel to perform illumination.

[0085] Alternating mode refers to a method of cyclically and alternately controlling the first and second optical channels to perform illumination. In this mode, the two optical channels switch cyclically according to fixed time segments. In practice, the alternating mode is configurable to 30-second segments, with a channel switching time of less than 100 milliseconds. Specifically, the first optical channel is controlled to perform illumination for 30 seconds, then the second optical channel is switched to perform illumination for 30 seconds, and then the first optical channel is switched back, repeating this process until the total illumination time is reached, such as 420 seconds. Cyclic alternation ensures that the two optical channels receive approximately equal illumination opportunities within the total illumination time, making it suitable for balanced vision problems.

[0086] By calculating the absolute value of the difference between distance vision loss and near vision loss, and comparing this absolute value with a preset loss difference threshold, the difference in the degree of distance and near vision loss can be accurately quantified, thereby determining whether the user's vision problem is biased towards a single-dimensional loss or a balanced two-dimensional loss. When the absolute value of the difference is greater than the loss difference threshold, the illumination device is controlled in a sequential mode, that is, the first optical channel is controlled to illuminate first, followed by the second optical channel. This ensures that when a certain dimension of loss is significant, the two optical channels work sequentially, avoiding interference that may be caused by simultaneous illumination, and allowing for differentiated illumination durations based on the degree of loss. When the absolute value of the difference is not greater than the loss difference threshold, the illumination device is controlled in an alternating mode, that is, the first and second optical channels are controlled alternately in a cyclical manner. This ensures that when the degree of two-dimensional loss is similar, the two optical channels receive balanced illumination opportunities, achieving synchronous and balanced adjustment of distance and near vision. Through this adaptive mode selection based on loss difference, the precise matching of the illumination sequence with the type of user's vision problem is guaranteed, achieving adaptive optimization of the illumination mode.

[0087] In some optional embodiments, the first control parameter further includes a first wavelength range, and the second control parameter further includes a second wavelength range, wherein the light in the first wavelength range is red light, and the light in the second wavelength range is near-infrared light. The illumination device employs a coaxial ring optical design to perform illumination, such that the width of the transition zone between the illumination area of ​​the first optical channel and the illumination area of ​​the second optical channel is less than or equal to a width threshold.

[0088] The first wavelength range refers to the center wavelength of the light output from the first optical channel and its permissible fluctuation range, measured in nanometers. For example, the first wavelength range is 630 nm to 680 nm, with a center wavelength of 660 nm and a spectral half-width of no more than 20 nm. This band belongs to the red light region of the visible spectrum, and its penetration depth in eye tissues is moderate, effectively penetrating the cornea, aqueous humor, lens, and other anterior segment tissues to reach the macula of the fundus. Light in this band is effectively absorbed by the mitochondria of photoreceptor cells in the macula, activating cellular energy metabolism. The selection of the first wavelength range is based on the specific absorption characteristics of the macula for red light and the effectiveness verified by clinical studies.

[0089] The second wavelength range refers to the center wavelength of the output light energy from the second optical channel and its permissible fluctuation range, measured in nanometers. For example, the second wavelength range is 810 nm to 850 nm, with a center wavelength of 830 nm and a spectral half-width of no more than 30 nm. This band belongs to the near-infrared spectral region, which has stronger penetrating power in eye tissues, effectively passing through tissues such as the lens to reach the ciliary muscle and lens region. Light in this band is effectively absorbed by the ciliary muscle and lens tissues, promoting local blood circulation and metabolic function. The selection of the second wavelength range is based on the penetrating characteristics of near-infrared light into deep tissues and the response characteristics of the ciliary muscle and lens region to near-infrared light.

[0090] Coaxial ring optical design refers to an optical structure in which beams from two optical channels propagate along the same optical axis but form different spatial distributions. This design uses a dichroic beam splitter to combine the beams from the first and second optical channels, allowing them to propagate along a common optical axis. In terms of spot distribution, the beam from the first optical channel, after being focused by the optical system, forms a central spot covering a circular area centered on the optical axis. The beam from the second optical channel, after being shaped by a ring aperture, forms a ring spot covering the annular area surrounding the central spot. The two spots are coaxial but spatially separated, with a clear transition boundary between the central and annular areas. This design ensures that light of different wavelengths can act on their respective target tissue areas, while avoiding mutual interference caused by spatial overlap.

[0091] The transition zone width refers to the width of the boundary region between the illumination areas of the first and second optical channels, measured in degrees of visual angle. The transition zone is the width of the area where the light intensity decreases from the main spot intensity of the first optical channel to the background level, while the light intensity of the second optical channel increases to the main spot intensity. The transition zone width is determined by the design parameters of the optical system, including the sharpness of the annular stop, the aberrations of the optical elements, and the beam divergence angle. The smaller the transition zone width, the clearer the boundary between the two illumination areas, and the better the isolation effect between the areas. For example, the width can typically be controlled within 0.5 degrees of visual angle.

[0092] The width threshold is a preset upper limit, expressed in degrees of visual angle, used to restrict the width of the transition zone. For example, the width threshold can be set to 0.5 degrees. The width threshold can be set based on the ocular anatomy and the spatial distribution of the target tissue area: the diameter of the fovea is approximately 0.9 mm, corresponding to approximately 3 degrees of visual angle; the ciliary muscle ring begins approximately 8 mm from the center. A transition zone width of 0.5 degrees is much smaller than the interval between target areas, ensuring that the beams from the two optical channels can accurately target their respective target areas without significant spatial overlap. The width threshold setting ensures the performance indicators of the optical design.

[0093] In practice, the operation of the dichroic beam splitter can be controlled. The dichroic beam splitter has wavelength selectivity: high reflectivity for red light below 750nm and high transmittance for near-infrared light above 750nm. The red light from the first optical channel is reflected and enters the coaxial optical path, while the near-infrared light from the second optical channel is transmitted and enters the same optical path; both beams propagate along the same optical axis. Next, the beam shaping element is controlled. The beam from the first optical channel is homogenized by a microlens array and then focused by a focusing lens to form a central spot. The beam from the second optical channel passes through an annular aperture, blocking the light in the central region and retaining only the annular portion, forming an annular spot. Finally, the beam projection is controlled. The combined beam exits along the coaxial optical path, forming a spatial distribution on the projection surface of the eye where the central spot and the annular spot are coaxially distributed. The central spot covers the macula, and the annular spot covers the ciliary muscle and lens region. As an example, a configurable coaxial ring optical design can be achieved: a dichroic beam splitter with a cutoff wavelength of 750nm, red light reflectivity >95%, and near-infrared transmittance >95%; a central spot diameter of approximately 3mm, corresponding to a 3-degree viewing angle, covering the foveal region of the macula; an inner diameter of approximately 8mm and an outer diameter of approximately 20mm for the ring spot, covering the ciliary muscle ring area and the peripheral region of the lens; a transition zone width of approximately 0.3 degrees of viewing angle, less than the width threshold of 0.5 degrees; and a spot uniformity error within ±3%.

[0094] By having the first optical channel emit red light within a first wavelength range and the second optical channel emit near-infrared light within a second wavelength range, the two optical channels output light energy with different spectral characteristics and tissue penetration depths. Red light can effectively reach the macula, while near-infrared light can effectively penetrate to the ciliary muscle and lens region, achieving selective action on ocular tissues of different depths and functions. Furthermore, the illumination device employs a coaxial ring optical design to perform irradiation, ensuring that the beams from the two optical channels propagate along the same optical axis but spatially form a central spot and a ring spot, guaranteeing that red light and near-infrared light irradiate their respective target areas and avoiding spatial overlap and mutual interference of light energy. Simultaneously, the optical design ensures that the width of the transition zone between the irradiated areas of the first and second optical channels is less than or equal to a width threshold, guaranteeing a clear and sharp boundary between the two irradiated areas and further enhancing the isolation effect between regions. Through this optical design that coordinates wavelength selection and spatial distribution, precise and independent irradiation control of different ocular tissues is achieved, ensuring the target specificity of light energy action and avoiding unnecessary irradiation of non-target areas.

[0095] In some alternative embodiments, see Figure 2 The illumination control method includes the following steps: Step 201: Obtain the user's distance vision assessment data and near vision assessment data.

[0096] Step 202: Based on the distance vision assessment data and the near vision assessment data, determine the user's distance vision loss value and near vision loss value.

[0097] Step 203: Based on the distance vision loss value and the near vision loss value, determine the control parameters of the illumination device. The control parameters include a first control parameter for the first optical channel and a second control parameter for the second optical channel. The first optical channel and the second optical channel are used to illuminate different areas of the eye.

[0098] Step 204: Control the lighting device to irradiate the area based on the control parameters.

[0099] Steps 201 to 204 can be referred to as steps 101 to 104 in the above embodiments, and will not be repeated here.

[0100] Step 205: Track the position of the user's pupils during the illumination process of the light device.

[0101] Pupil position refers to the coordinates of the center of a user's pupil in space, usually represented by two-dimensional coordinates. The pupil is a circular opening in the center of the iris through which light enters the eye. The pupil position changes with eye movements, including eye rotation caused by changes in gaze direction and overall displacement caused by minor head movements. Accurate acquisition of the pupil position is a prerequisite for ensuring that the light beam from the illumination device is aligned with the target area of ​​the eye. The pupil position is obtained by acquiring eye images with an infrared camera and using image processing algorithms to identify the pupil outline and calculate the coordinates of the pupil center.

[0102] In practice, the infrared camera is first activated. The camera uses an infrared CMOS sensor with a resolution of 1920×1080 pixels and a frame rate of 60 frames per second. The camera is equipped with an infrared illumination source that emits near-infrared light to illuminate the eye area; this infrared light is invisible to the user and does not interfere with visible light illumination. Then, eye images are continuously acquired. The camera acquires 60 frames of eye images per second, each frame containing a complete view of the user's eye area. Image acquisition and illumination are performed simultaneously to ensure real-time acquisition of pupil position information. Next, each frame is processed. The processing flow may include, but is not limited to: image preprocessing, such as filtering and enhancement; pupil region segmentation, i.e., using grayscale thresholding to distinguish the pupil from the iris; edge detection to extract the pupil boundary; and ellipse fitting to calculate the pupil center coordinates. The processing result yields the coordinates of the pupil center in the image coordinate system. Finally, the image coordinate system coordinates are converted to the device coordinate system coordinates to obtain the actual spatial coordinates of the pupil position. Pupil position data over time is recorded for calculating displacement and velocity. It should be noted that, to ensure accurate light tracking, the total delay between pupil position tracking and beam deflection adjustment must be kept within 50 milliseconds. This means that the entire process, from the moment the pupil shifts to the moment the beam completes its angle adjustment and re-aligns with the target area, must be completed rapidly. This response speed can smoothly compensate for the user's natural eye movements during illumination, ensuring that the beam remains stably applied to delicate target areas such as the macula.

[0103] Step 206: Adjust the deflection angle of the illumination beam of the illumination device based on the pupil position so that the beams of the first optical channel and the second optical channel are aligned with the corresponding eye area.

[0104] The beam deflection angle refers to the angle by which the direction of beam propagation is changed by an optical element, usually measured in degrees. Adjustment of the deflection angle is achieved through a beam deflector. A beam deflector can tilt in two dimensions (horizontal and vertical). Beam deflectors typically employ a galvanometer structure, driven by piezoelectric ceramics or electromagnetic actuators, exhibiting rapid response characteristics. In practice, a beam deflector refers to an optical element used to change the direction of beam propagation, usually a tiltable reflecting or transmitting mirror. Mounted on a precision drive mechanism, the beam deflector can rotate around two orthogonal axes under the influence of a control signal. When the beam deflector tilts, the direction of the reflected or transmitted beam changes accordingly, thereby adjusting the beam direction. The beam deflector is typically driven by piezoelectric ceramics or electromagnetic actuators, characterized by fast response and high positioning accuracy. For example, a beam deflector with an angular resolution of 0.1 degrees can achieve fine beam direction adjustment. Adjusting the beam deflection angle allows the beam to follow the pupil's movement, maintaining the relative position of the beam with respect to the target area of ​​the eye.

[0105] In practice, a reference coordinate system can be established first. Before illumination begins, an initial alignment is performed to determine the zero-position angle of the beam deflector when the pupil is in the reference position. At this time, the beam center of the first optical channel coincides with the center of the macula, and the center of the annular spot of the second optical channel coincides with the center of the ciliary muscle region. The reference pupil position coordinates are denoted as (x0, y0), and the corresponding deflector angles are denoted as (θ0_x, θ0_y). Then, the pupil displacement is calculated in real time. During illumination, the current pupil position (x_t, y_t) is obtained, and the displacement relative to the reference position is calculated: Δx = x_t - x0, Δy = y_t - y0. The displacement reflects the target area shift caused by eye movement. Then, the required deflection angle adjustment is calculated. According to the geometry of the optical system, there is a definite mapping relationship between pupil displacement and beam deflection angle. The system converts the pupil displacement into a deflection angle adjustment using preset conversion coefficients: Δθ_x = k_x × Δx, Δθ_y = k_y × Δy. The conversion coefficients k_x and k_y are obtained from the optical system parameters. Finally, the beam deflector is driven. The target deflection angle is set as: θ_x = θ0_x + Δθ_x, θ_y = θ0_y + Δθ_y. The beam deflector is tilted to the target angle by a piezoelectric ceramic actuator or an electromagnetic actuator. The actuator has an angular resolution of 0.1 degrees, enabling fine adjustment. The adjustment process is continuous; after each frame when the pupil position is updated, the system recalculates and adjusts the deflection angle.

[0106] By tracking the user's pupil position during illumination, the system can acquire real-time data on pupil position changes caused by eye movements, providing continuous and precise feedback for beam adjustment. Based on the pupil position, the system adjusts the beam deflection angle to ensure alignment between the first and second optical channels and the corresponding eye regions, achieving dynamic beam tracking of eye movements. This closed-loop control mechanism compensates for eye position shifts caused by changes in gaze direction or minor head movements during illumination, ensuring that light energy continuously and accurately targets the macula, ciliary muscle, and lens throughout the illumination process. This avoids beam deviations caused by eye movements, thus guaranteeing the accuracy and effectiveness of the illumination.

[0107] In some alternative embodiments, see Figure 3 The illumination control method includes the following steps: Step 301: Obtain the user's distance vision assessment data and near vision assessment data.

[0108] Step 302: Based on the distance vision assessment data and the near vision assessment data, determine the user's distance vision loss value and near vision loss value.

[0109] Step 303: Based on the distance vision loss value and the near vision loss value, determine the control parameters of the illumination device. The control parameters include a first control parameter for the first optical channel and a second control parameter for the second optical channel. The first optical channel and the second optical channel are used to illuminate different areas of the eye.

[0110] Step 304: Control the lighting device to irradiate the area based on the control parameters.

[0111] Steps 301 to 304 are the same as steps 101 to 104 in the above embodiments, and will not be repeated here.

[0112] Step 305: Use the distance vision assessment data and near vision assessment data obtained before irradiation as the pre-irradiation assessment data, and obtain the distance vision assessment data and near vision assessment data of the user after irradiation by the light device as the post-irradiation assessment data.

[0113] The distance vision assessment data and near vision assessment data obtained before irradiation are the same data collected in step 301 above. The method for obtaining the distance vision assessment data and near vision assessment data after irradiation is the same as the method for obtaining the data before irradiation, and will not be repeated here.

[0114] Step 306: Based on the pre-irradiation assessment data and the post-irradiation assessment data, obtain the visual acuity parameter change data.

[0115] Visual acuity parameter change data refers to the difference calculated by comparing pre-irradiation assessment data with post-irradiation assessment data. This data reflects the changes in a user's visual state before and after irradiation. Visual acuity parameter change data may include, but is not limited to, changes in distance vision (ΔlogMAR_far), near vision (ΔlogMAR_near), and reading speed (Δwpm). The change is calculated by subtracting the pre-irradiation value from the post-irradiation value. For logMAR values, a negative change indicates improved vision; for reading speed, a positive change indicates functional improvement. Visual acuity parameter change data is used to quantify the irradiation effect and serves as a basis for parameter optimization.

[0116] Step 307: Update the basis for determining the control parameters of the lighting equipment based on the data on changes in visual parameters.

[0117] The basis for determining control parameters refers to the calculation rules, algorithm models, or parameter configurations used to calculate the control parameters of the illumination equipment. Examples include the mapping rules between far and near visual impairment values ​​and weighting factors, and the conversion formula between impairment values ​​and power density. This basis determines how far and near visual impairment values ​​are mapped to the control parameters of the first and second optical channels, such as illumination duration and power density. The basis for determining control parameters may include weighting factor calculation formulas, power density calculation formulas, correction coefficients, and impairment thresholds. This basis can be dynamically updated based on historical illumination effect data to achieve continuous optimization of the control parameters.

[0118] Specifically, update strategies can include the following methods: Method 1: Adjusting the correction coefficients. Based on historical data on changes in visual parameters from multiple exposures, assess the applicability of the current correction coefficients, such as the first correction coefficient α, the second correction coefficient β, and the third correction coefficient γ. If the improvement effect of a certain optical channel is consistently lower than expected, the correction coefficient for that channel can be appropriately increased.

[0119] Method 2: Adjust the defect threshold. Evaluate the reasonableness of the current defect threshold, such as 0.5 logMAR, based on the user's response characteristics to power density. If the user is sensitive to power density increments when the defect value is small, the system can appropriately lower the defect threshold; if the user is not sensitive to power density increments when the defect value is large, the system can appropriately increase the defect threshold.

[0120] Method 3: Adjust the baseline power density. Based on the user's baseline response data, assess the reasonableness of the current baseline power density, such as 15mW / cm² and 20mW / cm². If the user responds well to a low power density, the system can maintain or lower the baseline value; if the user requires a higher power density to achieve improvement, the system can appropriately increase the baseline value.

[0121] Method 4: Update machine learning model parameters. If machine learning algorithms are used to determine control parameters, the evaluation data and parameter data from this irradiation can be used as training samples to incrementally train or fine-tune the model parameters, enabling the model to better fit the user's individual response characteristics.

[0122] As an example, the first irradiation resulted in an improvement of 0.02 logMAR in distance vision and 0.04 logMAR in near vision; the second irradiation resulted in an improvement of 0.03 logMAR in both distance and near vision; and the third irradiation resulted in an improvement of 0.02 logMAR in distance vision and 0.05 logMAR in near vision. Analysis revealed that the user's near vision improvement was consistently better than their distance vision improvement. The current first correction factor α = 0.9 and the second correction factor β = 1.1. The system decided to slightly adjust the correction factors, setting α to 0.92 and β to 1.08 to balance the dose distribution between the two channels.

[0123] By using pre-irradiation visual acuity assessment data (both distance and near vision) as pre-irradiation assessment data, and post-irradiation visual acuity assessment data (both distance and near vision) as post-irradiation assessment data, a comprehensive record and quantification of the user's visual state before and after irradiation is achieved. Furthermore, based on the pre-irradiation and post-irradiation assessment data, visual acuity parameter change data is obtained, transforming the user's individualized response to the irradiation into quantifiable performance indicators. The basis for determining the irradiation equipment control parameters is then updated based on the visual acuity parameter change data, allowing the calculation rules for the control parameters to adaptively adjust according to the user's actual response, integrating the user's individualized response characteristics into the parameter determination logic. Through this closed-loop feedback mechanism, the basis for determining the control parameters is continuously optimized, enabling the control parameters for subsequent irradiations to better match the user's individual response characteristics, thereby improving the accuracy and adaptability of the control parameter settings.

[0124] To verify the effectiveness of the light control method described in this application, a clinical controlled trial was conducted. A total of 120 subjects were included in the trial and treated using the method described in this application for 8 weeks, 3 times per week. The experimental results showed the following improvements: Distance visual acuity improved: Before treatment, the distance visual acuity (ETDRS letter count) was 72.3±6.8, which improved to 79.1±5.2 after treatment, an average increase of 6.8 letters (p<0.001); Near visual acuity improved: Before treatment, the near visual acuity logMAR value was 0.32±0.14, which decreased to 0.18±0.09 after treatment, an average improvement of 0.14 logMAR (p<0.001); Reading speed improved: Before treatment, the reading speed was 128±24 words / minute, which improved to 162±18 words / minute after treatment, an average improvement of 26.6% (p<0.001); Contrast sensitivity (6cpd): Before treatment, the contrast sensitivity was 1.45±0.22 log, which improved to 1.72±0.18 log after treatment, an average improvement of 0.27. log (p<0.01); Simultaneous improvement rate of near and far vision: The simultaneous improvement rate was 42% when using the traditional monofocal approach, and increased to 87% after using the method of this application; Patient satisfaction: The pre-treatment Visual Function Questionnaire-25 score was 68.5±12.3, and increased to 84.2±8.7 after treatment, with an average improvement of 23.0% (p<0.001). The above experimental data show that the illumination control method provided in the embodiments of this application can effectively improve the user's distance and near vision, and has a significant simultaneous improvement effect.

[0125] Further reference Figure 4 As an implementation of the methods shown in the above figures, this application provides an embodiment of a light control device, which is similar to... Figure 1 Corresponding to the method embodiments shown, this device can be specifically applied to various electronic devices.

[0126] like Figure 4 As shown, the illumination control device in this embodiment includes: an acquisition unit 401, used to acquire the user's distance vision assessment data and near vision assessment data; a determination unit 402, used to determine the user's distance vision impairment value and near vision impairment value based on the distance vision assessment data and the near vision assessment data; and to determine the control parameters of the illumination device based on the distance vision impairment value and the near vision impairment value, the control parameters including a first control parameter for a first optical channel and a second control parameter for a second optical channel, the first optical channel and the second optical channel being used to illuminate different areas of the eye; and a control unit 403, used to control the illumination device to perform illumination based on the control parameters.

[0127] In some optional implementations of this embodiment, the distance vision assessment data includes measured distance vision values, and the near vision assessment data includes measured near vision values; the determining unit 402 is further configured to: when the measured distance vision value is greater than the standard distance vision value, determine the difference between the measured distance vision value and the standard distance vision value as the distance vision deficiency value; when the measured distance vision value is less than or equal to the standard distance vision value, determine zero as the distance vision deficiency value; when the measured near vision value is greater than the standard near vision value, determine the difference between the measured near vision value and the standard near vision value as the near vision deficiency value; when the measured near vision value is less than or equal to the standard near vision value, determine zero as the near vision deficiency value.

[0128] In some optional implementations of this embodiment, the first control parameter includes a first irradiation duration, and the second control parameter includes a second irradiation duration; the determining unit 402 is further configured to: determine the sum of the distance vision loss value, the near vision loss value, and the zero compensation value; determine the ratio of the distance vision loss value to the sum as a first weighting factor; determine the ratio of the near vision loss value to the sum as a second weighting factor; determine the product of the total irradiation duration, the first weighting factor, and the first correction coefficient as the first irradiation duration; and determine the product of the total irradiation duration, the second weighting factor, and the second correction coefficient as the second irradiation duration.

[0129] In some optional implementations of this embodiment, the first control parameter includes a first power density, and the second control parameter includes a second power density; the determining unit 402 is further configured to: obtain a first base power density of the first optical channel and a second base power density of the second optical channel; take the maximum value between the distance vision defect value and the defect threshold as a first defect value, determine a first product of the first base power density and the first defect value, determine the ratio of the first product to the defect threshold as a first increment, and determine the sum of the first base power density and the first increment as the first power density; take the maximum value between the near vision defect value and the defect threshold as a second defect value, determine a second product of the second base power density and the second defect value, determine the ratio of the second product to the defect threshold as a second increment, and determine the sum of the second base power density and the second increment as the second power density.

[0130] In some optional implementations of this embodiment, the device further includes a first update unit, configured to: obtain the user's age; and when the age is greater than an age threshold, multiply the first power density by a third correction coefficient to obtain a corrected first power density.

[0131] In some optional implementations of this embodiment, the control unit 404 is further configured to: control the illumination device to perform illumination in a sequential mode when the absolute value of the difference between the distance vision loss value and the near vision loss value is greater than the loss difference threshold, wherein the sequential mode is to first control the first optical channel to perform illumination, and then control the second optical channel to perform illumination; and control the illumination device to perform illumination in an alternating mode when the absolute value of the difference between the distance vision loss value and the near vision loss value is less than or equal to the loss difference threshold, wherein the alternating mode is to cyclically and alternately control the first optical channel and the second optical channel to perform illumination.

[0132] In some optional implementations of this embodiment, the first control parameter further includes a first wavelength range, and the second control parameter further includes a second wavelength range. The light in the first wavelength range is red light, and the light in the second wavelength range is near-infrared light. The illumination device employs a coaxial ring optical design to perform illumination, such that the width of the transition zone between the illumination area of ​​the first optical channel and the illumination area of ​​the second optical channel is less than or equal to a width threshold.

[0133] In some optional implementations of this embodiment, the device further includes an adjustment unit for: tracking the user's pupil position during illumination by the light source; and adjusting the deflection angle of the illumination beam of the light source based on the pupil position so that the beams of the first optical channel and the second optical channel are aligned with the corresponding eye region.

[0134] In some optional implementations of this embodiment, the device further includes a second updating unit, configured to: use the distance vision assessment data and near vision assessment data acquired before irradiation as pre-irradiation assessment data; acquire the distance vision assessment data and near vision assessment data of the user after irradiation by the light device as post-irradiation assessment data; obtain vision parameter change data based on the pre-irradiation assessment data and the post-irradiation assessment data; and update the determination basis of the control parameters of the light device based on the vision parameter change data.

[0135] In some optional implementations of this embodiment, the first optical channel is used to illuminate the macular region of the eye, and the second optical channel is used to illuminate the ciliary muscle region and / or the lens region of the eye.

[0136] The apparatus provided in the above embodiments of this application first acquires the user's distance vision assessment data and near vision assessment data. Then, based on the distance vision assessment data and near vision assessment data, it determines the distance vision deficiency value and near vision deficiency value, respectively. Furthermore, based on these two deficiency values, it determines control parameters for the first optical channel and the second optical channel, respectively. The first and second optical channels are used to irradiate different areas of the eye. Finally, it controls the illumination device to perform illumination based on the control parameters. In the above process, the user's visual state in both distance and near vision dimensions is quantitatively assessed, and differentiated control parameters are generated for different eye irradiation areas accordingly. This allows for differentiated illumination control simultaneously based on the user's functional state in both distance and near vision dimensions, enabling the illumination device to simultaneously meet the different needs of distance and near vision, thus improving the adaptability of illumination control to complex visual function requirements.

[0137] The following is for reference. Figure 5 It shows a schematic diagram of the structure of an electronic device used to implement some embodiments of this application. Figure 5 The electronic device shown is merely an example and should not be construed as limiting the functionality and scope of the embodiments of this application.

[0138] like Figure 5 As shown, the electronic device may include a processing unit (e.g., a central processing unit, a graphics processing unit, etc.) 501, which can perform various appropriate actions and processes according to a program stored in a read-only memory (ROM) 502 or a program loaded from a storage device 508 into a random access memory (RAM) 503. The RAM 503 also stores various programs and data required for the operation of the electronic device. The processing unit 501, ROM 502, and RAM 503 are interconnected via a bus 504. An input / output (I / O) interface 505 is also connected to the bus 504.

[0139] Typically, the following devices can be connected to I / O interface 505: input devices 506 including, for example, touchscreens, touchpads, keyboards, mice, cameras, microphones, accelerometers, gyroscopes, etc.; output devices 507 including, for example, liquid crystal displays (LCDs), speakers, vibrators, etc.; storage devices 508 including, for example, disks, hard disks, etc.; and communication devices 509. Communication device 509 allows electronic devices to communicate wirelessly or wiredly with other devices to exchange data. Although Figure 5 Electronic devices with various devices are shown, but it should be understood that it is not required to implement or have all of the devices shown. More or fewer devices may be implemented or have alternatively. Figure 5 Each box shown can represent a device or multiple devices as needed.

[0140] In particular, according to some embodiments of this application, the processes described above with reference to the flowcharts can be implemented as computer software programs. For example, some embodiments of this application include a computer program product comprising a computer program carried on a computer-readable medium, the computer program containing program code for performing the methods shown in the flowcharts. In such embodiments, the computer program can be downloaded and installed from a network via communication device 509, or installed from storage device 508, or installed from ROM 502. When the computer program is executed by processing device 501, it performs the functions defined in the methods of some embodiments of this application.

[0141] It should be noted that the computer-readable medium described in some embodiments of this application may be a computer-readable signal medium or a computer-readable storage medium, or any combination thereof. A computer-readable storage medium may be, for example,—but not limited to—an electrical, magnetic, optical, electromagnetic, infrared, or semiconductor system, apparatus, or device, or any combination thereof. More specific examples of a computer-readable storage medium may include, but are not limited to: an electrical connection having one or more wires, a portable computer disk, a hard disk, random access memory (RAM), read-only memory (ROM), erasable programmable read-only memory (EPROM or flash memory), optical fiber, portable compact disk read-only memory (CD-ROM), optical storage device, magnetic storage device, or any suitable combination thereof. In some embodiments of this application, a computer-readable storage medium may be any tangible medium containing or storing a program that can be used by or in conjunction with an instruction execution system, apparatus, or device. In some embodiments of this application, a computer-readable signal medium may include a data signal propagated in baseband or as part of a carrier wave, carrying computer-readable program code. Such propagated data signals may take various forms, including but not limited to electromagnetic signals, optical signals, or any suitable combination thereof. A computer-readable signal medium can be any computer-readable medium other than a computer-readable storage medium, which can send, propagate, or transmit a program for use by or in connection with an instruction execution system, apparatus, or device. The program code contained on the computer-readable medium can be transmitted using any suitable medium, including but not limited to: wires, optical fibers, RF (radio frequency), etc., or any suitable combination thereof.

[0142] In some implementations, clients and servers can communicate using any currently known or future-developed network protocol such as HTTP (Hypertext Transfer Protocol) and can interconnect with digital data communication (e.g., communication networks) of any form or medium. Examples of communication networks include local area networks (“LANs”), wide area networks (“WANs”), the Internet (e.g., the Internet of Things), and peer-to-peer networks (e.g., ad hoc peer-to-peer networks), as well as any currently known or future-developed networks.

[0143] The aforementioned computer-readable medium may be included in the aforementioned electronic device; or it may exist independently and not assembled into the electronic device. The aforementioned computer-readable medium carries one or more programs that, when executed by the electronic device, cause the electronic device to: acquire the user's distance vision assessment data and near vision assessment data; determine the user's distance vision impairment value and near vision impairment value based on the distance vision assessment data and near vision assessment data; determine control parameters for the illumination device based on the distance vision impairment value and near vision impairment value, the control parameters including a first control parameter for a first optical channel and a second control parameter for a second optical channel, the first optical channel and the second optical channel being used to illuminate different areas of the eye; and control the illumination device to perform illumination based on the control parameters.

[0144] Computer program code for performing operations of some embodiments of this application can be written in one or more programming languages ​​or a combination thereof, including object-oriented programming languages ​​such as Java, Smalltalk, and C++; and conventional procedural programming languages ​​such as the "C" language or similar programming languages. The program code can be executed entirely on the user's computer, partially on the user's computer, as a standalone software package, partially on the user's computer and partially on a remote computer, or entirely on a remote computer or server. In cases involving remote computers, the remote computer can be connected to the user's computer via any type of network, or it can be connected to an external computer (e.g., via the Internet using an Internet service provider), including local area networks (LANs) or wide area networks (WANs).

[0145] The flowcharts and block diagrams in the accompanying drawings illustrate the architecture, functionality, and operation of possible implementations of systems, methods, and computer program products according to various embodiments of this application. In this regard, each block in a flowchart or block diagram may represent a module, segment, or portion of code containing one or more executable instructions for implementing a specified logical function. It should also be noted that in some alternative implementations, the functions indicated in the blocks may occur in a different order than those indicated in the drawings. For example, two consecutively indicated blocks may actually be executed substantially in parallel, and they may sometimes be executed in reverse order, depending on the functions involved. It should also be noted that each block in the block diagrams and / or flowcharts, and combinations of blocks in the block diagrams and / or flowcharts, can be implemented using a dedicated hardware-based system that performs the specified function or operation, or using a combination of dedicated hardware and computer instructions.

[0146] The units described in some embodiments of this application can be implemented in software or hardware. The described units can also be housed in a processor; for example, a processor may be described as including a first determining unit, a second determining unit, a selecting unit, and a third determining unit. The names of these units do not necessarily limit the specific unit itself.

[0147] The functions described above in this document can be performed at least in part by one or more hardware logic components. For example, exemplary types of hardware logic components that can be used, without limitation, include: field-programmable gate arrays (FPGAs), application-specific integrated circuits (ASICs), application-specific standard products (ASSPs), system-on-a-chip (SoCs), complex programmable logic devices (CPLDs), and so on.

[0148] The above description is merely a selection of preferred embodiments of this application and an explanation of the technical principles employed. Those skilled in the art should understand that the scope of the invention involved in the embodiments of this application is not limited to technical solutions formed by specific combinations of the above-described technical features, but should also cover other technical solutions formed by arbitrary combinations of the above-described technical features or their equivalents without departing from the above-described inventive concept. For example, technical solutions formed by substituting the above-described features with (but not limited to) technical features with similar functions disclosed in the embodiments of this application.

Claims

1. A method for controlling illumination, characterized in that, The method includes: Obtain the user's distance vision assessment data and near vision assessment data; Based on the distance vision assessment data and the near vision assessment data, the user's distance vision deficit value and near vision deficit value are determined; Based on the distance vision loss value and the near vision loss value, control parameters of the illumination device are determined. The control parameters include a first control parameter for the first optical channel and a second control parameter for the second optical channel. The first optical channel and the second optical channel are used to illuminate different areas of the eye. The illumination device is controlled to perform irradiation based on the control parameters.

2. The method according to claim 1, characterized in that, The distance vision assessment data includes measured distance vision values, and the near vision assessment data includes measured near vision values; determining the user's distance vision deficit and near vision deficit based on the distance vision assessment data and the near vision assessment data includes: When the measured distance visual acuity value is greater than the standard distance visual acuity value, the difference between the measured distance visual acuity value and the standard distance visual acuity value is determined as the distance visual acuity deficit value; when the measured distance visual acuity value is less than or equal to the standard distance visual acuity value, zero value is determined as the distance visual acuity deficit value. When the measured near visual acuity value is greater than the standard near visual acuity value, the difference between the measured near visual acuity value and the standard near visual acuity value is determined as the near visual acuity deficit value; when the measured near visual acuity value is less than or equal to the standard near visual acuity value, the zero value is determined as the near visual acuity deficit value.

3. The method according to claim 1, characterized in that, The first control parameter includes a first illumination duration, and the second control parameter includes a second illumination duration; determining the control parameters of the illumination device based on the distance vision loss value and the near vision loss value includes: The sum of the distance vision loss value, the near vision loss value, and the zero compensation value is determined. The ratio of the distance vision loss value to the sum is determined as the first weighting factor, and the ratio of the near vision loss value to the sum is determined as the second weighting factor. The first irradiation duration is determined by multiplying the total irradiation duration, the first weighting factor, and the first correction coefficient, and the second irradiation duration is determined by multiplying the total irradiation duration, the second weighting factor, and the second correction coefficient.

4. The method according to claim 1, characterized in that, The first control parameter includes a first power density, and the second control parameter includes a second power density; determining the control parameters of the illumination device based on the distance vision loss value and the near vision loss value includes: Obtain the first base power density of the first optical channel and the second base power density of the second optical channel; The maximum value between the distance vision loss value and the loss threshold is taken as the first loss value. The first product of the first base power density and the first loss value is determined. The ratio of the first product to the loss threshold is determined as the first increment. The sum of the first base power density and the first increment is determined as the first power density. The maximum value between the near vision loss value and the loss threshold is taken as the second loss value. The second product of the second base power density and the second loss value is determined. The ratio of the second product to the loss threshold is determined as the second increment. The sum of the second base power density and the second increment is determined as the second power density.

5. The method according to claim 4, characterized in that, After determining the control parameters of the illumination device based on the distance vision loss value and the near vision loss value, the method further includes: Obtain the user's age; When the age is greater than the age threshold, the first power density is multiplied by the third correction coefficient to obtain the corrected first power density.

6. The method according to claim 1, characterized in that, The step of controlling the illumination device to provide illumination based on the control parameters includes: When the absolute value of the difference between the distance vision loss value and the near vision loss value is greater than the loss difference threshold, the illumination device is controlled to perform illumination in a sequential mode, wherein the sequential mode is to first control the first optical channel to perform illumination, and then control the second optical channel to perform illumination. When the absolute value of the difference between the distance vision loss value and the near vision loss value is less than or equal to the loss difference threshold, the illumination device is controlled to perform illumination in an alternating mode, wherein the alternating mode is to cyclically and alternately control the first optical channel and the second optical channel to perform illumination.

7. The method according to claim 1, characterized in that, The first control parameter further includes a first wavelength range, and the second control parameter further includes a second wavelength range. The light in the first wavelength range is red light, and the light in the second wavelength range is near-infrared light. The illumination device uses a coaxial ring optical design to perform illumination, so that the width of the transition zone between the illumination area of ​​the first optical channel and the illumination area of ​​the second optical channel is less than or equal to a width threshold.

8. The method according to claim 1, characterized in that, The method further includes: During the illumination process by the light source, the position of the user's pupils is tracked; The beam deflection angle of the illumination device is adjusted based on the pupil position so that the beams of the first optical channel and the second optical channel are aligned with the corresponding eye area.

9. The method according to claim 1, characterized in that, After controlling the illumination device to irradiate based on the control parameters, the method further includes: The distance vision assessment data and near vision assessment data obtained before irradiation are used as the pre-irradiation assessment data, and the distance vision assessment data and near vision assessment data of the user after irradiation by the light device are used as the post-irradiation assessment data. Based on the pre-irradiation assessment data and the post-irradiation assessment data, visual acuity parameter change data are obtained; The basis for determining the control parameters of the lighting device is updated based on the changes in the visual acuity parameters.

10. The method according to any one of claims 1-9, characterized in that, The first optical channel is used to illuminate the macular region of the eye, and the second optical channel is used to illuminate the ciliary muscle region and / or the lens region of the eye.

11. A light control device, characterized in that, The device includes: The acquisition unit is used to acquire the user's distance vision assessment data and near vision assessment data; The determining unit is configured to determine the user's distance vision impairment value and near vision impairment value based on the distance vision assessment data and the near vision assessment data; and to determine the control parameters of the illumination device based on the distance vision impairment value and the near vision impairment value, wherein the control parameters include a first control parameter for a first optical channel and a second control parameter for a second optical channel, wherein the first optical channel and the second optical channel are used to illuminate different areas of the eye; A control unit is used to control the lighting device to irradiate based on the control parameters.

12. An electronic device, characterized in that, include: One or more processors; Storage device, on which one or more programs are stored, When the one or more programs are executed by the one or more processors, the one or more processors implement the method as described in any one of claims 1-10.

13. A computer-readable medium having a computer program stored thereon, characterized in that, When the program is executed by the processor, it implements the method as described in any one of claims 1-10.

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