A method of visualizing control of optical power density on the retina and safety

Abstract

The application provides a method for visualizing control of light power density on retina and safety, which comprises: irradiating reference light on a simulation eye, and collecting optical reference data of a cornea region of the simulation eye and a retina region of the simulation eye, wherein the reference light is red light; irradiating a to-be-tested light on the simulation eye, and collecting optical test data of the cornea region of the simulation eye and the retina region of the simulation eye; determining a correlation data set of the retina region of the simulation eye under different diopters based on a patch refraction method; and adjusting an exit device of the to-be-tested light according to a type of the exit device, the optical reference data, the optical test data and the correlation data set. The application solves the problem that there is no method for measuring and controlling the retina light power density and the spot size in the RLRL red light treatment technology in the prior art.

Description

Technical Field

[0001] This invention relates to the field of red light testing and control technology, and in particular to a method for visually controlling the light power density on the retina and ensuring safety. Background Technology

[0002] With the global myopia rate continuing to rise, especially among teenagers, the search for safe, effective, and easy-to-adhere-based myopia intervention methods has become an urgent need in the medical and research fields. Against this backdrop, repetitive low-intensity red light therapy (RLRL), commonly known as a phototherapy device, has rapidly gained popularity and widespread attention as a new and highly effective myopia intervention method due to its unique mechanism of action and convenient usage.

[0003] The core principle of this device is to irradiate the fundus with a low-intensity red laser of a specific wavelength (such as 650nm) (currently, the mainstream on the market is a semiconductor laser, i.e., Laser Diode, LD). It is easy to use; simply irradiate for 3 minutes each morning and evening to effectively inhibit the abnormal increase in lens curvature and excessive elongation of the axial length, thereby slowing down or even reversing the progression of myopia. This advantage gives it enormous application potential in the field of myopia control. RLRL devices on the market are mainly divided into two categories based on the type of light source: laser-based phototherapy devices and non-laser-based phototherapy devices.

[0004] However, in practical application, a series of problems have gradually emerged. First, there are issues with user comfort and compliance. Although the manufacturer claims to use low-intensity red light, testing revealed that the light power density at the corneal location reached 2mW / cm². This intensity means that most people find the red light too strong and unbearable during their first irradiation. From a medical perspective, this directly manifests as poor product comfort, leading to poor patient compliance. Many patients abandon treatment due to intolerance, severely impacting the promotion and effectiveness of the therapy. Second, there are safety concerns. Although some existing studies have affirmed the effectiveness of RLRL therapy, the long-term safety of red laser intervention still lacks sufficient evidence. Furthermore, a very small number of suspected retinal light damage cases have indeed occurred in clinical applications. Although these cases ultimately resulted in full recovery, they still cast a shadow over the safety of this therapy.

[0005] The above analysis clearly shows that the core issues concerning safety and effectiveness in the field of phototherapy devices currently lie in how to accurately characterize the light power density and spot size on the retina. However, neither domestic nor international methods currently provide effective methods for detecting and controlling the light power density and spot size on the retina, and there is also a lack of convincing natural reference standards for defining safe dosages. Summary of the Invention

[0006] Based on this, the purpose of this invention is to provide a method for visually controlling the light power density and safety on the retina, aiming to solve the problem in the prior art of lacking a method for measuring and controlling the light power density and spot size of the retina in RLRL red light therapy.

[0007] A method for visually controlling the light power density on the retina and ensuring safety according to an embodiment of the present invention, the method comprising:

[0008] A reference light is shone onto a simulated eye, and optical reference data of the corneal region and the retinal region of the simulated eye are collected. The reference light is red sunlight.

[0009] The light to be tested is shone onto a simulated eye, and optical test data of the corneal region and the retinal region of the simulated eye are collected.

[0010] The associated dataset of the retinal regions of the simulated eye under different refractive powers was determined based on the interpolation method.

[0011] The emitting device is adjusted according to the type of the emitting device of the light to be tested, the optical reference data, the optical test data, and the associated dataset.

[0012] In addition, the method for visually controlling the light power density on the retina and ensuring safety according to the above embodiments of the present invention may also have the following additional technical features:

[0013] Furthermore, under preset conditions, a reference light is shone onto a simulated eye, and optical reference data of the corneal region and the retinal region of the simulated eye are collected, wherein the reference light is red sunlight. The steps include:

[0014] Under preset conditions and within a preset time period, illumination data of sunlight illuminating the corneal and retinal regions of multiple simulated eyes from sunrise to the target time point were collected on different dates.

[0015] The optical reference data is determined by filtering and fusing all the illumination data, and the preset conditions include at least a fixed location and a fixed angle.

[0016] Furthermore, the step of filtering and fusing all the illumination data to determine the optical reference data includes:

[0017] Obtain the time point at which the operator's naked-eye observation of sunrise corresponds to each of the simulated eyes;

[0018] The illumination data is filtered according to the extreme time nodes to determine the target illumination data;

[0019] The target illumination data is statistically processed to determine the optical reference data.

[0020] Furthermore, the step of adjusting the emitting device according to the type of the emitting device of the light under test, the optical reference data, the optical test data, and the associated dataset includes:

[0021] When the emitting device of the light to be tested is an LD type, the optical test data is adjusted according to the associated dataset to determine the differences in corneal position power density, retinal spot area and retinal power density parameters between the adjusted optical test data and the optical reference data under different refractive powers.

[0022] Adjust the drive current of the emission device so that the values ​​of the corneal power density and the retinal power density are lower than the reference values ​​in the corresponding optical reference data;

[0023] Adjust the lens of the emission device so that the area of ​​the retinal spot is higher than the reference value in the corresponding optical reference data, in order to determine the optical data of the correction device;

[0024] The single-use time of the emission device is determined based on the optical data of the correction device and the dose reference value in the optical reference data, so that the actual dose value generated in a single use is consistent with the dose reference value or adjusted in combination with historical clinical data.

[0025] Furthermore, the step of adjusting the emitting device according to the type of the emitting device of the light under test, the optical reference data, the optical test data, and the associated dataset includes:

[0026] A single-sided frosted glass and a collimating lens are sequentially arranged outside the outlet of the emission device so that the emitted light from the emission device is focused on the single-sided frosted glass to form a small light spot, and the small light spot is then collimated by the collimating lens to form parallel light.

[0027] The emission device is adjusted based on the optical test data of the parallel light on the simulated eye, the optical reference data, the type of emission device, and the associated dataset.

[0028] Furthermore, the step of adjusting the emitting device according to the type of the emitting device of the light under test, the optical reference data, the optical test data, and the associated dataset includes:

[0029] When the emitting device of the light to be tested is an LED type and the light to be tested is a collimated parallel light, the optical test data is adjusted according to the associated dataset to determine the differences in corneal position power density, retinal spot area and retinal power density parameters between the adjusted optical test data and the optical reference data under different refractive powers.

[0030] The size and model of the LED chip, the average operating current, and the distance between the collimating lens and the LED chip or the focal length of the device are adjusted to make the power density at the corneal position and the power density of the retina lower than the reference value in the corresponding optical reference data, and the area of ​​the retinal spot higher than the reference value in the corresponding optical reference data, so as to determine the optical data of the correction device.

[0031] The single-use time of the emission device is determined based on the optical data of the correction device and the dose reference value in the optical reference data, so that the actual dose value generated in a single use is consistent with the dose reference value or adjusted in combination with historical clinical data.

[0032] Furthermore, the simulated eye includes a main body and a single-sided frosted glass disposed on one side of the main body, wherein the non-transparent side of the single-sided frosted glass is the retina of the simulated eye.

[0033] Another object of the present invention is a system for visually controlling the light power density on the retina and ensuring safety, the system comprising:

[0034] The reference data determination module is used to illuminate the simulated eye with reference light and collect optical reference data of the corneal region and the retinal region of the simulated eye, wherein the reference light is red sunlight;

[0035] The test data determination module is used to illuminate the simulated eye with the light to be tested and to collect optical test data of the corneal region and the retinal region of the simulated eye.

[0036] The associated data determination module is used to determine the associated dataset of the retinal region of the simulated eye under different refractive powers based on the interpolation method.

[0037] The determination and adjustment module is used to adjust the emitting device according to the type of the emitting device of the light to be tested, the optical reference data, the optical test data, and the associated dataset.

[0038] Another objective of this invention is to provide a storage medium storing a computer program that, when executed by a processor, implements the steps of the above-described method for visually controlling the light power density on the retina and ensuring safety.

[0039] Another object of the present invention is to provide an electronic device, including a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor executes the program to implement the steps of the above-described method for visually controlling the light power density on the retina and ensuring safety.

[0040] This invention introduces a simulated eye equipped with a retina. By illuminating the simulated eye with red sunlight as a reference light, optical reference parameters on the cornea and retina are obtained under a natural reference frame. The light to be tested is then tested through the simulated eye to determine the corresponding optical test data. This allows for accurate determination of the optical data on the retina, enabling precise identification and judgment of the light to be tested. Furthermore, by introducing a natural parameter system—based on sunlight that people are constantly exposed to in daily life—as a safety assessment standard, using data on the gradual change in intensity during sunrise as a benchmark, the safety and reliability of this reference system are ensured, thereby enhancing public trust in RLRL technology. This allows the development of RLRL treatment technology and instruments to eliminate safety risks and improve efficacy without excessive clinical validation. Simultaneously, adjustments are made by reasonably comparing the differences between the light to be tested and the reference system on the retina and cornea to improve user comfort and compliance. Moreover, for the first time, personalized treatment can be achieved for patients with different refractive errors, ensuring the safety of the entire treatment process, reducing doctor-patient conflicts, and alleviating the concerns of patients and their families. Therefore, this invention solves the problem in the prior art of lacking a method for measuring and controlling retinal light power density and spot size in RLRL red light therapy. Attached Figure Description

[0041] Figure 1 This is a flowchart of a method for visually controlling the light power density on the retina and ensuring safety, as described in the first embodiment of the present invention.

[0042] Figure 2 This is an optical path diagram for measuring the size of a simulated light spot on the retina according to an embodiment of the present invention;

[0043] Figure 3 This is a schematic diagram of an intrinsically reliable photometer for spot uniformity and power density according to an embodiment of the present invention.

[0044] Figure 4 This is a graph showing the variation of the light spot size and optical power density on the retina under different refractive powers according to an embodiment of the present invention;

[0045] Figure 5This is a schematic diagram illustrating how the size of the LED chip determines the size of the light spot on the retina, according to an embodiment of the present invention.

[0046] Figure 6 This is a schematic diagram illustrating the optimization of the light spot size on the retina in an embodiment of the LD-type red light therapy device of the present invention;

[0047] Figure 7 This is a schematic diagram of the results of a system for visually controlling the light power density on the retina and ensuring safety, as described in the fifth embodiment of the present invention.

[0048] Figure 8 This is a schematic diagram of the structure of the electronic device in the sixth embodiment of the present invention;

[0049] The following detailed description, in conjunction with the accompanying drawings, will further illustrate the present invention. Detailed Implementation

[0050] To facilitate understanding of the present invention, a more complete description will be given below with reference to the accompanying drawings. Several embodiments of the invention are illustrated in the drawings. However, the invention can be implemented in many different forms and is not limited to the embodiments described herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete.

[0051] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains. The terminology used herein in the specification of this invention is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. The term "and / or" as used herein includes any and all combinations of one or more of the associated listed items.

[0052] Example 1

[0053] Please see Figure 1 The figure shows a method for visually controlling the light power density on the retina and ensuring safety in the first embodiment of the present invention. The method specifically includes steps S01-S04.

[0054] S01, a reference light is shone onto the simulated eye, and optical reference data of the corneal region and the retinal region of the simulated eye are collected, wherein the reference light is red sunlight.

[0055] Specifically, under preset conditions, illumination data of sunlight illuminating the corneal and retinal regions of multiple simulated eyes from sunrise to a target time point are collected. The above steps are repeated on different dates within a preset time period to collect the illumination data. All illumination data are filtered and fused to determine the optical reference data. The preset conditions include at least a fixed location and a fixed angle. Further, the tolerance limit time point for the operator's naked-eye observation of sunrise for each simulated eye is obtained. The illumination data is filtered according to the limit time point to determine the target illumination data. The target illumination data is statistically processed to determine the optical reference data. By using the parameters collected from the simulated eye illumination by red sunlight during normal sunrise as the evaluation reference value, its accuracy and safety can be effectively guaranteed. Specifically, during the specific filtering, the maximum tolerance light power density value of the naked eye to red sunlight is used as the safe reference value for corneal position. This value is measured to be approximately 2.1 ± 0.2 mW / cm² using conventional methods. This value should be the extreme short-term visible power density of parallel sunlight at the corneal location, and the average power density of 1.0 mW / cm² for viewing sunrise should be set as the comfort value to assess the comfort of the light being tested, ensuring compliance. Additionally, as an example, and not a limitation, in some optional embodiments, when the pupil diameter is 3 mm and the corneal power density is the average value or comfort value of 1.0 mW / cm² for viewing sunrise, the simulated 0.25 mm diameter spot on the retina corresponds to a power density of 144 mW / cm², and this value is defined as the original safety reference value. The formula for calculating this value is (IS) / (πr). 2 The molecule represents the light power entering the pupil, I is the light power density at the corneal location (I = 1.0 mW / cm²), S is the pupil area, and r is the radius of the solar spot on the retina (r = 0.025 / 2 cm). Clearly, the smaller r is, the greater the light power density on the retina for the same I and S values. Furthermore, in practical implementation, because the sun rises too quickly, it is difficult to measure all parameters simultaneously; therefore, the size of the solar spot can be replaced by sunlight from other times of the day.

[0056] Because the human retina can tremble, it may defocus and dodge when exposed to strong light. Combined with diffraction effects and coma effects in the solar continuous spectrum, it is estimated that the diameter of the light spot on the simulated retina will double (estimated to be 0.5 mm). In this case, the correction value for the safety reference is 38 mW / cm². Furthermore, based on the sunrise time, the duration until the naked eye can no longer tolerate the light is approximately 7 minutes. The average retinal light power density is 1 mW / cm², the average pupil diameter is 3 mm, and the total light dose is calculated to be 0.030 J / particle. It should be noted that these parameters were obtained experimentally during the implementation of a specific embodiment and are used here for illustrative purposes, not as limitations.

[0057] Furthermore, the simulated eye includes a main body and a single-sided frosted glass disposed on one side of the main body, with the non-transparent side of the single-sided frosted glass serving as the retina of the simulated eye. In specific implementations, in all embodiments of the present invention, the simulated eyeball 101 is an optical glass sphere with a diameter of 22 mm; the simulated iris 102 is an aluminum foil with a hole of approximately 3 mm in diameter, forming a simulated pupil 106; the simulated retina 104 is one side of the single-sided frosted glass 105, which is closer to the simulated eyeball 101, while the other side remains transparent. The light-blocking rubber 103 provides elastic clamping for the frosted glass 105. By squeezing the light-blocking rubber 103, the frosted glass 105 can be moved back and forth to achieve focusing. Focusing can be performed on distant building outlines in sunlight or in shady conditions. Theoretically, the frosted glass surface should be located approximately 1.5R from the center point of the glass simulated eye 101, where R is the radius of the simulated eyeball 101. Therefore, the simulated retina 104 is theoretically approximately 5.5 mm from the surface of the simulated eyeball 101.

[0058] S02, the light to be tested is shone onto the simulated eye, and optical test data of the corneal region and the retinal region of the simulated eye are collected.

[0059] Specifically, since LD lasers are Gaussian beams, their beam uniformity needs to be accurately detected to avoid potential safety hazards caused by poor beam uniformity, thus requiring the elimination of this interference. Therefore, in practical implementation, an intrinsically reliable optical power density photometer suitable for monochromatic light can be used for detection. The photometer 5 consists of a silicon photodiode 501, an aluminum cover 502, a probe aperture 503, a transparent insulating layer 504, a photoelectric conversion module 505, a resistor 506, and a photoelectric display 507.

[0060] The so-called "intrinsic reliability" is based on the following physical logic: a 650nm photon can excite an electron in a silicon photovoltaic cell 501. The photocurrent forms a voltage through resistor 506. Measuring this voltage directly yields the total number of received photons. Multiplying this voltage by the energy of a single photon, hν, gives the total light energy illuminating the detector aperture 503. Dividing this by the area of ​​the detector aperture 503 gives the light power density. The reliability of this measurement method is determined by physical laws and requires no calibration; therefore, it is called intrinsic reliability.

[0061] In all embodiments of the present invention, the detection aperture 503 on the aluminum cover 502 has a diameter of 1 mm; the light-receiving area of ​​the silicon photovoltaic cell 501 is 4 mm × 4 mm; the transparent insulating layer 504 is a layer of air with a gap of less than 0.5 mm. This design ensures that the aperture area is equal to the light-receiving area of ​​the silicon photovoltaic cell. The detection aperture 503 has a diameter of only 1 mm, which makes it suitable for detecting the uniformity of the light spot, something that currently commercially available lux meters cannot achieve. For example, when a 5 mW LD is expanded to the highest power density of 2 mW / cm² (a common value for RLRL) at the center of the light spot, the laser spot becomes 70 mm × 40 mm. Measurements show that within a range of 12 mm × 8 mm, the light power density fluctuation is < ±6%, while the pupil diameter under strong light is typically about 3 mm. Therefore, the laser power within the pupil range can be considered uniform. That is, under this expansion condition, there is no need to worry about the Gaussian distribution of the LD causing uneven light spot and leading to safety issues.

[0062] Although the measurement method is intrinsically reliable, two corrections are still needed: First, the photoelectric conversion quantum efficiency cannot reach the ideal 100%, and this invention uses 90% based on experience; second, the reflectivity of the silicon surface of a silicon photovoltaic cell is about 33%, meaning that the detected light power is 33% less than the actual incident power. Both of these factors can lead to significantly underestimated measurement results, and failure to correct them may cause safety or compliance issues.

[0063] S03, Based on the interpolation method, determine the associated dataset of the retinal regions of the simulated eye under different refractive powers.

[0064] Specifically, because the illumination parameters at the retina of the eye differ under the same light irradiation at different refractive degrees, the interpolation method is used to determine the mapping correlation data of illumination parameters between different refractive degrees and no refractive degree. This allows for personalized treatment for patients with different refractive degrees, ensuring the safety of the entire treatment process.

[0065] S04, the emitting device is adjusted according to the type of the emitting device of the light to be tested, the optical reference data, the optical test data and the associated dataset.

[0066] Specifically, when the emitting device for the light under test is an LD type, the optical test data is adjusted according to the associated dataset to determine the differences in corneal position power density, retinal spot area, and retinal power density parameters between the adjusted optical test data and the optical reference data under different refractive powers; the driving current of the emitting device is adjusted so that the values ​​of corneal position power density and retinal power density are lower than the reference values ​​in the corresponding optical reference data; the lens of the emitting device is adjusted so that the retinal spot area is higher than the reference value in the corresponding optical reference data to determine the corrected device optical data; the single-use time of the emitting device is determined according to the corrected device optical data and the dose reference value in the optical reference data, so that the actual dose value generated by a single use is consistent with the dose reference value or adjusted in combination with historical clinical data.

[0067] Additionally, when the emitting device for the light under test is an LED type and the light under test is collimated parallel light, the optical test data is adjusted according to the associated dataset to determine the differences in corneal position power density, retinal spot area, and retinal power density parameters between the adjusted optical test data and the optical reference data under different refractive errors. The size and model of the LED chip, the average operating current, and the distance between the collimating lens and the LED chip or the focal length of the emitting device are adjusted to ensure that the corneal position power density and the retinal power density are lower than the reference values ​​in the corresponding optical reference data, and that the retinal spot area is higher than or lower than the reference values ​​in the corresponding optical reference data, thereby determining the corrected device optical data. The single-use time of the emitting device is determined based on the corrected device optical data and the dose reference value in the optical reference data, so that the actual dose value generated in a single use is consistent with the dose reference value, or adjusted in conjunction with historical clinical data. It should be noted that "consistency" as described in this specification requires small-scale adjustments based on clinical trials, ensuring safety. Furthermore, when adjusting in conjunction with historical clinical data, small-scale adjustments are usually made by physicians based on clinical experience.

[0068] Furthermore, the step of adjusting the emitting device according to the type of the emitting device of the light under test, the optical reference data, the optical test data, and the associated dataset includes: sequentially setting a single-sided frosted glass and a collimating lens outside the emitting port of the emitting device, so that the emitted light of the emitting device is focused on the single-sided frosted glass to form a small light spot, and the small light spot is then collimated by the collimating lens to form parallel light; adjusting the emitting device according to the optical test data of the parallel light on the simulated eye, the optical reference data, the type of the emitting device, and the associated dataset. In practice, because the type of light to be measured by both LD and LED devices differs from that of red sunlight and is not collimated parallel light, it is difficult to achieve a good adjustment effect due to interference from the difference in light type. For LED devices, the requirements are usually met by changing the chip size; for LD devices, an additional single-sided frosted glass and a collimating lens are used to make the emitted light of the LD device consistent with the red sunlight of the reference system, reducing the interference from the difference in light type. This results in a better effect after adjustment, ensuring both safety and compliance, as well as the therapeutic effect.

[0069] It should be noted that the method of this invention allows for the intuitive determination of parameters affecting safety, compliance, and therapeutic efficacy, which can then be adjusted based on a reference light to optimize the therapeutic effect. When the reference system changes, for example, with a new standard or irradiation light, new standard values ​​for safety, compliance, and therapeutic efficacy are determined, adjustments can still be made without question according to the scheme of this invention. Furthermore, these various modifications and improvements all fall within the protection scope of this invention.

[0070] In summary, the method for visually controlling the light power density on the retina and ensuring safety in the above embodiments of the present invention introduces a simulated eye equipped with a retina. The simulated eye is illuminated with red sunlight as a reference light to obtain optical reference parameters on the cornea and retina under a natural reference system. The light to be tested is then tested through the simulated eye to determine the corresponding optical test data. This allows for accurate determination of the optical data on the retina, enabling accurate identification and judgment of the light to be tested. Furthermore, by introducing a natural parameter system—based on sunlight that people are constantly exposed to in daily life—as a safety assessment standard, using data on the gradual change in intensity during sunrise as a benchmark, the safety and reliability of this reference system are ensured, thereby enhancing public trust in RLRL technology. This allows the development of RLRL treatment technologies and instruments to eliminate safety risks and improve efficacy without excessive clinical validation. Simultaneously, adjustments are made by reasonably comparing the differences between the light to be tested and the reference system on the retina and cornea to improve user comfort and compliance. In addition, for the first time, personalized customization can be achieved for patients with different refractive errors, ensuring the safety of the entire treatment process, reducing doctor-patient conflicts, and alleviating the concerns of patients and their families. Therefore, this invention solves the problem in the prior art of lacking a method for measuring and controlling retinal light power density and spot size in RLRL red light therapy.

[0071] Example 2

[0072] Please see Figures 2 to 4 In a specific implementation, an example of a method for controlling laser light power density, dose, and safety on the retina in one embodiment of the present invention is as follows:

[0073] S11: Hardware preparation.

[0074] The hardware component is a simulated eye 1, which can be purchased or made by oneself. The simulated eye 1 consists of a simulated eyeball 101, a simulated iris 102, light-blocking rubber 103, a simulated retina 104, a frosted glass 105, and a simulated pupil 106. The simulated eyeball 101 is an optical glass sphere with a diameter of approximately 22mm; the simulated retina 104 is one side of the frosted glass 105, which faces the simulated eyeball 101, while the other side of the frosted glass 105 remains transparent.

[0075] Before using the simulated eye 1, it needs to be focused: Theoretically, for a simulated eyeball 101 with a refractive index of 1.5, the simulated retina 104 should be positioned R / 2 (i.e., 5.5 mm) from the surface of the eyeball after focusing. In practice, on a sunny day in a shaded area, point the simulated eye 1 at a distant building and move the frosted glass 105 until the center of the simulated retina 104 clearly shows the outline of the building. In addition, to accurately measure the spot size, the microscope focusing markings should be marked on the simulated retina 104 with a marker.

[0076] Hardware component two is an intrinsically reliable photometer 5 suitable for monochromatic light, which can be purchased externally or made in-house. It includes a silicon photodiode 501, an aluminum cover 502, a probe aperture 503, a transparent insulating layer 504, a photoelectric conversion module 505, a resistor 506, and a photoelectric display 507. The intrinsically reliable photometer 5 is used to measure the optical power density of monochromatic light at the corneal location and to determine the uniformity of the light spot.

[0077] S12, Measurement of the size of the red sunlight spot.

[0078] The simulated eyeball 101 has a diameter of 22mm, which is comparable to the axial length or diameter of a child's eyeball. The simulated iris 102 is made of aluminum foil and has a hole with a diameter of about 3mm, forming the simulated pupil 106. The simulated retina 104 is one side of a single-sided frosted glass 105, which is close to the simulated eyeball 101, while the other side remains transparent. The frosted glass 105 is 3mm-4mm thick and 22mm in diameter. The light-blocking rubber 103 has an inner diameter of 20mm and is fixed by elastic clamping. Squeezing the light-blocking rubber 103 can move the frosted glass 105 back and forth to achieve focusing. The focusing operation can be performed on a sunny or shaded day, aiming at the outline of a distant building. Theoretically, the frosted glass surface should be located 1.5R away from the center point of the simulated eyeball 101 (R is the radius of the simulated eyeball 101).

[0079] When red light 2 selects red sunlight, the size of its spot on the simulated retina 104 (i.e., the image of the solar "disk") is measured using the reading display mirror 4. The measured diameter is about 0.25 mm, which is much smaller than the 1.5 mm diameter of the extended fovea, but comparable to the 0.5 mm diameter of the fovea core region.

[0080] S13, Measurement of red light spot size of LD and judgment of safety and dosage rationality.

[0081] When red light 2 is selected as LD red light, a common pen-type red light LD8 is used. Utilizing its built-in lens 801, the light spot at a distance of 2.2 meters from the LD is adjusted to approximately 70mm × 40mm, forming LD red light (divergence angle approximately 36 mrad). An intrinsically reliable photometer 5 is used to adjust the value at the flat center of the light spot power distribution to the common RLRL prescription value of 2.0mW / cm². The spot size on the simulated retina 104 is measured using a reading display mirror 4 and found to be 0.427mm, which is larger than the 0.25mm spot diameter of red sunlight. The approximate assessment is as follows:

[0082] An emmetropic eye can look directly at LD red light with these light parameters, but for no more than 3 minutes, to ensure that the dose does not exceed the daily dose of red sunlight viewed with the naked eye (0.030J / day).

[0083] The light power density of 2.0 mW / cm² exceeds the tolerance value when viewing the sunrise and should be adjusted to 1.0 mW / cm², which meets the maximum limit specified in IEC 60825. To maintain the reference dose, the irradiation time should be extended to 6 minutes at this time.

[0084] The simulated retinal spot size of 0.427 mm on retina 104 is close to the size of the foveal core area (0.5 mm in diameter), which is basically reasonable. Adjusting it to 0.5 mm may result in better treatment effect and improved compliance.

[0085] In summary, when the power density entering the eye at the corneal position is less than half of the maximum tolerance value for direct viewing of red sunlight with the naked eye, the collimated LD red light can be considered safe, and this judgment can be made without measuring the power density on the actual retina of the human eye. The measured maximum tolerance value for viewing red sunlight with the naked eye is 2.1 ± 0.2 mW / cm², and half of this, the average value, is 1.0 mW / cm², which is also the upper limit for laser safety specified by IEC 60825. However, as we will see in the next step, even if the IEC standard is met under certain collimation conditions, LD red light still poses an extremely high risk, indicating that the IEC standard needs improvement.

[0086] S14, Measurement and parameter correction of LD red light spot size under different refractive powers.

[0087] The red light parameters of LD are the same as described above. Different optometry lenses 3 are placed about 10mm in front of the simulated pupil 106. The reading display mirror 4 is used to measure the changes in the diameter D and area S of the light spot on the simulated retina 104 under different refractive power D values, and the DD curve 10 and DS curve 11 are obtained.

[0088] As shown in DD curve 10, the spot size is smallest when a -7D negative lens is inserted, only 0.082 mm, and its area is 1 / 10 of the area of ​​the red sunlight spot, meaning the light power density on the retina is 10 times that of red sunlight. It should be noted that this conclusion is based on the collimation state of LD red light described in the previous step. However, regardless of how the lowest point of DD curve 10 shifts with other collimation states, the spot diameter of LD red light may be much smaller than the 0.25 mm of red sunlight. Therefore, when using an LD-type optical supplement, it is necessary to monitor and measure the spot size of the simulated retina 104 using a simulated eye 1. This operation is not currently adopted in the industry.

[0089] DS curve 11 shows that different refractive errors require adjustments to the corresponding RLRL treatment parameters to avoid exceeding the light power density limit. For example, the light power density on the simulated retina 104 of an emmetropic eye (0D) is more than twice that of a 300-degree myopic eye (-3D). Therefore, emmetropic children should not use red light therapy devices calibrated for 300-degree myopic eyes (-3.0D). Currently, the field of optometry has not paid enough attention to the impact of refractive error on the safety of RLRL. The proportional relationship between refractive errors obtained by simulating eye 1 in this embodiment can be fully extended to practical applications.

[0090] In this embodiment, after the LD red light reduces the light power density to 1.0 mW / cm², this parameter is only safe for emmetropic eyes compared to red sunlight, and the 6-minute treatment dose and retinal spot size are reasonable. For patients with other refractive errors, the built-in lens 801 in the LD8 needs to be adjusted so that the spot size on the simulated retina is not less than 0.25 mm of red sunlight, while ensuring that the light power density at the corneal position is 1 mW / cm². These dual requirements are sometimes difficult to meet simultaneously and require improvement through the following embodiments.

[0091] Example 3

[0092] See Figure 2 Figure 5 illustrates the retinal spot size, light power density, and treatment dose control method of an LED-type phototherapy device in one embodiment of the present invention. The implementation steps are similar to those in Embodiment 1, as detailed below:

[0093] Red light 2 uses LED red light, and its spot size on the simulated retina 104 is measured using a reading display mirror 4. To improve the power density on the simulated retina 104, the developed LED phototherapy glasses employ special packaging technology to reduce the LED emission angle to 17° (the minimum emission angle of commercially available LEDs is usually 30°). During testing, the distance between the LED surface and the simulated pupil 106 was 10mm, and the measured spot size on the simulated retina 104 was approximately 6mm × 6mm. If the power density at the corneal position remains the same, the power density on the simulated retina 104 is only 1 / 733 of that of red sunlight. In this case, the RLRL effect may be inferior to that of the LD type phototherapy device. If an LED with an emission angle of 30° is used, the effect will be even worse, but these glasses can still be used for phototherapy of the macular region (5mm diameter) or for macular degeneration treatment.

[0094] Based on the above measurement results, the optical path design of the LED-type phototherapy device requires the addition of a collimating lens 7. The LED chip 6 is a vertical chip (preferably a vertical thin-film chip), located at the front focal point of the collimating lens 7 and bonded to the LED substrate 601. The hemispherical LED package 602 of the LED chip 6 does not alter the optical path; this optical path design is roughly consistent with that used by current high-power flashlight manufacturers such as CREE. The difference lies in the fact that high-power flashlights typically use large-size power chips with side lengths in the millimeter range, while this invention, to control the size of the retinal light spot, tends to use smaller chips, such as a 10mil InGaAlP red light vertical small chip (actual size approximately 0.20mm × 0.20mm, light power output 4mW~8mW, meeting the needs of naked-eye phototherapy). Currently, the size of Micro LED chips can be further reduced to 0.05mm, therefore, the light spot size of the LED-type red light phototherapy device on the simulated retina 104 can reach the level of red sunlight, and the therapeutic effect can be comparable to that of the LD-type phototherapy device.

[0095] The LED chip in the LED-type red light therapy device can be designed as a multi-chip combination (such as 4 chips). The 4 chips emit light under computer control, which can achieve full spatiotemporal modulation and, to a certain extent, mimic the speckle effect of laser. The speckle effect originates from the coherence of laser, and its irradiation effect is essentially the modulation of light intensity in time and space.

[0096] By simulating the eye 1, the anterior and posterior positions of the collimating lens 7 can be changed, adjusting the light spot parameters on the simulated retina 104. This allows for automatic adaptation to the RLRL treatment parameters of patients with different refractive errors, making the LED phototherapy device more reasonable and safer than the existing LD type phototherapy device. However, this design leads to inconsistencies in the optical path, making it less readily accepted by the industry than the improved LD type phototherapy device described below (which uses parallel light, strictly mimicking red sunlight). Furthermore, a single LED 6, in conjunction with the collimating lens 7, can also achieve time-varying control of the retinal light spot.

[0097] Example 4

[0098] Referring to Figures 2 to 6, the retinal spot size, optical power density, and dose control method of the improved LD phototherapy device in one embodiment of the present invention are as follows:

[0099] Based on the idea that "the size of the LED chip 6 can change the size of the light spot on the simulated retina 104," an innovative design was implemented for the LD-type red light phototherapy device: LD8 focuses the laser onto a single-sided frosted glass 9 to form a small light spot. This small light spot is then collimated by a collimating lens 7 to form parallel light similar to red sunlight, and the size of the light spot on the simulated retina 104 is measured. By controlling the size of the light spot on the single-sided frosted glass 9, the size of the light spot on the retina can be flexibly adjusted. This method is safer and more controllable than directly irradiating the eye with LD red light, and it can also provide personalized parameter correction for patients with different refractive errors.

[0100] Furthermore, while ensuring that the total light flux or total dose is consistent with the total amount of red light obtained during the entire sunrise viewing process, the improved LD type red light therapy device can make red light fill the entire fovea by controlling the size of the light spot on the single-sided frosted glass 9, which greatly reduces the retinal power density and improves the compliance and effectiveness of RLRL treatment.

[0101] The luminous intensity of LD8 itself can be modulated over time. When LD8 is used in conjunction with its built-in lens 801, time-controlled modulation can be achieved. This modulation method can enhance the therapeutic effect of RLRL and even expand new therapeutic efficacy.

[0102] Example 5

[0103] Please see Figure 7 The diagram shown is a structural block diagram of a system for visually controlling retinal light power density and safety, as proposed in the fifth embodiment of the present invention. This system 200 includes: a reference data determination module 21, a test data determination module 22, a correlation data determination module 23, and a judgment and adjustment module 24, wherein:

[0104] The reference data determination module 21 is used to illuminate the simulated eyeball with reference light and collect optical reference data of the corneal region and the retinal region of the simulated eyeball, wherein the reference light is red sunlight;

[0105] The test data determination module 22 is used to illuminate the simulated eyeball with the light to be tested and to collect optical test data of the corneal region and the retinal region of the simulated eyeball.

[0106] The associated data determination module 23 is used to determine the associated dataset of the retinal region of the simulated eyeball under different refractive powers based on the interpolation method.

[0107] The judgment and adjustment module 24 is used to adjust the emitting device according to the type of the emitting device of the light to be tested, the optical reference data, the optical test data and the associated dataset.

[0108] Example 6

[0109] In another aspect, the present invention also proposes an electronic device, please refer to [link to relevant documentation]. Figure 8 The diagram shows an electronic device according to the sixth embodiment of the present invention, including a memory 20, a processor 40, and a computer program 30 stored in the memory and executable on the processor 40. When the processor 40 executes the computer program 30, it implements the above-described method for visually controlling the light power density on the retina and ensuring safety.

[0110] In some embodiments, the processor 40 may be a central processing unit (CPU), controller, microcontroller, microprocessor or other data processing chip, used to run program code stored in memory 20 or process data, such as executing access restriction programs.

[0111] The memory 20 includes at least one type of readable storage medium, such as flash memory, hard disk, multimedia card, card-type memory (e.g., SD or DX memory), magnetic memory, magnetic disk, optical disk, etc. In some embodiments, the memory 20 can be an internal storage unit of an electronic device, such as the hard disk of the electronic device. In other embodiments, the memory 20 can also be an external storage device of the electronic device, such as a plug-in hard disk, smart media card (SMC), secure digital (SD) card, flash card, etc. Furthermore, the memory 20 can include both internal and external storage units of the electronic device. The memory 20 can be used not only to store application software and various types of data of the electronic device, but also to temporarily store data that has been output or will be output.

[0112] It should be pointed out that, Figure 8 The structure shown does not constitute a limitation on the electronic device. In other embodiments, the electronic device may include fewer or more components than shown, or combine certain components, or have different component arrangements.

[0113] This invention also proposes a computer-readable storage medium storing a computer program that, when executed by a processor, implements the above-described method for visually controlling the light power density on the retina and ensuring safety.

[0114] Those skilled in the art will understand that the logic and / or steps represented in the flowcharts or otherwise described herein, for example, can be considered as a ordered list of executable instructions for implementing logical functions, and can be embodied in any computer-readable medium for use by, or in conjunction with, an instruction execution system, apparatus, or device (such as a computer-based system, a processor-included system, or other system that can fetch and execute instructions from, an instruction execution system, apparatus, or device). For the purposes of this specification, "computer-readable medium" can mean any means that can contain, store, communicate, propagate, or transmit programs for use by, or in conjunction with, an instruction execution system, apparatus, or device.

[0115] More specific examples of computer-readable media (a non-exhaustive list) include: electrical connections (electronic devices) having one or more wires, portable computer disk drives (magnetic devices), random access memory (RAM), read-only memory (ROM), erasable and editable read-only memory (EPROM or flash memory), fiber optic devices, and portable optical disc read-only memory (CDROM). Furthermore, computer-readable media can even be paper or other suitable media on which the program can be printed, because the program can be obtained electronically, for example, by optically scanning the paper or other medium, followed by editing, interpreting, or otherwise processing as necessary, and then stored in computer memory.

[0116] It should be understood that various parts of the present invention can be implemented in hardware, software, firmware, or a combination thereof. In the above embodiments, multiple steps or methods can be implemented in software or firmware stored in memory and executed by a suitable instruction execution system. For example, if implemented in hardware, as in another embodiment, it can be implemented using any one or a combination of the following techniques known in the art: discrete logic circuits having logic gates for implementing logical functions on data signals, application-specific integrated circuits (ASICs) having suitable combinational logic gates, programmable gate arrays (PGAs), field-programmable gate arrays (FPGAs), etc.

[0117] In the description of this specification, references to terms such as "one embodiment," "some embodiments," "example," "specific example," or "some examples," etc., indicate that a specific feature, structure, material, or characteristic described in connection with that embodiment or example is included in at least one embodiment or example of the invention. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples.

[0118] The above embodiments merely illustrate several implementation methods of the present invention, and their descriptions are relatively specific and detailed, but they should not be construed as limiting the scope of the present invention. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of the present invention, and these all fall within the protection scope of the present invention. Therefore, the protection scope of this patent should be determined by the appended claims.

Claims

1. A method for visually controlling the light power density on the retina and ensuring safety, characterized in that, The method includes: A reference light is shone onto a simulated eye, and optical reference data of the corneal region and the retinal region of the simulated eye are collected. The reference light is red sunlight. The light to be tested is shone onto a simulated eye, and optical test data of the corneal region and the retinal region of the simulated eye are collected. The associated dataset of the retinal regions of the simulated eye under different refractive powers was determined based on the interpolation method. The emitting device is adjusted according to the type of the emitting device of the light to be tested, the optical reference data, the optical test data, and the associated dataset; The step of adjusting the emitting device according to the type of the emitting device of the light under test, the optical reference data, the optical test data, and the associated dataset specifically includes: When the emitting device of the light to be tested is an LD type, the optical test data is adjusted according to the associated dataset to determine the differences in corneal position power density, retinal spot area and retinal power density parameters between the adjusted optical test data and the optical reference data under different refractive powers. Adjust the drive current of the emission device so that the values ​​of the corneal power density and the retinal power density are lower than the reference values ​​in the corresponding optical reference data; Adjust the lens of the emission device so that the area of ​​the retinal spot is higher than the reference value in the corresponding optical reference data, in order to determine the optical data of the correction device; The single-use time of the emission device is determined based on the optical data of the correction device and the dose reference value in the optical reference data, so that the actual dose value generated by a single use is consistent with the dose reference value or is adjusted in combination with historical clinical data. Or, specifically including: When the emitting device of the light to be tested is an LED type and the light to be tested is a collimated parallel light, the optical test data is adjusted according to the associated dataset to determine the differences in corneal position power density, retinal spot area and retinal power density parameters between the adjusted optical test data and the optical reference data under different refractive powers. The size and model of the LED chip, the average operating current, and the distance between the collimating lens and the LED chip or the focal length of the device are adjusted to make the power density at the corneal position and the power density of the retina lower than the reference value in the corresponding optical reference data, and the area of ​​the retinal spot higher than the reference value in the corresponding optical reference data, so as to determine the optical data of the correction device. The single-use time of the emission device is determined based on the optical data of the correction device and the dose reference value in the optical reference data, so that the actual dose value generated in a single use is consistent with the dose reference value or adjusted in combination with historical clinical data.

2. The method for visually controlling the light power density on the retina and ensuring safety according to claim 1, characterized in that, Under preset conditions, the steps of illuminating a simulated eye with reference light and collecting optical reference data of the corneal and retinal regions of the simulated eye, wherein the reference light is red sunlight, include: Under preset conditions and within a preset time period, illumination data of sunlight illuminating the corneal and retinal regions of multiple simulated eyes from sunrise to the target time point were collected on different dates. The optical reference data is determined by filtering and fusing all the illumination data, and the preset conditions include at least a fixed location and a fixed angle.

3. The method for visually controlling the light power density on the retina and ensuring safety according to claim 2, characterized in that, The steps of filtering and fusing all the illumination data to determine the optical reference data include: Obtain the time point at which the operator's naked-eye observation of sunrise corresponds to each of the simulated eyes; The illumination data is filtered according to the extreme time nodes to determine the target illumination data; The target illumination data is statistically processed to determine the optical reference data.

4. The method for visually controlling the light power density on the retina and ensuring safety according to claim 1, characterized in that, The step of adjusting the emitting device according to the type of the emitting device of the light under test, the optical reference data, the optical test data, and the associated dataset includes: A single-sided frosted glass and a collimating lens are sequentially arranged outside the outlet of the emission device so that the emitted light from the emission device is focused on the single-sided frosted glass to form a small light spot, and the small light spot is then collimated by the collimating lens to form parallel light. The emission device is adjusted based on the optical test data of the parallel light on the simulated eye, the optical reference data, the type of emission device, and the associated dataset.

5. The method for visually controlling the light power density on the retina and ensuring safety according to any one of claims 1 to 4, characterized in that, The simulated eye includes a main body and a single-sided frosted glass disposed on one side of the main body, wherein the non-transparent side of the single-sided frosted glass is the retina of the simulated eye.

6. A system for visually controlling the light power density on the retina and ensuring safety, characterized in that, The system is used to implement the method for visually controlling the light power density on the retina and ensuring safety as described in any one of claims 1 to 5, the system comprising: The reference data determination module is used to illuminate the simulated eye with reference light and collect optical reference data of the corneal region and the retinal region of the simulated eye, wherein the reference light is red sunlight; The test data determination module is used to illuminate the simulated eye with the light to be tested and to collect optical test data of the corneal region and the retinal region of the simulated eye. The associated data determination module is used to determine the associated dataset of the retinal region of the simulated eye under different refractive powers based on the interpolation method. The determination and adjustment module is used to adjust the emitting device according to the type of the emitting device of the light to be tested, the optical reference data, the optical test data, and the associated dataset.

7. A computer-readable storage medium having a computer program stored thereon, characterized in that, When the program is executed by the processor, it implements the steps of the method for visually controlling the light power density on the retina and ensuring safety as described in any one of claims 1 to 5.

8. An electronic device, characterized in that, It includes a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor, when executing the program, implements the method for visually controlling the light power density on the retina and ensuring safety as described in any one of claims 1-5.

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