A scattering lens and a design method thereof

Abstract

The application discloses a scattering lens and a design method thereof applied to the technical field of optical devices and vision correction, and aims to solve the technical contradiction that a traditional myopia control lens is difficult to consider central vision clarity and effective intervention of a peripheral retina, the method constructs a central, transition and peripheral three-zone heterogeneous scattering array, differentiates and configures unit density, size and scattering angle, and adopts non-periodic arrangement to inhibit optical artifacts; in combination with a pupil self-adaptive modulation layer and a task mode switching module, dynamic response of light and a visual task is realized; on the design, based on individual physiological parameters, a multi-objective genetic algorithm is iteratively calibrated, and the peripheral retina contrast control efficiency is improved by more than three times, while the central area contrast loss is less than 5%, so that high-precision, personalized and all-weather myopia control effect is realized.

Description

Technical Field

[0001] This invention relates to the field of optical devices and vision correction technology, and in particular to a scattering lens and its design method. Background Technology

[0002] With the global incidence of myopia continuing to rise, especially among adolescents, showing a trend of high prevalence and younger onset, optical intervention, as a non-invasive and long-term wearable method of prevention and control, has become a core direction for clinical research and industrial application. Currently, mainstream myopia control lenses are mainly based on peripheral defocus theory and retinal contrast modulation mechanisms. By introducing microstructured optical elements on or inside the lens surface, they alter the imaging characteristics of incident light on the retina, thereby inhibiting abnormal axial elongation. These lenses typically use microlens arrays or diffractive optical elements as basic scattering units, and their design goal is to transmit inhibitory optical signals to the peripheral retina without significantly sacrificing central vision.

[0003] Among them, contrast control lenses based on the principle of uniform scattering have dominated the market. The core design idea is to deploy scattering units with completely consistent geometry and optical function throughout the entire lens area. By globally reducing the contrast of retinal imaging, the eye growth regulation mechanism is triggered. Although this method has a high degree of consistency and reproducibility in manufacturing process, its inherent homogeneous structure makes it impossible to dynamically adjust optical performance with spatial position. It is difficult to match the regional physiological response differences of the human eye's visual system. The high dependence of the fovea on high-contrast detail information and the sensitivity of the peripheral retina to low-frequency defocus signals form a natural contradiction. Existing lenses, due to the lack of spatial modulation capabilities, are forced to compromise between visual clarity and control performance.

[0004] In existing technologies, uniformly scattering lenses generally suffer from a dual drawback: excessive scattering in the central region leads to glare and blurred vision, while insufficient scattering in the peripheral region causes attenuation of the control signal. The root cause is that all scattering units share the same optical response function, making it impossible to differentiate configurations based on field of view, pupil position, or individual axial length parameters. Furthermore, different users' visual behavior patterns (such as prolonged near reading or distant viewing) and physiological characteristics (such as pupil dynamic range and accommodative hysteresis) place highly personalized demands on the lens's scattering distribution, which existing products cannot achieve due to their structural rigidity. In clinical practice, this "one-size-fits-all" optical design not only limits the upper limit of myopia control efficiency but also reduces wearing compliance due to decreased visual comfort, ultimately weakening the intervention effect. Therefore, there is an urgent need for a new myopia control lens architecture that can achieve spatially programmable scattering characteristics and synergistic optimization of visual quality and control efficiency. Summary of the Invention

[0005] The core of this invention lies in the regional precise control of retinal imaging contrast by configuring microstructure units with differentiated optical scattering characteristics in different areas of the lens. This solves the technical contradiction in existing myopia control lenses that are difficult to balance central visual clarity and effective intervention of the peripheral retina. At the same time, it combines a pupil adaptive modulation layer and a task mode switching module to achieve dynamic response to illumination and visual tasks.

[0006] To solve the above problems, the present invention adopts the following technical solution.

[0007] A scattering lens includes a base optical lens, a heterogeneous scattering unit array, a pupil adaptive modulation layer, and a task mode switching module. The heterogeneous scattering unit array covers the surface of the base optical lens or is embedded inside it. The base optical lens is divided into three concentric ring areas: a central vision protection area, a transitional function adjustment area, and a peripheral myopia control area.

[0008] The pupil adaptive modulation layer is composed of electrochromic material or liquid crystal polymer and is disposed above or below the heterogeneous scattering unit array. The optical transmittance or scattering intensity of the pupil adaptive modulation layer varies with the incident light intensity or the applied electric field.

[0009] The task mode switching module is used to drive the heterogeneous scattering unit array to produce submicron-level displacement along the optical axis. The direction and amplitude of the displacement are determined according to the wearer's axial length and accommodative hysteresis.

[0010] The task mode switching module includes a piezoelectric ceramic actuator, a flexible hinge, a displacement amplification mechanism, a position sensor, and a control circuit. The piezoelectric ceramic actuator has a maximum displacement of 20 micrometers and a driving voltage of 0 to 150 volts. The flexible hinge adopts a double parallelogram structure with a magnification factor of 5, amplifying the piezoelectric ceramic displacement to 100 micrometers. The output end of the displacement amplification mechanism is rigidly connected to the heterogeneous scattering unit array substrate. The position sensor is a capacitive displacement sensor. The control circuit outputs a driving voltage according to the wearer's visual task switching signal.

[0011] Furthermore, the heterogeneous scattering unit array consists of multiple optical scattering units. The spatial distribution density, geometry, size parameters, and scattering intensity of the optical scattering units on the substrate optical lens are configured differently according to the visual function requirements of their respective areas. In the central vision protection zone, the distribution density of optical scattering units is less than five units per square millimeter, the unit size is less than five micrometers, and the half-width at half-maximum (WHM) of the scattering angle is less than three degrees. In the peripheral myopia control zone, the distribution density of optical scattering units is more than fifty units per square millimeter, the unit size is between ten and thirty micrometers, and the WHM of the scattering angle is between ten and twenty-five degrees. In the transitional function adjustment zone, the distribution density, size, and scattering angle parameters of the optical scattering units exhibit a continuous gradient change along the radial direction.

[0012] Furthermore, the arrangement of the optical scattering units adopts an aperiodic spatial coding strategy, employing a pseudo-random distribution pattern in the central vision protection zone, a radially symmetrical distribution pattern in the peripheral myopia control zone, and a weighted interpolation distribution pattern in the transitional function adjustment zone.

[0013] A method for designing a scattering lens, applied to the aforementioned scattering lens, specifically includes the following steps:

[0014] Step 1: Obtain the wearer's physiological parameter dataset, which includes axial length, corneal curvature, pupil diameter, accommodation amplitude, and retinal sensitivity distribution map.

[0015] Step 2: Establish a ray tracing model of the wearer's eyeball. The ray tracing model includes the optical parameters of the cornea, lens, vitreous body, and retina, and imports the physiological parameter dataset for individualized calibration.

[0016] Step 3: Define the functional zone boundaries of the lens. The functional zone boundaries are determined based on the dynamic range of the wearer's pupil diameter and the retinal functional zone diagram, and are divided into three concentric ring areas: the central vision protection zone, the transitional functional accommodation zone, and the peripheral myopia control zone.

[0017] Step 4: Assign target scattering characteristic parameters to each functional zone. The target scattering characteristic parameters include scattering intensity, scattering angle distribution function, and spatial frequency attenuation coefficient.

[0018] Step 5: Based on the target scattering characteristic parameters, reverse optimize the design of the geometry, size, distribution density and arrangement function of the heterogeneous scattering unit array in each functional zone;

[0019] Step 6: Verify the design results using a ray tracing model. Calculate the contrast modulation function and defocus distribution of retinal imaging at each field of view. If the calculated result deviates from the target value by more than 10%, return to the reverse optimization design step for parameter iteration and correction. If the calculated result meets the preset tolerance, output the final heterogeneous scattering unit array structure parameter file to guide lens manufacturing.

[0020] Step 7: After the lens is manufactured, a fit test is conducted on the wearer through subjective visual quality assessment and objective optical performance testing. Subjective visual quality assessment includes visual acuity chart test, contrast sensitivity function measurement, and glare discomfort threshold questionnaire. Objective optical performance testing includes wavefront aberration analysis, modulation transfer function scanning, and scattered light distribution imaging. If the assessment results do not meet the preset standards, the local parameters of the heterogeneous scattering unit array are fine-tuned according to the test data, and the lens is further corrected through laser micromachining or local coating process.

[0021] Furthermore, step seven, the adaptation testing and secondary correction, includes the following steps:

[0022] A1. Conduct a subjective visual quality assessment:

[0023] A1.1 After wearing the lenses, the wearer should test their distance and near vision in front of a standard visual acuity chart and record the visual acuity value corresponding to the smallest resolvable optotype.

[0024] A1.2. Use a contrast sensitivity tester to measure the wearer's contrast sensitivity function at different spatial frequencies;

[0025] A1.3 Distribute a glare discomfort threshold questionnaire. The questionnaire includes multiple usage scenarios, and wearers rate the degree of glare discomfort in each scenario on a five-level scale.

[0026] A2. Conduct objective optical performance testing:

[0027] A2.1. Measure the root mean square value of the total higher-order aberrations of the wearer's eyeball using a wavefront aberrometer;

[0028] A2.2 Use a modulation transfer function scanner to measure the modulation transfer function value of the lens at different spatial frequencies, with the spatial frequency range being zero to fifty cycles per millimeter, and the measurement directions being both horizontal and vertical.

[0029] A2.3. Use a scattered light distribution imaging system to capture images of the scattered light spot of the lens under parallel light illumination, and analyze the angular distribution uniformity and radial intensity attenuation curve of the light spot;

[0030] A3. Determine the evaluation results:

[0031] The following conditions are considered as not meeting the standard: Condition 1: Visual acuity is lower than 0.8 in subjective assessment; Condition 2: Contrast sensitivity decreases by more than 20% at any frequency; Condition 3: Glare score is higher than level 4; Condition 4: Root mean square value of higher-order aberrations is greater than 0.5 micrometers in objective testing; Condition 5: Modulation transfer function is lower than 0.3 at 10 cycles per millimeter; Angular non-uniformity of scattered light spot is greater than 15%.

[0032] A4. Secondary Correction: Based on the sensitivity analysis results of the parameters corresponding to the non-compliant items, the parameters of the local scattering unit are fine-tuned. The fine-tuned parameters are then used to locally correct the lens surface through a laser micromachining device. After correction, the adaptation test is repeated until all indicators meet the standards.

[0033] Furthermore, the operation of fine-tuning the local parameters of the heterogeneous scattering unit array in step A4 includes the following situations: 1. When the contrast in the central region is insufficient, reduce the unit size or distribution density in that region; 2. When the scattering in the peripheral region is insufficient, increase the unit size or distribution density; 3. When the glare is severe, adjust the arrangement function to increase angular randomness; 4. When the aberration is too large, optimize the unit curvature distribution. The fine-tuning step size is determined according to the parameter sensitivity analysis results, with a maximum of five iterations.

[0034] Furthermore, step two, establishing a ray-tracing model of the wearer's eyeball, includes the following operations: constructing a standard optical model of the eyeball containing the anterior and posterior corneal surfaces, aqueous humor, anterior and posterior lens surfaces, vitreous humor, and retina; using the measured axial length as the total length of the model; scaling the thickness of each optical medium proportionally; replacing the radius of curvature of the anterior corneal surface in the model with the measured corneal curvature value; setting a variable aperture in the model based on the dynamic range of pupil diameter, with its aperture dynamically adjusted according to simulated lighting conditions; using the adjustment amplitude value to adjust the radius of curvature of the anterior lens surface; establishing a linear mapping relationship between the adjustment state and lens deformation; and using the retinal sensitivity distribution map as a weight matrix for regional weighting in subsequent contrast modulation function calculations.

[0035] Furthermore, step three, defining the functional zone boundaries of the lens, includes the following operations: determining the outer boundary radius of the central vision protection zone based on the maximum pupil diameter of the wearer under photopic conditions. This radius is equal to the maximum pupil radius plus a safety margin of two millimeters. Determining the inner boundary radius of the peripheral myopia control zone based on the position where the sensitivity drops to 50% of the foveal peak value in the retinal sensitivity distribution map. The transitional functional accommodation zone is located between the outer boundary of the central vision protection zone and the inner boundary of the peripheral myopia control zone. The functional zone boundaries are stored in polar coordinates, with each boundary defined by 360 radial sampling points at a sampling angle interval of one degree.

[0036] Furthermore, in step four: the target scattering intensity of the central visual protection zone is set to 0.05 to 0.1, the target scattering angle half-width is set to 1 to 3 degrees, and the target spatial frequency attenuation coefficient is set to 0.95 to 0.99. The target scattering intensity of the peripheral myopia control zone is set to 0.3 to 0.6, the target scattering angle half-width is set to 10 to 25 degrees, and the target spatial frequency attenuation coefficient is set to 0.4 to 0.7. The target parameters of the transition function adjustment zone are linearly interpolated radially, and the interpolation function is a linear weighted average. The weighting coefficient is determined by the distance ratio between the current radial position and the partition boundary.

[0037] Furthermore, in step five, the reverse optimization design of the geometry, size, distribution density, and arrangement function of the heterogeneous scattering unit array within each functional zone is performed. A multi-objective genetic algorithm is used for parameter optimization. The fitness function of the multi-objective genetic algorithm consists of three weighted terms: the first term is the contrast retention rate of the central visual protection zone, with a weight coefficient of 0.6; the second term is the contrast decay rate of the peripheral myopia control zone, with a weight coefficient of 0.3; and the third term is the gradient smoothness index of the transitional functional adjustment zone, with a weight coefficient of 0.1. The population size of the multi-objective genetic algorithm is set to 500, the upper limit of the number of iterations is 2,000 generations, the crossover probability is 0.8, and the mutation probability is 0.05.

[0038] Furthermore, in step six, verifying the design results using a ray tracing model: the simulated field of view ranges from -30 degrees to +30 degrees, the simulated pupil diameter ranges from 2 mm to 7 mm, the simulated illumination conditions include photopic, mesopic, and scotopic states, the contrast modulation function is calculated based on a sinusoidal grating target object, the spatial frequency ranges from 0.5 cycles per degree to 30 cycles per degree, the defocus distribution is calculated based on the centroid offset of the point spread function, and the sampling point density is 100 per square millimeter. If any of the following conditions are met, it is considered unqualified: Condition 1: The contrast modulation function of the central visual protection zone is lower than 0.9 at any field of view; Condition 2: The contrast modulation function of the peripheral myopia control zone is higher than 0.7 at any field of view; Condition 3: The absolute value of the defocus in the peripheral myopia control zone exceeds 0.5 diopters at any field of view.

[0039] Compared with the prior art, the advantages of this invention are:

[0040] (1) This scheme, by constructing a spatially heterogeneous scattering unit array, has for the first time achieved independent and precise optical control of the central visual area and the peripheral retinal area on the same lens, and completely solved the irreconcilable contradiction between visual clarity and myopia control performance of traditional homogeneous scattering lenses.

[0041] (2) By introducing a pupil adaptive modulation layer and a task mode switching module, the lens can dynamically respond to changes in ambient light and visual task requirements, which significantly improves wearing comfort and intervention effectiveness.

[0042] (3) By using a reverse design method based on individual physiological parameters, it is ensured that each lens is customized for the wearer, maximizing the use of their physiological characteristics to achieve precise intervention;

[0043] (4) By using a non-periodic spatial coding arrangement strategy, the generation of optical artifacts is effectively suppressed, ensuring the stability of visual quality in all weather conditions.

[0044] (5) The overall solution improves the contrast regulation efficiency of the peripheral retina to more than three times that of the traditional solution without increasing the burden on the wearer, while controlling the contrast loss of the central visual area to a clinically imperceptible level, providing a new technical path for the field of myopia prevention and control that combines scientific, engineering and clinical applicability. Attached Figure Description

[0045] Figure 1 This is a schematic diagram of the overall technical solution architecture of the present invention;

[0046] Figure 2 This is a schematic diagram of the core principle framework of the present invention for spatial non-uniform regulation of retinal imaging contrast by heterogeneous scattering unit array.

[0047] Figure 3 This is a logical framework diagram of the functional zoning and parameter gradient configuration of the central visual protection zone, the transitional functional adjustment zone, and the peripheral myopia control zone of the present invention.

[0048] Figure 4 This is a cross-regional differentiated design framework diagram of the coding strategy for the geometric shape and spatial arrangement of the optical scattering unit of the present invention.

[0049] Figure 5 This is a schematic diagram illustrating the principle framework of the dynamic response of the pupil adaptive modulation layer in this invention.

[0050] Figure 6 This is a schematic diagram of the dynamic response and defocus control principle framework of the task mode switching module of the present invention;

[0051] Figure 7 This is a flowchart illustrating the multi-stage closed-loop iterative process of the reverse optimization design method based on individual physiological parameters of the present invention.

[0052] Figure 8 This is a schematic diagram illustrating the interaction and data flow between personalized lens fitting and closed-loop correction of optical performance after lens manufacturing, as described in this invention. Detailed Implementation

[0053] The technical solutions will now be clearly and completely described with reference to the accompanying drawings in the embodiments of the present invention.

[0054] First implementation method:

[0055] Please see Figures 1-8 A scattering lens includes a base optical lens, a heterogeneous scattering unit array, a pupil adaptive modulation layer, and a task mode switching module. The heterogeneous scattering unit array covers the surface of the base optical lens or is embedded inside it. The base optical lens is divided into three concentric ring areas: a central vision protection area, a transitional function adjustment area, and a peripheral myopia control area.

[0056] Please see Figure 5 The pupil adaptive modulation layer is composed of an electrochromic material doped with tungsten oxide or a liquid crystal polymer, and is disposed above or below the heterogeneous scattering unit array. The optical transmittance or scattering intensity of the pupil adaptive modulation layer varies with the incident light intensity or the applied electric field. The thickness of the pupil adaptive modulation layer is five micrometers, consisting of two electrode layers: the upper electrode is a transparent conductive indium tin oxide thin film, and the lower electrode is a patterned metal mesh. The voltage driving circuit is integrated into the lens frame, and the ambient illuminance is detected by a photoresistor. When the ambient illuminance is below fifty lux, the pupil adaptive modulation layer is in a low scattering state, and its scattering contribution to the heterogeneous scattering unit array is reduced by more than fifty percent, with a scattering contribution rate of less than ten percent. When the ambient illuminance is higher than 500 lux, the pupil adaptive modulation layer is in a high scattering state, and its scattering contribution to the heterogeneous scattering unit array is increased by more than 30%. The voltage switching response time is 50 milliseconds, ensuring a flicker-free visual experience. The activation threshold and response time of the pupil adaptive modulation layer are individually calibrated based on the wearer's physiological measurement data of pupil diameter. For example, if the wearer's pupil diameter in scotoma is greater than 6 mm, the activation threshold is lowered to 30 lux; if it is less than 5 mm, the activation threshold is increased to 70 lux, ensuring that the modulation layer response is synchronized with the wearer's physiological reaction.

[0057] Please see Figure 6 The task mode switching module is used to drive the heterogeneous scattering unit array to produce submicron-level displacement along the optical axis. The direction and amplitude of the displacement are determined according to the wearer's axial length and accommodative hysteresis. When the wearer performs near reading tasks, the task mode switching module drives the heterogeneous scattering unit array to move three to eight micrometers toward the eyeball, so that the scattered light spot forms a forward defocus distribution on the retina. When the wearer performs far-distance observation tasks, the task mode switching module drives the heterogeneous scattering unit array to move five to twelve micrometers away from the eyeball, so that the scattered light spot forms a backward defocus distribution on the retina. The amount of displacement is determined by the clinical measurement values ​​of the wearer's axial length and accommodative hysteresis.

[0058] The task mode switching module includes a piezoelectric ceramic actuator, a flexible hinge, a displacement amplification mechanism, a position sensor, and a control circuit. The piezoelectric ceramic actuator is model PST-50 / 10 / 20, with a maximum displacement of 20 micrometers and a driving voltage of 0 to 150 volts. The flexible hinge adopts a double parallelogram structure with a magnification factor of 5, amplifying the piezoelectric ceramic displacement to 100 micrometers. The output end of the displacement amplification mechanism is rigidly connected to the heterogeneous scattering unit array substrate. The position sensor is a capacitive displacement sensor, model LMI-00, with a measurement range of ±100 micrometers and a resolution of 0.1 micrometers. The control circuit outputs a driving voltage according to the wearer's visual task switching signal. For example, when a reading task is detected, a 70-volt voltage is output to drive the heterogeneous scattering unit array to move 5 micrometers towards the eye; when a distance viewing task is detected, a 120-volt voltage is output to drive the heterogeneous scattering unit array to move 10 micrometers away from the eye. The displacement is calculated based on the wearer's axial length and accommodative hysteresis: Displacement = Accommodative Hysteresis × 0.5 + (Axial Length - 24mm) × 0.2, in micrometers. The control circuit samples at a frequency of 1 kHz to ensure zero displacement response delay.

[0059] Please see Figure 3 The heterogeneous scattering unit array consists of multiple optical scattering units. The spatial distribution density, geometry, size parameters, and scattering intensity of the optical scattering units on the substrate optical lens are configured differently according to the visual function requirements of their respective areas. In the central vision protection zone, the distribution density of optical scattering units is less than five units per square millimeter, the unit size is less than five micrometers, and the half-width at half-maximum (WHM) of the scattering angle is less than three degrees, ensuring that the imaging contrast loss in this area is less than five percent. In the peripheral myopia control zone, the distribution density of optical scattering units is more than fifty units per square millimeter, the unit size is between ten and thirty micrometers, and the half-width at half-maximum (WHM) of the scattering angle is between ten and twenty-five degrees, ensuring that the imaging contrast reduction in this area is between thirty and sixty percent. In the transition function adjustment zone, the distribution density, size, and scattering angle parameters of the optical scattering units change in a continuous gradient along the radial direction, achieving a smooth transition from central high definition to peripheral high scattering intensity.

[0060] Please see Figure 4The geometric shapes of the optical scattering units include circular protrusions, elliptical depressions, polygonal pyramids, asymmetric corrugated structures, or composite micro-relief structures. Each geometric shape corresponds to specific spatial frequency response characteristics and angular scattering distribution functions. In the central vision protection zone, circular protrusions or elliptical depressions are preferred, with a surface curvature radius greater than 50 micrometers to suppress higher-order diffraction effects. In the peripheral myopia control zone, polygonal pyramids or asymmetric corrugated structures are preferred, with edge angles between 60 and 120 degrees and corrugation periods between 5 and 15 micrometers to enhance the scattering efficiency of low spatial frequency components. The arrangement of the heterogeneous scattering unit array adopts a non-periodic spatial coding strategy to avoid moiré fringes and coherent interference artifacts caused by regular arrays. Specifically, in the central vision protection zone, the optical scattering units adopt a pseudo-random distribution pattern, and their position coordinates are determined by a low-difference sequence generation algorithm to ensure that the local density uniformity deviation is less than 3%. In the peripheral myopia control zone, the optical scattering units adopt a radially symmetrical distribution pattern, and their angular positions are arranged according to a sinusoidal modulation function. The modulation frequency decreases as the radius increases to match the spatial sampling characteristics of retinal ganglion cells. In the transitional function adjustment zone, the position distribution function of the optical scattering units is the weighted interpolation result of the central pseudo-random pattern and the peripheral radial modulation pattern, and the weighting coefficient changes linearly with the radial distance.

[0061] The difference between the refractive index of the material of the optical scattering unit and the refractive index of the substrate optical lens is between 0.05 and 0.3. In the central vision protection zone, the refractive index difference is between 0.05 and 0.1, and in the peripheral myopia control zone, the refractive index difference is between 0.2 and 0.3. The materials include polymethyl methacrylate, polycarbonate, cyclic olefin copolymer or siloxane photocurable resin. The optical scattering unit is formed on the surface of the substrate optical lens by nanoimprinting, grayscale lithography or femtosecond laser direct writing process, or embedded in the interior of the substrate optical lens by multilayer injection molding process.

[0062] The fabrication process of the heterogeneous scattering unit array is as follows: First, a grayscale mask is fabricated on a quartz substrate using electron beam lithography. The mask contains unit patterns in the central, transition, and peripheral regions, with the pattern depth encoded as an 8-bit grayscale value. Second, a polymethyl methacrylate substrate is placed in a nanoimprint lithography machine, heated to 120 degrees Celsius, subjected to a pressure of 10 bar, and imprinted for 60 seconds. After imprinting, it is cooled to room temperature and demolded to obtain the preliminary structure. Third, the structure is refined using reactive ion etching (RIE), employing a mixture of oxygen and carbon tetrafluoride in a 4:1 ratio, at a power of 200 watts for 30 seconds to eliminate residual burrs from the imprinting process. Finally, a silicon dioxide thin film with a thickness of 50 nanometers is deposited on the structure surface using atomic layer deposition (ALD) to adjust the refractive index difference. For the embedded structure, multi-layer injection molding is used: first, the base layer is injection molded, and the material is polycarbonate; then, a light-curing resin with a thickness of ten micrometers is coated on the surface of the base layer; next, patterning and curing are performed by irradiating the mask with ultraviolet light; finally, the cover layer is injection molded, and the material is cyclic olefin copolymer, to complete the sandwich structure encapsulation.

[0063] The specific implementation of the non-periodic spatial coding arrangement is as follows: The pseudo-random distribution of the central vision protection zone is generated by a Halton sequence with a two-dimensional dimension and a cardinality of two or three, generating 360 points, which are mapped onto a circular area with a radius of eight millimeters. The minimum distance constraint between points is two hundred micrometers. The radial modulation arrangement of the peripheral myopia control zone is defined by the following formula: r = R 零 +Asin(2πfθ), where R 零 Let r be the base radius, A be the modulation amplitude, f be the modulation frequency, and θ be the angular coordinate. The modulation frequency f decreases linearly with the radius r, as shown in the following formula:

[0064] ;

[0065] f 零 It is 25 Hz, R 内 It is ten millimeters, R 外 The value is 25 millimeters. The weighted interpolation function for the transition zone is calculated using the following formula: , where R 中内 It is eight millimeters, R 中外 The value is 10 mm. w is used for linear interpolation of the layout coordinates of the central and peripheral areas. All layout coordinates are verified by Delaunay triangulation to ensure no overlap and excessive clustering.

[0066] Please see Figure 7 A method for designing a scattering lens, applied to the fabrication of the aforementioned scattering lens, specifically includes the following steps:

[0067] Step 1: Obtain the wearer's physiological parameter dataset, which includes axial length, corneal curvature, pupil diameter, accommodation amplitude, and retinal sensitivity distribution map.

[0068] In acquiring the physiological parameter dataset, the wearer's axial length and corneal curvature data were first collected using a non-contact biometer, with a measurement accuracy of ±0.01 mm. Secondly, the dynamic range of pupil diameter changes was recorded under different lighting conditions using an infrared pupil meter. The lighting conditions included three standard illuminance levels: 5 lux, 50 lux, and 500 lux. Ten pupil diameter measurements were collected at each level, and the average value was taken as the stable pupil diameter at that illuminance. Thirdly, the wearer's accommodation amplitude was determined using an automated refractometer combined with a subjective refraction process, and the negative lens method was used to gradually increase the negative power. When the wearer reports the first blurring of the target, the negative value at this point is recorded as the accommodation amplitude. Finally, the wearer's retinal sensitivity distribution map is obtained using a microperimeter or an adaptive optics scanning laser ophthalmoscope. The test field of view covers a range from the fovea to the periphery of 30 degrees, with a spatial resolution of four sampling points per square millimeter. The diameter of the test stimulus spot is 0.5 degrees, and the background brightness is 30 Å. The light sensitivity threshold of each sampling point is recorded, and a two-dimensional sensitivity distribution heatmap is generated. All physiological parameter data are stored in the form of a structured data table, with fields including parameter name, measurement value, measurement unit, measurement conditions, and measurement timestamp.

[0069] Step 2: Establish a ray tracing model of the wearer's eyeball. The ray tracing model includes the optical parameters of the cornea, lens, vitreous body, and retina, and imports the physiological parameter dataset for individualized calibration.

[0070] In establishing the ray-tracing model of the wearer's eyeball, a standard optical model of the eyeball is first constructed, including the anterior and posterior corneal surfaces, aqueous humor, anterior and posterior lens surfaces, vitreous humor, and retina. The curvature radius, thickness, and refractive index of each optical interface are all initialized using the precise Gullstrand model parameters. Subsequently, the wearer's physiological parameter dataset is imported into the model for individualized calibration: the measured axial length is used as the total model length, and the thickness of each optical medium is scaled proportionally; the corneal curvature measurement value replaces the anterior corneal surface curvature radius in the model; a variable aperture is set in the model according to the dynamic range of pupil diameter, and its aperture is dynamically adjusted according to the simulated illumination conditions; the adjustment amplitude value is used to adjust the curvature radius of the anterior lens surface, establishing a linear mapping relationship between the adjustment state and lens deformation; and the retinal sensitivity distribution map is used as a weight matrix for regional weighting in the subsequent contrast modulation function calculation. The model employs a ray tracing algorithm, with the light source set as a parallel beam at a wavelength of 550 nanometers. Ten thousand rays are traced per field of view, and tracing terminates when the light reaches the retinal plane or undergoes total internal reflection. The model output includes the coordinates of each ray's landing point on the retina, its intensity, and the optical path difference.

[0071] Step 3: Define the functional zone boundaries of the lens. The functional zone boundaries are determined based on the dynamic range of the wearer's pupil diameter and the retinal functional zone diagram, and are divided into three concentric ring areas: the central vision protection zone, the transitional functional accommodation zone, and the peripheral myopia control zone.

[0072] First, the outer boundary radius of the central vision protection zone is determined based on the maximum pupil diameter of the wearer under photopic conditions. This radius is equal to the maximum pupil radius plus a safety margin of two millimeters. Second, the inner boundary radius of the peripheral myopia control zone is determined based on the position where the sensitivity drops to 50% of the foveal peak value in the retinal sensitivity distribution map. The transitional functional accommodation zone is located between the outer boundary of the central vision protection zone and the inner boundary of the peripheral myopia control zone. The functional zone boundaries are stored in polar coordinates, with each boundary defined by 360 radial sampling points at a sampling angle interval of one degree. The boundary data is used for subsequent spatial interpolation calculations of scattering unit parameters.

[0073] Step 4: Assign target scattering characteristic parameters to each functional zone. The target scattering characteristic parameters include scattering intensity, scattering angle distribution function, and spatial frequency attenuation coefficient.

[0074] In the central vision protection zone, the target scattering intensity is set to 0.05 to 0.1, the target scattering angle half-width is set to 1 to 3 degrees, and the target spatial frequency attenuation coefficient is set to 0.95 to 0.99. In the peripheral myopia control zone, the target scattering intensity is set to 0.3 to 0.6, the target scattering angle half-width is set to 10 to 25 degrees, and the target spatial frequency attenuation coefficient is set to 0.4 to 0.7. The target parameters in the transition function adjustment zone are linearly interpolated radially, with the interpolation function being a linear weighted average, and the weighting coefficients being determined by the distance ratio between the current radial position and the zone boundary. All target parameters are stored in the form of a three-dimensional tensor, with the first dimension being the radial position index, the second dimension being the angular position index, and the third dimension being the parameter type index.

[0075] Step 5: Based on the target scattering characteristic parameters, reverse optimize the design of the geometry, size, distribution density and arrangement function of the heterogeneous scattering unit array in each functional zone;

[0076] Step 6: Verify the design results using a ray tracing model. Calculate the contrast modulation function and defocus distribution of retinal imaging at each field of view. If the calculated result deviates from the target value by more than 10%, return to the reverse optimization design step for parameter iteration and correction. If the calculated result meets the preset tolerance, output the final heterogeneous scattering unit array structure parameter file to guide lens manufacturing.

[0077] Step 7: After the lens is manufactured, a fit test is conducted on the wearer through subjective visual quality assessment and objective optical performance testing. Subjective visual quality assessment includes visual acuity chart test, contrast sensitivity function measurement, and glare discomfort threshold questionnaire. Objective optical performance testing includes wavefront aberration analysis, modulation transfer function scanning, and scattered light distribution imaging. If the assessment results do not meet the preset standards, the local parameters of the heterogeneous scattering unit array are fine-tuned according to the test data, and the lens is further corrected through laser micromachining or local coating process.

[0078] Please see Figure 8 Step seven, the adaptation test and secondary correction, includes the following steps:

[0079] A1. Conduct a subjective visual quality assessment:

[0080] A1.1 After wearing the lenses, the wearer should test their distance and near vision in front of a standard visual acuity chart and record the visual acuity value corresponding to the smallest resolvable optotype.

[0081] A1.2. Use a contrast sensitivity tester to measure the wearer's contrast sensitivity function at different spatial frequencies, including 1, 3, 6, 12, and 18 cycles per degree, with a background brightness of 80 candela per square meter;

[0082] A1.3 Distribute a glare discomfort threshold questionnaire. The questionnaire includes multiple usage scenarios, such as driving at night, reading in sunlight, and working under fluorescent lights. Wearers rate the degree of glare discomfort in each scenario on a five-level scale.

[0083] A2. Conduct objective optical performance testing:

[0084] A2.1. The root mean square value of the total higher-order aberrations of the wearer's eyeball was measured using a wavefront aberrometer at a wavelength of 780 nanometers and a pupil diameter of 6 millimeters.

[0085] A2.2 Use a modulation transfer function scanner to measure the modulation transfer function value of the lens at different spatial frequencies, with the spatial frequency range being zero to fifty cycles per millimeter, and the measurement directions being both horizontal and vertical.

[0086] A2.3. Use a scattered light distribution imaging system to capture images of the scattered light spot of the lens under parallel light illumination, and analyze the angular distribution uniformity and radial intensity attenuation curve of the light spot;

[0087] A3. Determine the evaluation results:

[0088] The following conditions are considered as not meeting the standard: Condition 1: Visual acuity is lower than 0.8 in subjective assessment; Condition 2: Contrast sensitivity decreases by more than 20% at any frequency; Condition 3: Glare score is higher than level 4; Condition 4: Root mean square value of higher-order aberrations is greater than 0.5 micrometers in objective testing; Condition 5: Modulation transfer function is lower than 0.3 at 10 cycles per millimeter; Angular non-uniformity of scattered light spot is greater than 15%.

[0089] A4. Secondary Correction: Based on the sensitivity analysis results of the parameters corresponding to the non-compliant items, the parameters of the local scattering unit are fine-tuned. The fine-tuned parameters are then used to locally correct the lens surface using a laser micromachining device. The laser wavelength is 355 nanometers, the pulse width is 10 picoseconds, and the processing accuracy is 0.1 micrometers. After correction, the adaptation test is repeated until all indicators meet the standards.

[0090] The operation of fine-tuning the local parameters of the heterogeneous scattering unit array in step A4 includes the following situations: 1. When the contrast in the central region is insufficient, reduce the unit size or distribution density in that region; 2. When the scattering in the peripheral region is insufficient, increase the unit size or distribution density; 3. When the glare is severe, adjust the arrangement function to increase angular randomness; 4. When the aberration is too large, optimize the unit curvature distribution. The fine-tuning step size is determined according to the parameter sensitivity analysis results, with a maximum of five iterations.

[0091] In step five, the reverse optimization design of the geometry, size, distribution density, and arrangement function of the heterogeneous scattering unit array within each functional zone is performed. A multi-objective genetic algorithm is used for parameter optimization. The fitness function of the multi-objective genetic algorithm consists of three weighted terms: the first term is the contrast retention rate of the central visual protection zone, with a weight coefficient of 0.6; the second term is the contrast decay rate of the peripheral myopia control zone, with a weight coefficient of 0.3; and the third term is the gradient smoothness index of the transitional functional adjustment zone, with a weight coefficient of 0.1. The population size of the multi-objective genetic algorithm is set to 500, the maximum number of iterations is 2000 generations, the crossover probability is 0.8, and the mutation probability is 0.05. The optimization variables include the size, curvature, depth, spacing, and arrangement angle of the optical scattering units.

[0092] In the reverse optimization design step, the population is first initialized. Each individual represents a complete set of scattering unit parameter configurations, including the size of the central visual protection zone, the size of the peripheral myopia control zone, the gradient coefficient of the transitional functional accommodation zone size, the distribution density of the central visual protection zone, the distribution density of the peripheral myopia control zone, the density gradient coefficient of the transitional functional accommodation zone, the curvature of the central visual protection zone, the edge angle of the peripheral myopia control zone, the curvature interpolation coefficient of the transitional functional accommodation zone, the seed sequence of the central visual protection zone layout, the modulation frequency coefficient of the peripheral myopia control zone, and the interpolation weight function of the transitional functional accommodation zone. Latin hypercube sampling is used for population initialization to ensure uniform coverage of the parameter space.

[0093] The genetic algorithm then iterates through a loop, calculating the fitness value for each individual. The fitness function is a weighted sum of three terms: the first term is the absolute error between the contrast retention rate of the central visual protection zone and the target value of 0.95; the second term is the absolute error between the contrast decay rate of the peripheral myopia control zone and the target value of 0.4; and the third term is the standard deviation of the rate of change of parameters of adjacent radial sampling points in the transitional functional accommodation zone. Selection is performed using a tournament selection method with a tournament size of five. Crossover is performed using simulated binary crossover with a distribution exponent of 20. Mutation is performed using multinomial mutation with a distribution exponent of 20. The mutation probability is adaptively adjusted with the number of iterations, initially at 0.05, decaying by 5% every 50 generations. An elite retention strategy preserves the best individual from each generation directly into the next generation. The iteration terminates when the optimal fitness value changes by less than 0.001 over 2000 generations or 50 consecutive generations.

[0094] The detailed execution flow of the multi-objective genetic algorithm is as follows: I. Initialization Phase: Generate 500 individuals, each a 12-dimensional real vector. Each dimension corresponds to an optimization variable, with values ​​set according to process constraints, such as unit size ranging from 1 to 50 micrometers, radius of curvature from 10 to 100 micrometers, and distribution density from 1 to 100 per square millimeter. II. Evaluation Phase: For each individual, use a ray tracing model to calculate three indicators: Contrast retention rate in the central visual protection zone (modulation transfer function value at 0 degrees field of view, 3 mm pupil diameter, and 30 cycles per degree spatial frequency); contrast decay rate in the peripheral myopia control zone (modulation transfer function value at 25 degrees field of view, 6 mm pupil diameter, and 2 cycles per degree spatial frequency); gradient smoothness in the transition function adjustment zone (standard deviation of parameter change rate between adjacent sampling points within a radial position ranging from 8 mm to 10 mm). The fitness value F is calculated using the following formula: Where C represents the central region index, P represents the peripheral region index, and S represents the smoothness index. III. Selection Phase: Five individuals are randomly selected from the population, their fitness values ​​are compared, and the individual with the lowest fitness value is selected to enter the next generation. This process is repeated 500 times. IV. Crossover Phase: Selected individuals are paired and crossover is performed with a probability of 0.8. The crossover point is randomly selected, and the offspring parameters are calculated using a simulated binary crossover formula. V. Mutation Phase: For each offspring individual, each dimension is mutated using the current mutation probability. The mutation magnitude is calculated using a polynomial mutation formula. VI. Elite Retention Phase: The best individual from the parent generation is directly copied to the offspring, replacing the worst individual in the offspring. The iteration count is incremented by one, and the termination condition is checked. If the condition is not met, the process returns to the evaluation phase.

[0095] In step six, verifying the design results using a ray tracing model: The optimized scattering unit parameter file is loaded to construct a complete lens optical model. The lens model is coupled with the eye model, with the lens positioned 12 mm in front of the cornea and its optical axis coinciding with the eye's optical axis. Different field of view angles are simulated, from -30 degrees to +30 degrees, with a step size of 5 degrees. Different pupil diameters are simulated, from 2 mm to 7 mm, with a step size of 1 mm. Different illumination conditions are simulated: photopic vision corresponds to 500 lux ambient light, with the minimum pupil diameter; scotopic vision corresponds to 5 lux ambient light, with the maximum pupil diameter; and mesopic vision corresponds to 50 lux ambient light, with the median pupil diameter. For each combination of simulation conditions, 100,000 rays are traced to calculate the light intensity distribution on the retinal plane. Based on the light intensity distribution, the contrast modulation function is calculated: First, sinusoidal grating target objects with spatial frequencies of 0.5, 1, 2, 4, 8, 16, and 30 periods per degree are generated. Imaging is performed through the optical system, and the modulation degree of the grating after imaging is calculated. , where I max For maximum light intensity, I min To achieve minimum light intensity, the contrast modulation function is equal to the imaging modulation degree divided by the target object modulation degree, i.e. mobj The target modulation scheme is set. The defocus distribution is calculated as follows: For each retinal sampling point, its point spread function is calculated. The point spread function is obtained by weighted averaging of the light intensities of all light rays within a 10-micrometer radius around the point, with weights of a Gaussian function and a standard deviation of 5 micrometers. The centroid coordinates of the point spread function are calculated, and the Euclidean distance between the centroid coordinates and the coordinates of the ideal imaging point is the defocus amount at that point. The calculation results are compared with the target value. If any of the following conditions are met, it is determined that the target has not been met, triggering parameter iterative correction: Condition 1: The contrast modulation function of the central visual protection zone is lower than 0.9 at any field of view; Condition 2: The contrast modulation function of the peripheral myopia control zone is higher than 0.7 at any field of view; Condition 3: The absolute value of the defocus amount in the peripheral myopia control zone exceeds 0.5 diopters at any field of view.

[0096] The numerical calculation details of the ray tracing model are as follows: The retinal plane is discretized into a 600x600 grid with a grid spacing of 10 micrometers. For the point spread function calculation, for each grid point, all rays within a 50-micrometer radius are collected, and the ray weights are calculated using a two-dimensional Gaussian function with a standard deviation of 25 micrometers. For the defocus calculation, the centroid coordinates (x...)... c y c The calculation formula for ) is as follows:

[0097] Among them, I i Let x be the light intensity at the i-th sampling point. i y i () represents the coordinates of the i-th sampling point;

[0098] The formula for calculating the defocus amount d is as follows:

[0099] , where x0, y0 are the coordinates of the ideal imaging point.

[0100] When calculating the contrast modulation function, the spatial frequency f of the sinusoidal grating target object corresponds to the period T, which is equal to 360 divided by f micrometers. The calculation formula is as follows: The grating fringes are horizontal, and the phase is uniformly sampled at eight points from zero to two π. The k-th phase sampling point is... k = 0, 1, 2...7; tracing ten thousand rays at each phase point, the average light intensity of the corresponding area on the retina is calculated, resulting in eight light intensity values. The average light intensity at the Kth phase is: N represents the number of rays / samples;

[0101] By fitting a sine function and extracting the amplitude A and average value M, the calculation formula is as follows: ф0 represents the phase shift;

[0102] The modulation index m is calculated as follows: The contrast modulation function (MTF) is calculated as follows: m obj The target temperature regulation is set to 0.9. All calculations are performed on a parallel computing cluster using 256 computing cores, with a single complete simulation taking approximately four hours.

[0103] The parameter sensitivity analysis method in personalized adaptation is as follows: For indicators that do not meet the standards, calculate the partial derivatives of each optimization variable. For example, if the contrast in the central area is insufficient, calculate the partial derivative of the contrast with respect to the unit size. Using the finite difference method, increase the unit size by 0.1 micrometers, re-simulate and calculate the change in contrast. The partial derivative is equal to the change divided by 0.1. Select the three variables with the largest absolute values ​​of the partial derivatives as the fine-tuning targets. The fine-tuning step size is determined by the sign and magnitude of the partial derivatives: if the partial derivative is negative and the absolute value is large, decrease the variable value; the step size is equal to the target deviation divided by the absolute value of the partial derivative, but does not exceed the maximum step size allowed by the process. After fine-tuning, re-simulate and verify. If there is improvement, it is accepted; otherwise, halve the step size and retry. This process is iterated a maximum of five times. If it still does not meet the standards, it is determined that there is a conflict with the design boundary conditions, and physiological parameters need to be re-collected or the target value adjusted.

[0104] The scattering lens and its design method proposed in this invention achieve a fundamental leap from static homogenization to dynamic heterogenization. Its technical effects are reflected in: the contrast loss in the central visual protection zone is strictly controlled within 5%, and in clinical tests, the wearer's visual acuity remains above 1.0; the reduction in peripheral retinal contrast is stable within the range of 35% to 55%, and animal experiments show a 40% reduction in the rate of axial elongation; there is no optical step in the transition zone, and the subjective glare score is below level 2; the pupil adaptive modulation layer responds without perceptible delay when switching between light and dark; the displacement accuracy of the task mode switching module reaches 0.5 micrometers, and the defocus control error is less than 0.1 diopters; the personalized fitting success rate exceeds 95%, and the secondary correction rate is less than 5%. This solution provides a new generation of optical intervention tools for myopia prevention and control that combines high precision, high comfort, and high compliance.

[0105] The above description is merely a preferred embodiment of the present invention; it encompasses all the protection scope of the present invention. Any equivalent substitutions or modifications made by those skilled in the art within the technical scope disclosed in the present invention, based on the technical solutions and improved concepts of the present invention, should be covered within the protection scope of the present invention.

Claims

1. A scattering lens, characterized by: The scattering lens comprises a base optical lens, a heterogeneous scattering unit array, a pupil adaptive modulation layer, and a task mode switching module. The pupil adaptive modulation layer is composed of electrochromic material or liquid crystal polymer and is arranged above or below the heterogeneous scattering unit array. The task mode switching module is used to drive the heterogeneous scattering unit array to produce sub-micron displacement along the optical axis. The task mode switching module comprises a piezoelectric ceramic driver, a flexible hinge, a displacement amplification mechanism, a position sensor, and a control circuit. The piezoelectric ceramic driver has a maximum displacement of 20 microns and a driving voltage of 0-150 volts.

2. A scattering lens according to claim 1, wherein: The flexible hinge adopts a double parallelogram structure and has an amplification factor of 5, which amplifies the piezoelectric ceramic displacement to 100 microns.

3. A scattering lens according to claim 2, wherein: The output end of the displacement amplification mechanism is rigidly connected with the substrate of the heterogeneous scattering unit array.

4. A method of designing a scattering lens, characterized by: The position sensor is a capacitive displacement sensor. The control circuit outputs a driving voltage according to the visual task switching signal of the wearer. The heterogeneous scattering unit array is composed of a plurality of optical scattering units. The spatial distribution density, geometric shape, size parameter, and scattering intensity of the optical scattering units are differentiated according to the visual function requirements of the region. The arrangement of the optical scattering units adopts a non-periodic spatial coding strategy. In the central vision guarantee zone, the distribution density of the optical scattering units is less than 5 units per square millimeter, the unit size is less than 5 microns, and the scattering angle half-width is less than 3 degrees. In the peripheral myopia control zone, the distribution density of the optical scattering units is more than 50 units per square millimeter, the unit size is between 10 microns and 30 microns, and the scattering angle half-width is between 10 degrees and 25 degrees. In the transition function adjustment zone, the distribution density, size, and scattering angle parameters of the optical scattering units change continuously along the radial direction. In the central vision guarantee zone, a pseudo-random distribution mode is adopted. In the peripheral myopia control zone, a radial symmetric distribution mode is adopted. In the transition function adjustment zone, a weighted interpolation distribution mode is adopted. The scattering lens is applied to the scattering lens of claim 1 and comprises the following steps: Step one, obtaining the physiological parameter data set of the wearer, which includes the axial length, corneal curvature, pupil diameter, accommodation amplitude, and retinal sensitivity distribution map. Step two, establishing the light ray tracing model of the wearer's eyeball, which includes the optical parameters of the cornea, lens, vitreous body, and retina, and importing the physiological parameter data set for individual calibration. Step three, define the functional zone boundary of the lens, which is determined according to the dynamic range of the wearer's pupil diameter and the retinal functional zone map, and is divided into three concentric annular regions: central vision guarantee zone, transition function adjustment zone and peripheral myopia control zone; Step four, assign target scattering characteristic parameters to each functional zone, including scattering intensity, scattering angle distribution function and spatial frequency attenuation coefficient; Step five, based on the target scattering characteristic parameters, inversely optimize the geometric shape, size, distribution density and arrangement function of the heterogeneous scattering unit array in each functional zone; Step six, verify the design results by a ray tracing model, calculate the contrast modulation function and defocus distribution of retinal imaging under each field of view angle, if the deviation between the calculated results and the target values exceeds ten percent, return to the inverse optimization design step for parameter iteration correction; if the calculated results meet the preset tolerance, output the final heterogeneous scattering unit array structure parameter file for guiding lens manufacturing; Step seven, after the lens is manufactured, perform an adaptation test on the wearer through subjective visual quality evaluation and objective optical performance detection, the subjective visual quality evaluation includes visual acuity test, contrast sensitivity function measurement and glare discomfort threshold questionnaire, the objective optical performance detection includes wavefront aberration analysis, modulation transfer function scanning and scattered light distribution imaging, if the evaluation results do not meet the preset standard, fine-tune the local parameters of the heterogeneous scattering unit array according to the test data, and perform secondary correction on the lens through laser micromachining or local coating process.

5. The method of designing a scattering optic according to claim 4, wherein: The adaptation test and secondary correction in step seven include the following steps: A1, perform subjective visual quality evaluation: A1.1, after the wearer wears the lens, test the distance vision and near vision in front of the standard visual acuity chart, and record the visual acuity value corresponding to the smallest resolvable visual target; A1.2, use a contrast sensitivity tester to measure the contrast sensitivity function of the wearer at different spatial frequencies; A1.3, distribute a glare discomfort threshold questionnaire, the questionnaire contains multiple use scenarios, and the wearer grades the glare discomfort degree of each scenario on a five-point scale; A2, perform objective optical performance detection: A2.1, use a wavefront aberration instrument to measure the root mean square value of the total high-order aberration of the wearer's eyeball; A2.2, use a modulation transfer function scanner to measure the modulation transfer function value of the lens at different spatial frequencies, the spatial frequency range is zero to fifty cycles per millimeter, and the measurement direction is horizontal and vertical; A2.3, use a scattered light distribution imaging system to shoot the scattered light spot image of the lens under parallel light irradiation, and analyze the angular distribution uniformity and radial intensity attenuation curve of the spot; A3, judge the evaluation results: If any of the following conditions is met, it is determined to be substandard: condition one, the visual acuity in subjective evaluation is lower than zero point eight, condition two, the contrast sensitivity decreases by more than twenty percent at any frequency, condition three, the glare score is higher than four, condition four, the root mean square value of high-order aberration in objective detection is greater than zero point five microns, condition five, the modulation transfer function is lower than zero point three at ten cycles per millimeter, and the angular non-uniformity of the scattered light spot is greater than fifteen percent. A4, second modification: according to the parameter sensitivity analysis results of the unqualified items, fine-tune the local parameters of the heterogeneous scattering unit array, the fine-tuned parameters are used to modify the lens surface by laser micro-processing equipment, and after modification, the test is repeated until all indicators are qualified.

6. The method of designing a scattering optic of claim 5, wherein: The operation of fine-tuning the local parameters of the heterogeneous scattering unit array in step A4 includes the following cases:

1. When the central area contrast is insufficient, the unit size or distribution density in this area is reduced, 2. When the peripheral area scattering is insufficient, the unit size or distribution density is increased, 3. When the glare is serious, adjust the arrangement function to increase the angular randomness, 4. When the aberration is too large, optimize the unit curvature distribution; the fine-tuning step is determined according to the parameter sensitivity analysis results, and the iteration is performed at most five times.

7. The method of designing a scattering optic according to claim 4, wherein: The step of establishing the ray tracing model of the wearer's eyeball in step two includes the following operations: constructing a standard eyeball optical model including the anterior surface of the cornea, the posterior surface of the cornea, the aqueous humor, the anterior surface of the lens, the posterior surface of the lens, the vitreous body and the retina, the measured eye axis length is used as the total length of the model, the thickness of each optical medium is scaled according to the proportion, the corneal curvature measurement value is used to replace the curvature radius of the anterior surface of the cornea in the model, according to the dynamic range of the pupil diameter, a variable diaphragm is set in the model, the aperture is dynamically adjusted according to the simulated lighting conditions, the accommodation amplitude value is used to adjust the curvature radius of the anterior surface of the lens, a linear mapping relationship between the accommodation state and the lens deformation is established, and the retinal sensitivity distribution map is used as a weight matrix for subsequent area weighting in the contrast modulation function calculation.

8. The method of designing a scattering optic of claim 4, wherein: The step of defining the functional partition boundary of the lens in step three includes the following operations: determining the outer boundary radius of the central vision guarantee area according to the maximum value of the wearer's pupil diameter under bright light conditions, which is equal to the maximum pupil radius plus a two-millimeter safety margin, determining the inner boundary radius of the peripheral myopia control area according to the position where the retinal sensitivity drops to fifty percent of the peak value of the fovea, and the transition function adjustment area is located between the outer boundary of the central vision guarantee area and the inner boundary of the peripheral myopia control area. The functional partition boundary is stored in polar form, and each boundary is defined by three hundred and sixty radial sampling points with one degree interval.

9. The method of designing a scattering optic of claim 4, wherein: In step four: the target scattering intensity of the central vision guarantee area is set to zero point zero five to zero point one, the target scattering angle half width is set to one degree to three degrees, the target spatial frequency attenuation coefficient is set to zero point nine five to zero point nine nine, the target scattering intensity of the peripheral myopia control area is set to zero point three to zero point six, the target scattering angle half width is set to ten degrees to twenty five degrees, and the target spatial frequency attenuation coefficient is set to zero point four to zero point seven. The target parameters of the transition function adjustment area are linearly interpolated along the radial direction, and the interpolation function is linear weighted average, and the weight coefficient is determined by the distance ratio of the current radial position to the partition boundary.

10. The method of designing a scattering optic of claim 4, wherein: In the operation of optimizing the geometry, size, distribution density and arrangement function of the heterogeneous scattering unit array in each functional subzone of the fifth step, a multi-objective genetic algorithm is used for parameter optimization, and the fitness function of the multi-objective genetic algorithm is composed of three weighted items: the first item is the contrast ratio retention rate of the central vision guarantee zone, the weight coefficient is zero point six; the second item is the contrast ratio decay rate of the peripheral myopia control zone, the weight coefficient is zero point three; the third item is the gradient smoothness index of the transition function adjustment zone, the weight coefficient is zero point one, the population size of the multi-objective genetic algorithm is set to five hundred, the upper limit of the iteration number is two thousand generations, the crossover probability is zero point eight, and the mutation probability is zero point zero five.

11. The method of designing a scattering optic of claim 4, wherein: In the step of verifying the design results by the light tracing model in the sixth step: the simulation field of view angle range covers negative thirty degrees to positive thirty degrees, the simulation pupil diameter range covers two millimeters to seven millimeters, the simulation lighting conditions include three states of bright, intermediate and dark, the calculation of the contrast modulation function is based on a sinusoidal grating target, the spatial frequency covers zero point five cycles per degree to thirty cycles per degree, the calculation of the defocus amount distribution is based on the centroid offset of the point spread function, the sampling point density is one hundred per square millimeter, and when any of the following conditions is met, it is determined that the standard is not met: condition one, the contrast modulation function of the central vision guarantee zone is less than zero point nine under any field of view angle, condition two, the contrast modulation function of the peripheral myopia control zone is greater than zero point seven under any field of view angle, and condition three, the absolute value of the defocus amount of the peripheral myopia control zone exceeds zero point five diopters under any field of view angle.

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