Spectacle lens and design method thereof

Abstract

The invention discloses a spectacle lens and a design method thereof. The spectacle lens comprises a lens body, wherein the lens body comprises a first surface arranged towards the retina of a human eye; the lens body is provided with an optical center which coincides with the geometric center of the first surface. The first surface comprises a retina refraction area, a retina periphery refraction area and a refraction correction area which are sequentially arranged from the optical center to the edge of the lens body; the retinal diopter, the peripheral retina diopter, and the diopter correction region are disposed around the optical center, respectively, and cooperate together to intervene in retinal imaging quality within the pupil range. According to the retina peripheral characteristics of the wearer, the micro-structure lens more adaptive to the retina of the human eye is designed, the retina peripheral diopter of the human eye can be more accurately obtained, and the progress of ametropia is efficiently intervened according to the characteristics of the retina peripheral diopter of the human eye.

Description

Technical Field

[0001] The present application belongs to the field of ophthalmic optics technology, and specifically relates to a microstructured spectacle lens based on retinal peripheral refractive topography data and a design method thereof. Background Art

[0002] The peripheral area of the retina, as a defocus control area, can change the growth and refractive state of the human eye. Specifically, peripheral hyperopic defocus will lead to axial myopia, and peripheral myopic defocus will even lead to axial hyperopia. The peripheral retinal data is obtained through human eye measurement equipment, and the corresponding refractive power data is generated, which helps to achieve a more accurate and personalized correction method to select the best refractive error management method based on the actual situation of the wearer. At present, the peripheral defocus amount of traditional defocus lenses is usually only set on the microstructure of the lens, such as using a fixed or progressive defocus amount setting, and there is no more accurate and personalized one-to-one matching of the peripheral retinal refractive power data and the lens for each wearer, which may lead to differences in the effect of suppressing the further development of refractive errors. Therefore, how to achieve personalized suppression of refractive errors according to the peripheral conditions of the human eye retina is of great significance. Summary of the Invention

[0003] Purpose of the invention: The embodiments of the present application provide a spectacle lens and a design method thereof, aiming to design a microstructured lens that is more suitable for the human retina based on the peripheral characteristics of the wearer's retina. This method can more accurately obtain the peripheral refractive power of the human retina and efficiently intervene in the further progression of refractive errors based on its characteristics.

[0004] Technical solution: A spectacle lens of the present application comprises: A lens body, the lens body comprising a first surface disposed toward a retina of a human eye; the lens body having an optical center, the optical center coinciding with a geometric center of the first surface; The first surface includes a retinal refractive zone, a retinal peripheral refractive zone, and a refractive correction zone arranged in sequence from the optical center to the edge of the lens body; the retinal refractive zone, the retinal peripheral refractive zone, and the refractive correction zone are respectively arranged around the optical center and cooperate to adjust the retinal imaging quality within the pupil range; Among them, the retinal refractive area is used to determine the optical performance of the lens body according to the refractive power of the human retina; the retinal peripheral refractive area is used to classify and compensate the first surface according to the refractive condition of the human retina periphery; the refractive correction area is used to correct the compensation to correct the refractive power of the human retina periphery.

[0005] In some embodiments, the lens body further comprises a second surface disposed away from the retina of a human eye; the second surface comprises a central optical zone, a microstructure zone, and a first edge zone disposed sequentially from the optical center toward the edge of the lens body; the central optical zone, the microstructure zone, and the first edge zone are respectively disposed around the optical center; The spectacle lens further comprises a plurality of microstructures, which are arranged in the microstructure area and are used to cooperate with the lens body to form a stimulation signal.

[0006] In some embodiments, the maximum distance from the optical center to the edge of the retinal refractive zone is l 1 mm, with a maximum distance R1 mm from the optical center to the edge of the central optical zone, satisfying: ; Where C1 is the radial coefficient and 0.1≤C1<0.3, f e The equivalent focal length of the human eye; f l is the equivalent focal length of the lens; D is the lens diameter.

[0007] In some embodiments, the maximum distance from the optical center to the edge of the retinal peripheral refractive zone is l 2 mm, and a maximum distance R2 mm from the optical center to the edge of the microstructure area, satisfying: ; Where C2 is the radial coefficient and 0.2≤C2<0.5, f e The equivalent focal length of the human eye; f l is the equivalent focal length of the lens; D is the lens diameter.

[0008] In some embodiments, the maximum distance from the optical center to the edge of the dioptric correction zone is l 3 mm, a maximum distance R3 mm from the optical center to the edge of the first edge zone satisfies: ; in, f e The equivalent focal length of the human eye; f l is the equivalent focal length of the lens; D is the lens diameter; ∆ x It is the maximum offset when the wearer wears the glasses, ranging from 2 to 5 mm.

[0009] In some embodiments, among the plurality of microstructures, at least two of the microstructures are connected to each other; or The plurality of microstructures are spaced apart from each other; Wherein, the microstructure is selected from at least one of a lens and a cylindrical lens.

[0010] In some embodiments, the retinal peripheral refractive zone has a plurality of first sub-areas, and the refractive correction zone has a plurality of second sub-areas; the first sub-areas are adjacent to the second sub-areas; the first sub-areas have a first opening disposed toward an edge of the lens body; and the second sub-areas have a second opening disposed toward an edge of the lens body. Among them, the first opening of at least one of the first sub-areas is set toward the nasal side, and the first opening of at least one of the first sub-areas is set toward the temporal side; the second opening of at least one of the second sub-areas is set toward the nasal side, and the second opening of at least one of the second sub-areas is set toward the temporal side.

[0011] In some embodiments, the peripheral refractive zone of the retina is divided into equal or non-equal angles around the optical center to obtain the first sub-area; the refractive correction zone is divided into equal or non-equal angles around the optical center to obtain the second sub-area.

[0012] In some embodiments, when the peripheral refractive area of the retina is divided into non-equiangular areas, the first opening of the first sub-area disposed toward the temporal side has a first angle at the optical center. The first opening of the first sub-region disposed toward the nose side has a second angle at the optical center ,satisfy: .

[0013] In some embodiments, when the refractive correction area is divided into non-equal angles, the second opening of the second sub-area disposed toward the temporal side has a third angle at the optical center. The second opening of the second sub-region disposed toward the nose side has a fourth angle at the optical center ,satisfy: .

[0014] In some embodiments, the retinal peripheral refractive zone and / or the refractive correction zone are selected from any one of a circle, an ellipse, a regular polygon, and an irregular shape.

[0015] In some embodiments, the present application further provides a method for designing eyeglass lenses, comprising the following steps: Obtain human retinal refractive data and divide the refractive data distribution into regions; Based on the area division, a diopter mapping relationship between the retina and the first surface of the lens body is established, and design parameters are obtained. Based on the design parameters, a retinal refractive zone, a retinal peripheral refractive zone, and a refractive correction zone are sequentially arranged on the first surface from the optical center of the lens body to the edge of the lens body; wherein the first surface is arranged toward the retina of the human eye; Providing a lens body and obtaining the prescription power of the lens body; According to the prescription diopter, the surface shapes of the retinal refractive zone, the retinal peripheral refractive zone and the refractive correction zone are designed to obtain a microstructured lens; The retinal refractive zone, the retinal peripheral refractive zone and the refractive correction zone are respectively arranged around the optical center and cooperate together to intervene in the retinal imaging quality within the pupil range.

[0016] In some embodiments, after the step of providing the lens body, the method further comprises: The second surface of the lens body is designed so that a central optical zone, a microstructure zone, and a first edge zone are sequentially arranged on the second surface from the optical center of the lens body to the edge of the lens body; wherein the central optical zone, the microstructure zone, and the first edge zone are respectively arranged around the optical center, and the second surface is arranged away from the retina of a human eye; A plurality of microstructures are provided in the microstructure area for cooperating with the lens body to form a stimulation signal.

[0017] In some embodiments, the steps of providing a lens body and obtaining a prescription power of the lens body further include: Get the upper and lower limits of the prescription light range; Calculate the vector height corresponding to the upper limit and lower limit respectively; Fit the Zernike polynomial in Fringe mode to the arrow height and invert its fitting coefficients; Use the fitting coefficient to calculate the corresponding RMS value, and take the minimum corresponding luminosity in the RMS value as the prescribed luminosity; The expression of RMS value is: ; Where c j is the fitting coefficient, N represents the number of second-order aberration terms, ranging from 3 to 5.

[0018] In some embodiments, in the step of obtaining retinal refractive data of the human eye and dividing the refractive data distribution into regions, the region division includes a fovea area, a first detection area, and a second detection area, which are arranged in sequence from the center of the retina to the edge of the retina. The fovea area, the first detection area, and the second detection area are respectively arranged around the center of the retina.

[0019] In some embodiments, the diopter mapping relationship between the retina and the first surface of the lens body is expressed as: ; Where, l represents the design parameters; L The distance between the lens and eyeball is 5 mm ≤ L ≤ 15 mm; s 1 is the distance from the pupil to the center of eyeball rotation, s 2 is the distance from the center of the retinal macula to the center of eyeball rotation, and it satisfies s 1+ s 2=24; ∆R(θ,d) is the correction term and ranges from -2.5 mm to 2.5 mm, θ is the half field angle and 0°≤θ≤50°, d is the entrance pupil diameter and 2 mm≤d≤6 mm; r The maximum distance between the edge of any one of the foveal area, the first detection area, and the second detection area and the center of the retina.

[0020] In some embodiments, the step of designing the surface shapes of the retinal refractive zone, the retinal peripheral refractive zone, and the refractive correction zone according to the prescription diopter to obtain a microstructured lens further includes: respectively calculating the diopters of the retinal refractive zone, the retinal peripheral refractive zone, and the refractive correction zone to obtain the face shape corresponding to each zone, and then smoothing the first surface to obtain a microstructured spectacle lens; The calculation expression of the refractive power of the retinal refractive zone is: ;in, P target is the prescription light intensity, S actual It is the retinal astigmatism data of human eyes; The calculation expression of the diopter of the peripheral refractive zone of the retina is: ;in, P target is the prescribed light intensity; To fit the retinal refractive data to obtain the Zernike polynomial in the standard mode; L N is the number of fitting terms and L N ≥171; is the correlation coefficient; The calculation expression of the diopter of the refractive correction area is: ; Wherein, α represents the direction angle corresponding to the minimum value of the refractive power change rate in any direction; β represents the direction angle corresponding to the maximum value of the refractive amplitude difference in any direction angle; D1 and D4 both represent the refractive power of the area where the α direction angle is located; D3 represents the refractive power of the entire first surface; D2 and D5 represent the refractive power of the area where the β direction angle is located; where 0.5≤D1≤3, 0.25≤D2≤1.25, 0.5≤D3≤3.0, 0.5≤D4≤2.5, D5=mD4, m is a constant and 0 <m<1。

[0021] Beneficial Effects: Compared to existing technologies, this application fully utilizes the measurement results of the human retinal peripheral area using human eye measurement equipment. By establishing a lens-eye imaging system model and employing ray tracing methods, it maps the relationship between the human retina and the refractive power gradient of the first surface of the lens body, thereby designing microstructured lenses that account for individual differences. Examples demonstrate that this method, under the same conditions for the microstructured surfaces, can achieve a more effective management effect in suppressing the further development of refractive error, providing a new approach for the optimized design of microstructured lenses. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] In order to more clearly illustrate the technical solutions in the embodiments of the present application, the following briefly introduces the drawings required for use in the description of the embodiments. Obviously, the drawings described below are only some embodiments of the present application. For those skilled in the art, other drawings can be obtained based on these drawings without creative work.

[0023] Figure 1 A schematic diagram of the first surface structure of the microstructured eyeglass lens provided in an embodiment of the present application; Figure 2 A schematic diagram of the second surface structure of the microstructured eyeglass lens provided in an embodiment of the present application; Figure 3 A schematic diagram of the human eye retinal refractive condition detection area provided in an embodiment of the present application; Figure 4 A planar projection diagram of the mirror-eye imaging system provided in this application; Figure 5 Schematic diagram of the optical path of light from the back surface of the lens through the pupil to the retina under the three fields of view provided in this application; Figure 6 A schematic diagram of the refractive power divisions on the back surface of the human eye retinal refractive power mapping lens provided in this application; Figure 7 Human eye retinal detection data provided in the embodiments of this application; Figure 8 A schematic diagram of the basic surface shape of the first surface provided in an embodiment of the present application; Figure 9 A contour map of the first surface astigmatism provided in an embodiment of the present application; Figure 10 A simulation diagram of the lens-eye imaging system provided in an embodiment of the present application; Figure 11 MTF curves of the two microstructured surfaces provided in the embodiments of this application under the same simulation conditions; Figure 12 A schematic diagram of non-equiangular division of the peripheral refractive zone of the retina provided in this embodiment; Figure 13 for Figure 12 A partial enlarged schematic diagram of a part in FIG; Figure 14 A schematic diagram of dividing the refractive correction area into non-equal angles provided in this embodiment; Figure 15 A schematic diagram showing that the peripheral refractive area of the retina provided in this embodiment is a regular octagon; Figure markings, 1-lens body, 2-microstructure, 10-optical center, 11-first surface, 12-second surface, 111-retinal refractive zone, 112-retinal peripheral refractive zone, 113-refractive correction zone, 121-central optical zone, 122-microstructure zone, 123-first edge zone, 30-retinal center, 31-retinal edge, 301-retinal fovea area, 302-first detection area, 303-second detection area, 1121-first sub-area, 1122-first opening, 1131-second sub-area, 1132-second opening. DETAILED DESCRIPTION

[0024] The following will be combined with the drawings in the embodiments of the present application to clearly and completely describe the technical solutions in the embodiments of the present application. Obviously, the embodiments described are only part of the embodiments of the present application, not all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by those skilled in the art without making creative efforts are within the scope of protection of this application.

[0025] In the description of this application, it should be understood that the terms "upper," "lower," "top," "bottom," "inner," "outer," etc., indicating orientations or positional relationships, are based on the orientations or positional relationships shown in the accompanying drawings and are intended only to facilitate the description of this application and simplify the description. They do not indicate or imply that the devices or elements referred to must have a specific orientation, be constructed and operate in a specific orientation, and therefore should not be understood as limiting this application. In the description of this application, "plurality" means two or more, and "at least one" means one, two, or more than two, unless otherwise expressly and specifically defined.

[0026] See also Figure 1and Figure 2 A spectacle lens comprises: a lens body 1, the lens body 1 including a first surface 11 disposed toward the retina of a human eye; the lens body 1 having an optical center 10, the optical center 10 coinciding with the geometric center of the first surface 11; the first surface 11 including a retinal refractive zone 111, a retinal peripheral refractive zone 112, and a refractive correction zone 113 disposed sequentially from the optical center 10 toward the edge of the lens body 1; the retinal refractive zone 111, the retinal peripheral refractive zone 112, and the refractive correction zone 113 are respectively disposed around the optical center 10 and cooperate to adjust the retinal imaging quality within the pupil range; Among them, the retinal refractive zone 111 is used to determine the optical performance of the lens body 1 according to the refractive power of the human retina; the peripheral retinal refractive zone 112 is used to classify and compensate the first surface 11 according to the peripheral refractive conditions of the human retina; the refractive correction zone 113 is used to correct the compensation to correct the peripheral refractive power of the human retina and make the refractive power distribution of the first surface 11 more matched with the peripheral refractive power distribution of the human retina.

[0027] It can be understood that in the microstructured lens of this embodiment, since the first surface 11 is provided with a retinal refractive zone 111, a peripheral retinal refractive zone 112, and a refractive correction zone 113, the retinal refractive zone 111 is responsible for providing precise central vision correction based on the foveal diopter, the peripheral retinal refractive zone 112 establishes a dynamic compensation gradient field to regulate the peripheral defocus distribution, and the refractive correction zone 113 is used to optimize the refractive distribution. By dividing the lens surface into the retinal refractive zone 111, the peripheral retinal refractive zone 112, and the refractive correction zone 113, and assigning independent functions based on the refractive data of the human retina and peripheral areas, a three-level optical control system of "basic correction - classified compensation - dynamic correction" is achieved. This design, for the first time, incorporates the refractive differences between the center and periphery of the retina into lens surface optimization, improving the match between the lens's refractive power distribution and the actual bio-optical properties of the human eye, significantly enhancing the personalized adaptability of myopia control. The peripheral refractive zone 112 of the retina utilizes microstructural classification compensation to create a progressive defocus gradient in the centrifugal direction (from the optical center to the periphery). The refractive correction zone 113 further corrects the wavefront aberrations of the compensated face shape. This synergistic effect improves the lens' modulation transfer function within the pupil, effectively reducing glare and visual fatigue. The primary focus established in the central zone and the defocus gradient in the peripheral zone create a "dual-focus zone" structure. Within a pupil diameter range of 2-6mm, defocus compensation is significantly increased while reducing the rate of axial eye growth. This structure, through regional optical property modulation, achieves multi-level visual optimization, from geometric optics to neural adaptation, providing a new engineering solution for inhibiting the progression of refractive error.

[0028] Furthermore, the refractive power of the first surface 11 is more closely matched with the peripheral refractive power of the human eye retina, which can be understood as allowing a certain error range such as plus or minus 0.25 diopters, plus or minus 0.50 diopters, etc. The trend of the peripheral refractive power distribution of the retina is roughly the same as the trend designed on the first surface.

[0029] In some embodiments, the lens body 1 also includes a second surface 12 arranged away from the retina of the human eye; the second surface 12 includes a central optical zone 121, a microstructure zone 122 and a first edge zone 123 arranged in sequence from the optical center 10 to the edge of the lens body 1; the central optical zone 121, the microstructure zone 122 and the first edge zone 123 are respectively arranged around the optical center 10; the lens also includes a plurality of microstructures 2, and the plurality of microstructures 2 are arranged in the microstructure zone 122, which are used to cooperate with the lens body 1 to form a stimulation signal.

[0030] It is understood that the present application also designs a central optical zone 121, a microstructure zone 122, and a first edge zone 123 on the second surface 12, which is located opposite the first surface 11. The microstructure zone 122 of the second surface 12 may generate dynamic light signals by forming a microlens array or prism structure, stimulating the retinal periphery and thereby slowing axial length growth. Simultaneously, the central optical zone 121 ensures central vision, while the edge zone may address aberrations or transitions. This can enhance the further development of the refractive array, improve visual quality, expand personalized adaptation, and balance dynamic stimulation adjustment. Furthermore, the first surface 11 handles refractive compensation and correction, while the second surface 12 provides additional stimulation signals. The combination of the two may complement each other in terms of defocus control, aberration correction, and dynamic response. The refractive correction zone 113 of the first surface 11 and the edge zone of the second surface 12 jointly influence wavefront aberrations, reducing the MTF value. The synergy between the first and second surfaces 11, 12 can achieve better optical performance integration, such as further enhancing the stimulation signal. Therefore, the microstructured eyeglass lens of this embodiment achieves the synergistic effect of defocus stimulation efficiency and visual quality, and at the same time provides a physical carrier for personalized parameter adjustment.

[0031] In some embodiments, the maximum distance from the optical center 10 to the edge of the retinal refractive zone 111 is l 1 mm, and a maximum distance R1 mm from the optical center 10 to the edge of the central optical zone 121, satisfying: ; Where C1 is the radial coefficient and 0.1≤C1<0.3, f e The equivalent focal length of the human eye; f l is the equivalent focal length of the lens; D is the lens diameter.f e Usually 17mm is used; f l Defined as the reciprocal of the wearer's corrected diopter.

[0032] In some embodiments, the maximum distance from the optical center 10 to the edge of the retinal peripheral refractive zone 112 is l 2 mm, and a maximum distance R2 mm from the optical center 10 to the edge of the microstructure region 122, satisfying: ; Where C2 is the radial coefficient and 0.2≤C2<0.5, f e The equivalent focal length of the human eye; f l is the equivalent focal length of the lens; D is the lens diameter. f e Usually 17mm is used; f l Defined as the reciprocal of the wearer's corrected diopter.

[0033] In some embodiments, the maximum distance from the optical center 10 to the edge of the dioptric correction zone 113 is l 3 mm, and a maximum distance R3 mm from the optical center 10 to the edge of the first edge region 123 satisfies: ; in, f e The equivalent focal length of the human eye; f l is the equivalent focal length of the lens; D is the lens diameter; ∆x is the maximum offset when the wearer wears the glasses, ranging from 2 to 5 mm.

[0034] In some embodiments, at least two microstructures 2 among the plurality of microstructures 2 are connected to each other; or, the plurality of microstructures 2 are spaced apart from each other; wherein the microstructures 2 are selected from at least one of lenses and lenticular lenses.

[0035] In some embodiments, when the microstructure is selected from a lens, the surface shape of the lens is selected from at least one of a spherical surface, an aspherical surface, a cylindrical surface, a conical surface, and a free-form surface.

[0036] In some embodiments, the term "optical center 10" refers to the axially symmetrical center point of the lens body 1, and can also be understood as the symmetrical center point of the lens body 1 along the optical axis. Light will not be deflected or refracted when passing through the optical center 10, that is, the propagation direction of the light beam will not deviate from the axis. The term "geometric center" refers to the symmetrical center point of the shape or boundary of the lens body 1, which is determined based on the geometric properties of the lens body 1. In this embodiment, the optical center 10 coincides with the geometric center of the first surface 11, and light propagating through the optical center 10 will not be deflected or refracted, which helps to maintain the collimation of the light and the stability of the focus, thereby simplifying the structural design of the lens.

[0037] In some embodiments, see further Figure 12 and Figure 13 The retinal peripheral refractive zone 112 has a plurality of first sub-areas 1121, and the refractive correction zone 113 has a plurality of second sub-areas 1131; the first sub-areas 1121 and the second sub-areas 1131 are adjacent to each other; the first sub-area 1121 has a first opening 1122 disposed toward the edge of the lens body 1; and the second sub-area 1131 has a second opening 1132 disposed toward the edge of the lens body 1; Among them, the first opening 1122 of at least one of the first sub-areas 1121 is set toward the nasal side, and the first opening 1122 of at least one of the first sub-areas 1121 is set toward the temporal side; the second opening 1132 of at least one of the second sub-areas 1131 is set toward the nasal side, and the second opening 1132 of at least one of the second sub-areas 1131 is set toward the temporal side.

[0038] It can be understood that by providing first sub-area 1121 and second sub-area 1131, differential compensation can be achieved for the asymmetric refractive distribution in the peripheral retina of the human eye. Adjacent first sub-areas 1121 and second sub-areas 1131 form a gradient distribution network for defocus energy, enabling the defocus energy to more accurately match the refractive requirements of each quadrant of the peripheral retina. The specific orientation of first opening 1122 and second opening 1132 ensures a smooth transition of defocus contributions from different sub-areas as the eye moves, effectively reducing dynamic visual interference.

[0039] It should be noted that the "multiple" in the multiple first sub-areas 1121 or the multiple second sub-areas 1131 specifically refers to a number greater than or equal to four. This ensures that the sub-areas in the retinal peripheral refractive zone 112 or the refractive correction zone 113 cover at least the nasal side, the temporal side, and the area between the nasal and temporal sides. The nasal side refers to the area on the lens closest to the wearer's nose when wearing the glasses; the temporal side refers to the area on the lens closest to the wearer's temple when wearing the glasses. For a right-eye lens, the nasal side is on the left and the temporal side is on the right; for a left-eye lens, the nasal side is on the right and the temporal side is on the left.

[0040] In some embodiments, the retinal peripheral refractive area 112 is divided into equal or non-equal angles around the optical center 10 to obtain a first sub-area 1121; the refractive correction area 113 is divided into equal or non-equal angles around the optical center 10 to obtain a second sub-area 1131. Figure 12 In the figure, the peripheral refractive zone 112 of the retina is divided into non-equiangular areas; Figure 14 Of course, the retinal peripheral refractive zone 112 and the refractive correction zone 113 can also be divided into non-equal angles or equal angles at the same time (e.g. Figure 1 ).

[0041] It can be understood that by dividing the retinal peripheral refractive zone 112 and refractive correction zone 113 into sub-areas around the optical center 10, targeted optical compensation can be performed based on the differences in the defocus characteristics of the retina at different locations. Equal-angle division ensures uniform defocus distribution in all locations, making visual transitions smoother during eye movement. Equal-angle division can be at angles of 20°, 30°, 40°, 45°, 60°, 90°, etc.; while non-equal-angle division can enhance defocus intervention at specific locations.

[0042] In some embodiments, see further Figure 12 When the retinal peripheral refractive area 112 is divided into non-equal angles, the first opening 1122 of the first sub-area 1121 disposed toward the temporal side has a first angle at the optical center 10. The first opening 1122 of the first sub-region 1121 disposed toward the nose side has a second angle at the optical center 10. ,satisfy: .

[0043] It is understandable that when This division method is more consistent with the physiological principles of the human eye when the temporal side has a larger field of view, which corresponds to a wider distribution angle of retinal diopter. The differentiated unequal division method in this range extracts the average diopter and defocus information of the retinal periphery that is consistent with the actual perception of the human eye, while avoiding fusion interference caused by excessive differences between the nasal and temporal sides.

[0044] In some embodiments, see further Figure 14 When the refractive correction area 113 is divided into non-equal angles, the second opening 1132 of the second sub-area 1131 disposed toward the temporal side has a third angle at the optical center 10. The second opening 1132 of the second sub-region 1131 disposed toward the nose side has a fourth angle at the optical center 10. ,satisfy: .

[0045] It is understandable that when When the range is within the range of 0.05, the defocus information caused by the unequal division can be better corrected while satisfying the division of the peripheral area of the retina, and the defocus effect of the edge area can be effectively corrected.

[0046] In some embodiments, the retinal peripheral refractive zone 112 and / or the refractive correction zone 113 are selected from any one of a circle, an ellipse, a regular polygon, and an irregular shape. Regular polygons may include regular triangles, squares, regular pentagons, regular hexagons, regular octagons, etc. For example, see Figure 15 , the retinal peripheral refractive zone 112 is a regular octagon.

[0047] In some embodiments, the present application further provides a method for designing a microstructured lens based on retinal peripheral refractive data, comprising the following steps: Obtain human eye retinal refractive data and divide the refractive data distribution into regions; Based on the regional divisions, a diopter mapping relationship between the retina and the first surface 11 of the lens body 1 is established, and design parameters are obtained. Based on the design parameters, a retinal refractive zone 111, a retinal peripheral refractive zone 112, and a refractive correction zone 113 are sequentially arranged on the first surface 11 from the optical center 10 of the lens body 1 toward the edge of the lens body 1; wherein the first surface 11 is arranged toward the retina of the human eye; Providing a lens body 1 and obtaining the prescription power of the lens body 1; According to the prescription diopter, the surface shapes of the retinal refractive zone 111, the retinal peripheral refractive zone 112 and the refractive correction zone 113 are designed to obtain a microstructured lens; The retinal refractive zone 111 , the retinal peripheral refractive zone 112 and the refractive correction zone 113 are respectively arranged around the optical center 10 and cooperate with each other to intervene in the retinal imaging quality within the pupil range.

[0048] It is understandable that the method of the present application fully utilizes the measurement results of the peripheral area of the human retina by human eye measurement equipment. By establishing a lens-eye imaging system model and using a ray tracing method, the relationship between the human retina and the refractive power gradient of the first surface 11 of the lens is mapped, thereby designing the optimal microstructure lens that takes into account individual differences. The examples show that this method can achieve a more effective management effect on the further development of refractive error under the condition that the surface where the microstructure is located is the same, providing a new approach for the optimized design of microstructure lenses. By obtaining the refractive data of the human retina and performing regional division, a refractive power mapping relationship between the retina and the first surface 11 is established, so that the division of the retinal refractive zone 111, the peripheral refractive zone 112, and the refractive correction zone 113 strictly matches the retinal bio-optical characteristics. This method realizes for the first time a full-link closed-loop design from "data acquisition-region division-face generation", reducing the adaptation error of the lens refractive distribution and significantly improving the accuracy of myopia control. Furthermore, based on the prescribed power of the lens body 1, a basic corrective profile is generated in stages for the retinal refractive zone 111, a classified compensation profile for the peripheral refractive zone 112, and an optimized profile for the refractive correction zone 113, forming a three-level superposition of "correction-compensation-correction" optical model. This design transcends the limitations of traditional lenses, which only superimpose fixed defocus values, reducing the coupling error between the prescribed power and the peripheral defocus parameters. It also ensures the functional decoupling of central vision correction and peripheral defocus intervention, preventing interference with optical performance.

[0049] In some embodiments, after the step of providing the lens body 1, the method further includes: The second surface 12 of the lens body 1 is designed to have a central optical zone 121, a microstructure zone 122, and a first edge zone 123 arranged sequentially from the optical center 10 of the lens body 1 toward the edge of the lens body 1. The central optical zone 121, the microstructure zone 122, and the first edge zone 123 are respectively arranged around the optical center 10, and the second surface 12 is positioned away from the retina of the human eye. A plurality of microstructures are provided in the microstructure area 122 for cooperating with the lens body 1 to form a stimulation signal.

[0050] In some embodiments, in the step of obtaining retinal refractive data of the human eye and dividing the refractive data distribution into regions, the regional division includes a retinal fovea region 301, a first detection region 302, and a second detection region 303 arranged in sequence from the retinal center 30 to the retinal edge 31, and the retinal fovea region 301, the first detection region 302, and the second detection region 303 are respectively arranged around the retinal center 30.

[0051] See also Figure 3 , set the rectangular coordinate system of the retinal area, where x The axis is the straight line where 0° (180°) is located, and the direction is horizontal to the right; y The axis is the straight line of 90° (270°), the direction is vertically upward, the coordinate origin is O, and it is defined as the fovea area of the retina.

[0052] The retinal area contains different detection areas, including: The retinal fovea area 301 is located within the detection area with a radius of r1, and the retinal fovea area 301 is within the radius; Retinal Peripheral Detection Areas: The areas between radius r1 and r2, and between radius r2 and r3, are defined as first detection area 302 and second detection area 303, respectively. Preferably, first detection area 302 and second detection area 303 are equally divided at 45° intervals, with each bisecting line having a corresponding axial position distribution, where the line outside the brackets represents the right eye's axial position, and the line within the brackets represents the left eye's axial position. By establishing multiple detection areas within different retinal regions, this method enables more accurate detection and analysis of the retinal periphery.

[0053] Establish the imaging system model of lens and human eye, as shown in the attached Figure 4 and Figure 5 As shown in Figure 1, light passes through the lens and the pupil to form an image on the retina. To more accurately characterize the mapping between the retinal area and the lens surface, the following formula is used for approximate calculation: ; Where, l represents the design parameters; L The distance between the lens and eyeball is 5 mm ≤ L ≤ 15 mm; s 1 is the distance from the pupil to the center of eyeball rotation, s 2 is the distance from the center of the retinal macula to the center of eyeball rotation, and it satisfies s 1+ s 2=24; ∆R(θ,d) is the correction term and ranges from -2.5 mm to 2.5 mm, θ is the half field angle and 0°≤θ≤50°, d is the entrance pupil diameter and 2 mm≤d≤6 mm; rIt represents the maximum distance between the edge of any one of the retinal fovea area 301, the first detection area 302 and the second detection area 303 and the retinal center 30. Therefore, based on the retinal measurement data and using the above formula, the range parameters of the wearer in the three areas of the lens surface are calculated respectively. l 1. l 2 and l 3.

[0054] In some embodiments, the steps of providing the lens body 1 and obtaining the prescription power of the lens body 1 further include: Get the upper and lower limits of the prescription light range; Calculate the vector height corresponding to the upper limit and lower limit respectively; Fit the Zernike polynomial in Fringe mode to the arrow height and invert its fitting coefficients; Use the fitting coefficient to calculate the corresponding RMS value, and take the minimum corresponding luminosity in the RMS value as the prescribed luminosity; The expression of RMS value is: ; Where c j is the fitting coefficient, N represents the number of second-order aberration terms, ranging from 3 to 5.

[0055] Furthermore, the lens body 1 often uses a single-focus lens as the basic surface shape, and the measurement data obtained by the measuring device deviates from the actual prescription diopter. Desirable or The specific way to obtain the value of one of the following is as follows: (1) Calculate separately and The corresponding vector heights z1 and z2; (2) Fit the Zernike polynomials in Fringe mode to the vector heights z1 and z2 and invert the fitting coefficients c 1j and c 1j ; (3) Use the fitting coefficient to calculate the corresponding RMS value and take the corresponding luminosity with the smallest RMS as the prescribed luminosity.

[0056] The upper limit of the prescription light intensity calculation is , the lower limit is ; Measure photometric data for the retina.

[0057] The sag corresponding to the prescription luminosity is expressed as: ; Where, is the coordinate of the center of curvature corresponding to each point on the retina, and its calculation formula is as follows: .

[0058] To determine a more accurate prescription photometry, a Zernike polynomial is fitted in Fringe mode on z and its fitting coefficients are inverted:

[0059] in, n is the radial degree, m is the azimuth frequency.

[0060] Calculate the RMS value and compare the RMS values. The luminosity corresponding to the smaller RMS is the prescribed luminosity. The specific calculation method is: .

[0061] In some embodiments, the step of designing the surface shapes of the retinal refractive zone 111, the retinal peripheral refractive zone 112, and the refractive correction zone 113 according to the prescription diopter to obtain a microstructured lens further includes: The refractive powers of the retinal refractive zone 111, the retinal peripheral refractive zone 112, and the refractive correction zone 113 are calculated respectively to obtain the face shape corresponding to each area, and then the first surface 11 is smoothed to obtain a microstructured spectacle lens; The calculation expression of the refractive power of the retinal refractive zone 111 is: ;in, P target is the prescription light intensity, S actual It is the retinal astigmatism data of human eyes; The calculation expression of the diopter of the peripheral refractive zone 112 of the retina is: ;in, P target is the prescribed light intensity; To fit the retinal refractive data to obtain the Zernike polynomial in the standard mode; L N is the number of fitting terms and L N ≥171; is the correlation coefficient; The diopter calculation expression of the refractive correction area 113 is: ; Wherein, α represents the direction angle corresponding to the minimum value of the refractive power change rate in any direction; β represents the direction angle corresponding to the maximum value of the refractive power amplitude difference in any direction angle; D1 and D4 both represent the refractive power of the area where the α direction angle is located; D3 represents the refractive power of the entire first surface 11; D2 and D5 represent the refractive power of the area where the β direction angle is located; wherein, 0.5≤D1≤3, 0.25≤D2≤1.25, 0.5≤D3≤3.0, 0.5≤D4≤2.5, D5=mD4, m is a constant and 0 <m<1。

[0062] Furthermore, the diopter calculation process of the refractive correction area 113 is: 1) Find the correction direction (the direction corresponding to the minimum refractive power change rate in each direction); in order to achieve personalized design of the rear surface of the microstructure lens, the refractive power of the refractive correction area 113 on the rear surface of the lens needs to be regionalized according to the refractive conditions of the human retina. Figure 6 As shown, taking the right eye as an example, the three detection areas are subdivided into area D i , B i and N i ， And calculate the mean refractive power P of each area, where i =1,...,8. The objective function is constructed to find the minimum value of the diopter change rate in each direction. The specific expression is:

[0063] Where, P D , P B , P N Respectively i The average value of D, B, and N regions. J The direction angle α corresponding to the minimum value of the back surface refractive power change rate is obtained.

[0064] 2) Calculate the angle corresponding to the direction with the maximum refractive error in each direction, and find the direction angle β with the maximum refractive error in each direction angle of the detection area. The calculation method is: ; 3) calculating the refractive power of the refractive correction area 113 based on the obtained direction angle relationship; 4) The other areas of the back surface of the lens only need to meet the requirements of smoothness and continuity. This step describes the calculation of the refractive power of each area to characterize the overall characteristics of the first surface 11. The calculation is performed area by area from the center to the periphery of the first surface 11. To ensure the overall smoothness and continuity of the back surface, the entire back surface can be smoothed if necessary.

[0065] In some embodiments, the shapes of the retinal refractive zone 111, the retinal peripheral refractive zone 112, and the refractive correction zone 113 include, but are not limited to, combinations of regular or irregular shapes such as circles and regular polygons. The retinal peripheral refractive zone 112 and the refractive correction zone 113 may include a combination of multiple regional shapes to ensure a smooth transition of posterior surface refraction. The distances between different regions may be equal or unequal. In some embodiments, the retinal peripheral refractive zone 112 and the refractive correction zone 113 may be further divided into equal or unequal areas, such as into 6, 8, 10, or 12 equal-area regions. This may further improve the adaptation of the defocus distribution of the microstructured lens to the biological characteristics of the retina, thereby improving the myopia management effect.

[0066] In some embodiments, the material of the eyeglass lenses of this embodiment includes a polymer material or an inorganic non-metallic material. The polymer material includes a thermoplastic resin or a thermosetting resin, and the inorganic non-metallic material includes glass. Thermoplastic resins include polycarbonate or polymethyl methacrylate; thermosetting resins include any of acrylic resins, episulfide resins, thiourethane resins, allyl resins, and polyurethanes.

[0067] In some embodiments, a coating is formed on at least one side of the lens. The coating may include a transparent coating to increase the lens's light transmittance, a hard coating to increase the lens's durability, a reflective coating to block harmful light, an anti-reflection and anti-reflection coating to enhance image visibility, a polarizing film with a color-changing function, or other color-changing films doped with UV-sensitive materials. The coating itself may have different colors, and the color visible in a reflective environment may be green, blue, yellow, purple, or other colors. Example

[0068] The human eye is tested using human eye measurement equipment to obtain the retinal refractive distribution as follows: Figure 7 As shown, their average value can be uniformly approximated to -6.61D. The spherical power measured by human eye measurement equipment is approximately -6.39. Assuming the surface shape is spherical, the design method is used to fit the adjacent prescription power data and obtain the Zernike coefficients shown in Table 1. Calculating the RMS prescription power shows that when the prescription power is -6.5D, RMS = 4.3584e-15, and when the prescription power is -6.25D, RMS = 5.2774e-15. Therefore, the mother lens power of the microstructured lens is set to -6.5D.

[0069] Table 1

[0070] The half field of view angles used in the calculation are 5°, 12.5°, and 25°; the lens-to-eye distance is 12 mm, and s1 is 13 mm. Substitute the formula Available, l 1=3.05 mm, l 2=5.57 mm, l 3=11.28 mm. In the standard mode, Zernike polynomial fitting is performed on the basic surface height as follows Figure 8 As shown, the area radius l The area outside of 3 is interpolated to achieve a smooth transition of the sag height. The equivalent focal length of the human eye is usually 17 mm. The equivalent focal length of the lens is approximately its reciprocal according to the distribution of the human eye's diopter. In this embodiment, the equivalent focal length of the lens is 154 mm. In the design process of the refractive correction area 113, the direction of the minimum rate of change of the refractive power of the lens surface is the area where 0° is located, and the direction of the maximum amplitude difference is the area where 180° is located. The value of m is 1.5. The two surface shapes are superimposed to obtain the final design result of the first surface 11. Its astigmatism distribution diagram is shown as follows. Figure 9 shown.

[0071] To further illustrate the application effect of this design in inhibiting the further development of refractive error, the following Figure 10 The lens eye model shown in FIG. 1 has a first surface 11 formed as follows: Figure 1 The distribution shown in FIG. 1 is respectively configured as a first surface 11 for a common single-focus lens and a face type with a retinal refractive zone 111, a retinal peripheral refractive zone 112 and a refractive correction zone 113 ( Figure 2 ), the obtained MTF curve is as follows Figure 11 As shown in the figure, it is not difficult to find that the MTF values of the micro-structured lenses with the retinal refractive zone 111, the retinal peripheral refractive zone 112 and the refractive correction zone 113 are lower than those of the lenses without the design. Therefore, this design is also effective in suppressing the further development of refractive error.

[0072] In the above embodiments, the description of each embodiment has its own focus. For parts that are not described in detail in a certain embodiment, reference can be made to the relevant descriptions of other embodiments.

[0073] The above is a detailed introduction to a kind of eyeglass lens and its design method provided in the embodiment of the present application, and the principles and implementation methods of the present application are explained by applying specific examples. The description of the above embodiments is only used to help understand the technical solution and its core idea of the present application; ordinary technicians in this field should understand that: they can still modify the technical solutions recorded in the aforementioned embodiments, or replace some of the technical features therein with equivalents; and these modifications or replacements do not cause the essence of the corresponding technical solution to deviate from the scope of the technical solution of the embodiments of the present application.

Claims

1. A spectacle lens, characterized in that: include: A lens body (1), the lens body (1) comprising a first surface (11) disposed toward the retina of a human eye; the lens body having an optical center (10), the optical center (10) coinciding with a geometric center of the first surface (11); The first surface (11) includes a retinal refractive zone (111), a retinal peripheral refractive zone (112), and a refractive correction zone (113) arranged in sequence from the optical center (10) to the edge of the lens body (1); the retinal refractive zone (111), the retinal peripheral refractive zone (112), and the refractive correction zone (113) are respectively arranged around the optical center (10), and cooperate together to intervene in the retinal imaging quality within the pupil range; The retinal refractive zone (111) is used to determine the optical performance of the lens body (1) according to the refractive power of the retina of the human eye; the peripheral retinal refractive zone (112) is used to classify and compensate the first surface (11) according to the peripheral refractive conditions of the retina of the human eye; and the refractive correction zone (113) is used to correct the compensation to correct the peripheral refractive power of the retina of the human eye.

2. The spectacle lens according to claim 1, wherein: The lens body (1) further comprises a second surface (12) disposed away from the retina of a human eye; the second surface (12) comprises a central optical zone (121), a microstructure zone (122), and a first edge zone (123) disposed in sequence from the optical center (10) to the edge of the lens body (1); the central optical zone (121), the microstructure zone (122), and the first edge zone (123) are respectively disposed around the optical center (10); The spectacle lens further comprises a plurality of microstructures (2), wherein the plurality of microstructures (2) are arranged in the microstructure area (122) and are used to cooperate with the lens body (1) to form a stimulation signal.

3. The spectacle lens according to claim 2, characterized in that: There is a maximum distance of l1 mm from the optical center (10) to the edge of the retinal refractive zone (111), and a maximum distance of R1 mm from the optical center (10) to the edge of the central optical zone (121), satisfying: ； Where C1 is the radial coefficient and 0.1≤C1<0.3, f e f is the equivalent focal length of the human eye; l is the equivalent focal length of the lens; D is the diameter of the lens.

4. The spectacle lens according to claim 2, wherein: There is a maximum distance of 12 mm from the optical center (10) to the edge of the retinal peripheral refractive zone (112), and a maximum distance of R2 mm from the optical center (10) to the edge of the microstructure zone (122), satisfying: ； Where C2 is the radial coefficient and 0.2≤C2<0.5, f e f is the equivalent focal length of the human eye; l is the equivalent focal length of the lens; D is the diameter of the lens.

5. The spectacle lens according to claim 4, characterized in that: There is a maximum distance of 13 mm from the optical center (10) to the edge of the refractive correction zone (113), and a maximum distance of R3 mm from the optical center (10) to the edge of the first edge zone (123), satisfying: ； Among them, f e f is the equivalent focal length of the human eye; l is the equivalent focal length of the lens; D is the diameter of the lens; ∆x is the maximum offset when the wearer wears the glasses, ranging from 2 to 5 mm.

6. The spectacle lens according to claim 2, characterized in that: Among the plurality of microstructures (2), at least two of the microstructures (2) are connected to each other; or The plurality of microstructures (2) are spaced apart from each other; Wherein, the microstructure (2) is selected from at least one of a lens and a cylindrical lens.

7. The spectacle lens according to claim 1, characterized in that: The retinal peripheral refractive zone (112) has a plurality of first sub-areas (1121), and the refractive correction zone (113) has a plurality of second sub-areas (1131); the first sub-areas (1121) and the second sub-areas (1131) are adjacent to each other; the first sub-area (1121) has a first opening (1122) arranged toward the edge of the lens body (1); and the second sub-area (1131) has a second opening (1132) arranged toward the edge of the lens body (1); Wherein, the first opening (1122) of at least one of the first sub-areas (1121) is set toward the nasal side, and the first opening (1122) of at least one of the first sub-areas (1121) is set toward the temporal side; the second opening (1132) of at least one of the second sub-areas (1131) is set toward the nasal side, and the second opening (1132) of at least one of the second sub-areas (1131) is set toward the temporal side.

8. The spectacle lens according to claim 7, characterized in that: The retinal peripheral refractive zone (112) is divided into equal or non-equal angles around the optical center (10) to obtain the first sub-area (1121); the refractive correction zone (113) is divided into equal or non-equal angles around the optical center (10) to obtain the second sub-area (1131).

9. The spectacle lens according to claim 8, characterized in that: When the retinal peripheral refractive area (112) is divided into non-equiangular areas, the first opening (1122) of the first sub-area (1121) arranged toward the temporal side has a first angle in the optical center (10). The first opening (1122) of the first sub-region (1121) disposed toward the nose side has a second angle at the optical center (10). ,satisfy: .

10. The spectacle lens according to claim 8, characterized in that: When the refractive correction area (113) is divided into non-equal angles, the second opening (1132) of the second sub-area (1131) arranged toward the temporal side has a third angle in the optical center (10). The second opening (1132) of the second sub-region (1131) disposed toward the nose side has a fourth angle at the optical center (10). ,satisfy: .

11. The spectacle lens according to claim 7, characterized in that: The retinal peripheral refractive zone (112) and / or the refractive correction zone (113) are selected from any one of a circle, an ellipse, a regular polygon, and an irregular shape.

12. A method for designing a spectacle lens, characterized in that: The following steps are involved: Obtain human retinal refractive data and divide the refractive data distribution into regions; A lens body (1) is provided, wherein the lens body (1) has a first surface (11) and an optical center (10), and the first surface (11) is arranged toward the retina of a human eye; according to the area division, a refractive power mapping relationship between the retina and the first surface (11) is established, and design parameters are obtained; according to the design parameters, a retinal refractive zone (111), a retinal peripheral refractive zone (112), and a refractive correction zone (113) are sequentially arranged on the first surface (11) from the optical center (10) to the edge of the lens body (1); Obtaining the prescription power of the lens body (1); According to the prescription diopter, the surface shapes of the retinal refractive zone (111), the retinal peripheral refractive zone (112), and the refractive correction zone (113) are designed to obtain a microstructured lens; The retinal refractive zone (111), the retinal peripheral refractive zone (112), and the refractive correction zone (113) are respectively arranged around the optical center (10), and cooperate together to intervene in the retinal imaging quality within the pupil range.

13. The method for designing a spectacle lens according to claim 12, wherein: The lens body (1) further comprises a second surface (12) disposed opposite to the first surface (11), wherein the second surface (12) is disposed away from the retina of a human eye; and after the step of providing the lens body (1), the step further comprises: The second surface (12) of the lens body (1) is designed so that a central optical zone (121), a microstructure zone (122), and a first edge zone (123) are sequentially arranged on the second surface (12) from the optical center (10) to the edge of the lens body (1); wherein the central optical zone (121), the microstructure zone (122), and the first edge zone (123) are respectively arranged around the optical center (10); A plurality of microstructures are provided in the microstructure area for cooperating with the lens body to form a stimulation signal.

14. The method for designing a spectacle lens according to claim 12, wherein: The step of obtaining the prescription power of the lens body (1) further comprises: Get the upper and lower limits of the prescription light range; Calculate the vector height corresponding to the upper limit and lower limit respectively; Fit the Zernike polynomial in Fringe mode to the arrow height and invert its fitting coefficients; Use the fitting coefficient to calculate the corresponding RMS value, and take the minimum corresponding luminosity in the RMS value as the prescribed luminosity; The expression of RMS value is: ； Where c j is the fitting coefficient, N represents the number of second-order aberrations, ranging from 3 to 5.

15. The method for designing a spectacle lens according to claim 12, wherein: In the step of obtaining retinal refractive data of a human eye and dividing the distribution of the refractive data into regions, the region division includes a retinal fovea region (301), a first detection region (302), and a second detection region (303) sequentially arranged from the retinal center (30) to the retinal edge (31), and the retinal fovea region (301), the first detection region (302), and the second detection region (303) are respectively arranged around the retinal center (30).

16. The method for designing a spectacle lens according to claim 15, wherein: The expression of the refractive power mapping relationship between the retina and the first surface (11) is: ； Wherein, l represents the design parameter; L is the lens-to-eye distance and is 5 mm ≤ L ≤ 15 mm; s1 is the distance from the pupil to the center of eyeball rotation, s2 is the distance from the center of the macula lutea to the center of eyeball rotation, and satisfies s1 + s2 = 24; ∆R(θ, d) is a correction term and ranges from -2.5 mm to 2.5 mm, θ is the half field of view angle and is 0° ≤ θ ≤ 50°, d is the entrance pupil diameter and is 2 mm ≤ d ≤ 6 mm; r represents the maximum distance between the edge of any one of the foveal area (301), the first detection area (302) and the second detection area (303) and the center of the retina.

17. The method for designing a spectacle lens according to claim 12, wherein: The step of designing the surface shapes of the retinal refractive zone (111), the retinal peripheral refractive zone (112), and the refractive correction zone (113) according to the prescription diopter to obtain a microstructured lens further includes: The refractive powers of the retinal refractive zone (111), the retinal peripheral refractive zone (112), and the refractive correction zone (113) are calculated respectively to obtain the face shape corresponding to each area, and then the first surface (11) is smoothed to obtain a microstructured spectacle lens; The calculation expression of the refractive power of the retinal refractive zone (111) is: Among them, P target is the prescribed photometry, S actual It is the retinal astigmatism data of human eyes; The calculation expression of the refractive power of the peripheral refractive zone (112) of the retina is: Among them, P target is the prescribed light intensity; To fit the retinal refractive data to obtain the Zernike polynomial in the standard mode; L N is the number of fitting terms and L N ≥171; is the correlation coefficient; The calculation expression of the diopter of the refractive correction area (113) is: ； Wherein, α represents the direction angle corresponding to the minimum value of the refractive power change rate in any direction; β represents the direction angle corresponding to the maximum value of the refractive power amplitude difference in any direction; D1 and D4 both represent the refractive power of the region where the α direction angle is located; D3 represents the refractive power of the entire first surface (11); D2 and D5 represent the refractive power of the region where the β direction angle is located; wherein, 0.5≤D1≤3, 0.25≤D2≤1.25, 0.5≤D3≤3.0, 0.5≤D4≤2.5, D5=mD4, m is a constant and 0 <m<1。

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