Peripheral defocus control lens and manufacturing method

Abstract

The present application relates to the technical field of optical lenses, and discloses a peripheral defocus control lens and a manufacturing method. The peripheral defocus control lens comprises: a substrate, a microlens array, and a freeform surface. The substrate is a main area of the lens and has a spherical surface shape. The microlens array is arranged on the outer side of the substrate and is used for providing myopic defocus. The freeform surface is distributed on the inner side of the substrate and is used for compensating for or screening out refractive deviations in peripheral refraction of human eyes.

Description

Peripheral defocus control lens and manufacturing method

[0001] Related applications

[0002] This application claims priority to Chinese patent application No. 202410827784.9, filed on June 25, 2024, the entire contents of which are incorporated herein by reference. Technical Field

[0003] This application relates to the field of optical lens technology, and in particular to a peripheral defocus control lens and its manufacturing method. Background Technology

[0004] Myopia among teenagers has become a significant social problem in my country. Medically, myopia is a type of refractive error. In a normal eye, both central and peripheral objects are focused on the retina. However, in a myopic eye, due to axial elongation, central and peripheral objects are focused in front of the retina when accommodation is relaxed, making it difficult to see distant objects clearly. When myopic individuals wear single-vision glasses to correct their vision, although the central image is focused on the macula of the retina, the single-focus nature of the glasses causes peripheral images to fall behind the peripheral retina. This condition, known as hyperopic defocus in the myopic defocus theory, continuously stimulates axial elongation, accelerating the progression of myopia. Multi-point defocus eyeglasses based on microlens arrays are one of the mainstream methods for controlling myopia progression. Their main working principle is to provide compensation for the refractive error of the central macular of the retina while introducing a microlens array structure on the front surface of the lens. This microlens array can provide additional refractive power, i.e., defocus, causing some light rays in the peripheral retina to converge in advance, so that the hyperopic defocus is converted into myopic defocus, thereby inhibiting the excessive growth of the axial length of the eye.

[0005] However, commercially available multi-lens defocus lenses offer a fixed arrangement of microlenses and corresponding defocus amounts for different eyes, consistently providing the same defocus stimulus. However, the peripheral refractive values ​​of different eyes are not uniformly distributed; this is closely related to the structure and refractive index uniformity of the cornea, lens, vitreous humor, and other media, and this variability varies from person to person. Therefore, traditional single-solution multi-lens defocus lenses struggle to effectively control individualized peripheral refractive deviations, making it difficult to achieve the desired defocus amount across the retina and thus failing to achieve the expected therapeutic effect.

[0006] The above content is only used to help understand the technical solution of this application and does not represent an admission that the above content is prior art. Summary of the Invention

[0007] The main purpose of this application is to provide a peripheral defocus control lens and its manufacturing method, which aims to solve the technical problem that traditional single-solution multi-point microlens defocus lenses are difficult to effectively control the peripheral refractive deviation of the human eye that varies from person to person, making it difficult for the entire retina to achieve the expected defocus amount and thus failing to achieve the expected therapeutic effect.

[0008] To achieve the above objectives, this application provides a peripheral defocus control lens, which includes: a substrate, a microlens array, and a freeform surface;

[0009] The substrate is the main area of ​​the lens and has a spherical surface.

[0010] The microlens array is arranged on the outer side of the substrate to provide myopic defocus;

[0011] The freeform surface is distributed on the inner side of the substrate and is used to compensate for or filter refractive deviations between peripheral refractive points of the human eye.

[0012] In one embodiment, the substrate is provided with a central optical region and an annular region, the annular region including an annular defocus region and a defocus compensation region;

[0013] The substrate has a central optical region at its center, which is used to correct central refractive errors in the human eye.

[0014] The annular region surrounds the central optical region;

[0015] The substrate has an annular defocus area on its outer side, and the microlens array is arranged in the annular defocus area;

[0016] The substrate has a defocus compensation area on its inner side, and the freeform surface is distributed in the defocus compensation area.

[0017] In one embodiment, the position of the freeform surface corresponds to the position of the microlens array to compensate for or filter refractive deviations between peripheral refractive points of the human eye.

[0018] In one embodiment, the microlens array is arranged in a ten-ring array, and the microlens array includes multiple microlenses, each of which is equidistant in the tangential direction.

[0019] In one embodiment, the microlens has a diameter of 1.0 mm, the center-to-center distance between adjacent microlenses is 1.5 mm, and the distance between the center of the innermost microlens in the microlens array and the center of the central optical region is 5 mm.

[0020] In one embodiment, the radius of the central optical region is less than 4.5 mm, and the radius of the annular region is between 4.5 mm and 20.5 mm.

[0021] In one embodiment, the number of microlenses in each ring of the ten-ring array of the microlens array is 20, 26, 32, 38, 44, 50, 56, 62, 68, and 74 from the inside out, and the microlenses in each ring are evenly and equidistantly distributed in a circular array on their respective rings.

[0022] In one embodiment, the defocusing amount of the microlens ranges from 1.0D to 5.0D.

[0023] Furthermore, to achieve the above objectives, this application also proposes a method for manufacturing a peripheral defocus control lens, wherein the method is applied to the peripheral defocus control lens as described above, and the method includes:

[0024] To obtain central refractive information of the macula at the center of the human retina and peripheral refractive information of the periphery of the retina at different visual angles of the human eye;

[0025] Based on the central refractive information and the peripheral refractive information, the relative refractive distribution matrix of the human eye is determined;

[0026] The facial height matrix is ​​obtained by inverting the relative refractive distribution matrix of the human eye.

[0027] The peripheral defocus control lens is fabricated based on the aforementioned surface height matrix.

[0028] In one embodiment, the central refractive information includes spherical power and astigmatism; determining the relative refractive distribution matrix of the human eye based on the central refractive information and the peripheral refractive information includes:

[0029] Based on the spherical power and the astigmatism, determine the central refractive power at the central macula of the human eye's retina;

[0030] Extract peripheral refractive distribution data corresponding to different visual angles of the human eye from the peripheral refractive information;

[0031] Subtract the central refractive power from the peripheral refractive distribution data to obtain the relative refractive distribution matrix of the human eye.

[0032] This application proposes a peripheral defocus control lens, comprising: a substrate, a microlens array, and a freeform surface; the substrate is the main body of the lens and is spherical; the microlens array is arranged on the outer side of the substrate to provide myopic defocus; the freeform surface is distributed on the inner side of the substrate to compensate for or filter refractive deviations between peripheral refractive points of the human eye. Because this application introduces a freeform surface on the inner side of the lens based on the microlens array, it can simultaneously correct or filter defocus at both the central and peripheral positions of the human retina, thereby reducing the impact of peripheral refractive distribution differences on the insufficient myopic defocus formed by the microlens array, and further improving the myopia control effect of the lens. Attached Figure Description

[0033] Figure 1 is a schematic diagram of the structure of the first embodiment of the peripheral defocus control lens proposed in this application;

[0034] Figure 2 is a schematic diagram of the ideal human eye multi-point microlens defocusing effect of the first embodiment of the peripheral defocusing control lens proposed in this application;

[0035] Figure 3 is a schematic diagram of the actual human eye multi-point microlens defocusing effect of the first embodiment of the peripheral defocusing control lens proposed in this application;

[0036] Figure 4 is a schematic diagram of the actual human eye multi-point microlens defocus compensation effect of the first embodiment of the peripheral defocus control lens proposed in this application.

[0037] Figure 5 is a schematic diagram of the actual human eye multi-point microlens defocus screening effect of the first embodiment of the peripheral defocus control lens proposed in this application;

[0038] Figure 6 is a structural schematic diagram of the second embodiment of the peripheral defocus control lens proposed in this application;

[0039] Figure 7 is a multi-point microlens array distribution diagram of the second embodiment of the peripheral defocus control lens proposed in this application;

[0040] Figure 8 is a refractive distribution diagram of the second embodiment of the peripheral defocus control lens proposed in this application;

[0041] Figure 9 is a schematic diagram of the relative refractive distribution matrix and the refractive distribution of the lens defocus compensation area in the second embodiment of the peripheral defocus control lens proposed in this application.

[0042] Figure 10 is a schematic diagram of the radial refractive meridian division of the lens in the second embodiment of the peripheral defocus control lens proposed in this application;

[0043] Figure 11 is a flowchart illustrating the first embodiment of the method for manufacturing a peripheral defocus control lens according to this application.

[0044] Figure 12 is a schematic diagram of the lens fitting process of the defocus control lens in the first embodiment of the peripheral defocus control lens manufacturing method of this application.

[0045] The realization of the purpose, functional features and advantages of this application will be further explained in conjunction with the embodiments and with reference to the accompanying drawings. Detailed Implementation

[0046] It should be understood that the specific embodiments described herein are for illustrative purposes only and are not intended to limit the scope of this application.

[0047] This application provides a peripheral defocus control lens. Referring to FIG1, FIG1 is a structural schematic diagram of the first embodiment of the peripheral defocus control lens proposed in this application.

[0048] Studies have shown that axial elongation is closely related to the defocus state of peripheral retinal imaging. Peripheral hyperopic defocus can promote axial elongation and accelerate myopia progression, while peripheral myopic defocus can inhibit axial elongation and slow myopia progression. Although traditional single-vision lenses can effectively correct central retinal refractive errors in a simulated eye and ensure clear vision, they also promote peripheral hyperopic defocus, further exacerbating myopia development.

[0049] Therefore, multi-point defocus eyeglasses based on microlens arrays are one of the mainstream methods for controlling myopia progression. They have advantages such as low price, simple fitting process, wide applicability, suitability for people with high myopia, and low requirements for eye hygiene. Their main working principle is to provide compensation for the central macular refractive error while introducing a microlens array structure on the anterior surface of the lens. This microlens array provides additional refractive power, i.e., defocus, causing some light rays from the peripheral retina to converge prematurely, thus converting hyperopic defocus into myopic defocus, thereby inhibiting the rapid elongation of the eye axis. Simultaneously, the light intensity between the microlenses remains the same as the macular refractive error compensation intensity, ensuring the comfort of the simulated eye when viewing objects through this area.

[0050] However, commercially available multi-point microlens defocus lenses have a fixed microlens arrangement and corresponding defocus amount for different eyes, thus providing the same defocus stimulus. However, research shows that the central and peripheral refractive errors of the human eye reflect the ability of the medium within different visual angle channels to refract light, and their refractive values ​​are related to various factors such as the refractive index, curvature, and homogeneity of the medium within that channel. The peripheral refractive values ​​are not uniformly distributed among different eyes; therefore, the distribution of defocus in the peripheral retina varies from person to person. Therefore, traditional single-solution multi-point microlens defocusing lenses present two risks when worn. First, the uneven distribution of peripheral refractive error in an individual's eye can result in insufficient myopic defocus from the microlens. If a certain area of ​​the peripheral eye has hyperopic defocus, the microlens on the corresponding lens can convert some of that hyperopic defocus into myopic defocus, but this myopic defocus will be lower than the design value, thus reducing the stimulation to the eye. Second, hyperopic defocus still exists between microlenses, competing with the myopic defocus provided by nearby microlenses, thereby affecting the effectiveness of the microlenses in myopia control. Therefore, traditional single-solution multi-point microlens defocusing lenses struggle to effectively control the individualized peripheral refractive deviations of the eye, making it difficult for the entire retina to achieve the expected defocus amount and thus the desired therapeutic effect.

[0051] To address the aforementioned issues, based on Figure 1, a first embodiment of the peripheral defocus control lens of this application is proposed.

[0052] In this embodiment, the peripheral defocus control lens includes: a substrate, a microlens array, and a freeform surface;

[0053] The substrate is the main area of ​​the lens and has a spherical surface.

[0054] The microlens array is arranged on the outer side of the substrate to provide myopic defocus;

[0055] The freeform surface is distributed on the inner side of the substrate and is used to compensate for or filter refractive deviations between peripheral refractive points of the human eye.

[0056] The substrate is the main area of ​​the peripheral defocus control lens. It is generally spherical, made of transparent material, and used to correct vision problems. The substrate is usually made of plastic or glass and has specific optical properties. By adjusting the lens power and curvature, it can change the refraction and focusing of light, thereby helping people correct vision problems such as myopia, hyperopia, and astigmatism to achieve the best visual effect. The substrate corresponds to the refractive power of the prescription lens to ensure clear vision of the central retinal spot; this embodiment does not impose any limitations on this.

[0057] A microlens array is a series of tiny lenses arranged together to focus light onto a specific area of ​​the eye. Each microlens can adjust the refraction of light, thus producing a specific optical effect between the eye and an object. Placing a microlens array in eyeglasses can be used for myopia correction; by adjusting the refractive power of the microlenses, it can help nearsighted patients achieve clear vision.

[0058] Using a spherical surface as an example, the inner side is the concave side of the spherical surface, which is the side of the lens closest to the human eye; the outer side is the convex side of the spherical surface, which is the side of the lens furthest from the human eye.

[0059] For ease of understanding, refer to Figure 2, which is a schematic diagram of the ideal multi-point microlens defocusing effect of the first embodiment of the peripheral defocus control lens proposed in this application. A traditional multi-point microlens defocusing lens consists of two parts: a substrate that corresponds to the refractive power required for the prescription, ensuring clear vision of the central retinal spot; and a microlens array, typically arranged in a ring-shaped area in the center of the lens to provide additional myopic defocus. Ideally, after myopia correction, both the central and peripheral images are on the retina. Light rays passing through the central optical region converge at the macula of the retina; with the introduced microlens structure, light rays that have not passed through the microlens focus on the retina; while light rays that have passed through the microlens converge on the anterior side of the retina (as shown in Figure 2, i.e., converge at the optical convergence surface after passing through the microlens), thus forming myopic defocus. Since the defocusing amount of a traditional multi-point microlens defocusing lens is fixed, its defocusing amount is consistent.

[0060] However, compared to the ideal human eye, the peripheral refractive power of the actual human eye is not uniformly distributed across all locations; significant differences exist between different locations. Therefore, the actual defocusing situation of the multi-point microlens defocusing lens can be seen in Figure 3, which is a schematic diagram of the actual multi-point microlens defocusing effect in the human eye according to the first embodiment of the peripheral defocus control lens proposed in this application. As shown in Figure 3, light rays that have not passed through the microlens do not focus on the retina due to differences in peripheral refractive power. They may be in front of the retina (as shown in Figure 3, the optical converging surface without the microlens) or behind the retina, depending on whether the defocus is hyperopic or myopic and the magnitude of the defocus. While light rays that have passed through the microlens focus in front of the retina, forming myopic defocus, the defocus state at different locations is not consistent, and the amount of defocus converged in front of the retina also varies. If the human eye itself has hyperopic defocus at that location, the defocus formed by the microlens at that location will be much lower than the designed defocus amount of the microlens.

[0061] Therefore, embodiments of this application propose freeform surfaces to achieve defocus compensation or filtering.

[0062] The freeform surface is distributed on the inner side of the substrate, as shown in Figure 1. Its position corresponds to the microlens array on the outer side. Its refractive power is related to the relative refractive distribution of the human eye and is used to compensate for or filter the different peripheral refractive deviations of the human eye.

[0063] For ease of understanding, refer to Figure 4, which is a schematic diagram of the actual human eye multi-point microlens defocus compensation effect of the first embodiment of the peripheral defocus control lens proposed in this application. As shown in Figure 4, the dashed line at the retina of the human eye represents the retinal defocus state of the human eye itself. Light rays that do not pass through the microlens converge in front of and behind the retina, resulting in both myopic defocus in front of the retina and hyperopic defocus behind the retina. Due to the addition of a freeform surface behind the lens substrate, the refractive distribution of this freeform surface compensates for the differences in peripheral refractive power of the human eye. Light rays that do not pass through the microlens converge on the retina due to peripheral refractive compensation, while light rays that pass through the microlens have the same amount of defocus due to peripheral refractive compensation. That is, after compensation, the focusing position of the light rays is adjusted from the original front or back of the retina to the retina, meaning that both myopic and hyperopic defocus in the periphery of the retina are controlled to an emmetropic state. In conjunction with the microlens, the amount of myopic defocus generated by the multi-point microlens will remain consistent.

[0064] Furthermore, the freeform surface can not only compensate for defocus but also perform further screening. Referring to Figure 5, which is a schematic diagram of the actual human eye multi-point microlens defocus screening effect of the first embodiment of the peripheral defocus control lens proposed in this application, Figure 5 shows that the dashed line at the retina of the human eye represents the retinal defocus state of the human eye itself. Light rays that have not passed through the microlens converge in front of and behind the retina, resulting in both myopic defocus in front of the retina and hyperopic defocus behind the retina. Due to the addition of a freeform surface behind the lens substrate, the refractive distribution of this freeform surface can screen and control the differences in peripheral refractive power of the human eye. For the hyperopic defocus in the dashed line at the retina, since it has the risk of promoting myopia growth, the corresponding area of ​​the freeform surface in the lens compensates for it to a normal vision state, thus compensating for the hyperopic defocus. For the myopic defocus in the dashed line at the retina, it has an inhibitory effect on myopia growth, and the corresponding area of ​​the freeform surface in the lens has zero refractive power, effectively preserving it. This approach maximizes the preservation of myopic defocus and minimizes hyperopic defocus. Furthermore, due to peripheral refractive compensation, the final defocus amount after passing through the microlens is no less than the designed value. Therefore, by introducing a ring-shaped freeform surface on the rear surface of the multi-point microlens defocusing lens, defocus at both the central and peripheral positions of the retina can be simultaneously corrected or filtered. This ensures that the multi-point microlens provides the expected defocus amount, reducing the risk of myopia progression due to hyperopic defocus. This method ensures that the defocus value at each location on the retina is no less than the preset defocus amount, thus achieving the desired therapeutic effect.

[0065] This embodiment proposes a peripheral defocus control lens, comprising: a substrate, a microlens array, and a freeform surface. The substrate forms the main body of the lens and is spherical. The microlens array is arranged on the outer side of the substrate to provide myopic defocus. The freeform surface is distributed on the inner side of the substrate to compensate for or filter refractive deviations between peripheral refractive points of the human eye. Because this embodiment introduces a ring-shaped freeform surface on the rear surface of the lens, based on a multi-point microlens defocus lens, it can simultaneously correct or filter defocus at both the central and peripheral positions of the retina. This allows the multi-point microlens to provide the expected amount of defocus, reducing the risk of myopia progression due to hyperopic defocus. This method ensures that the defocus value at each position of the retina is not lower than a preset defocus amount, thereby achieving the desired therapeutic effect.

[0066] Referring to Figure 6, which is a structural schematic diagram of the second embodiment of the peripheral defocus control lens proposed in this application.

[0067] Based on the first embodiment described above, in this embodiment, the substrate is provided with a central optical region and an annular region, and the annular region includes an annular defocus region and a defocus compensation region.

[0068] The substrate has a central optical region at its center, which is used to correct central refractive errors in the human eye.

[0069] The annular region surrounds the central optical region;

[0070] The substrate has an annular defocus area on its outer side, and the microlens array is arranged in the annular defocus area;

[0071] The substrate has a defocus compensation area on its inner side, and the freeform surface is distributed in the defocus compensation area.

[0072] The central optical region is realized by the spherical structure of the substrate and is located at the center of the substrate. The corresponding refractive power meets the prescription for glasses, ensuring clear vision of the central spot on the retina and correcting central refractive errors of the human eye.

[0073] The annular region is the ring-shaped area immediately surrounding the central optical region. The annular defocus region is the area with an array of microlenses, located on the outer side of the substrate. The defocus compensation region is the area with a freeform surface, located on the inner side of the substrate.

[0074] Furthermore, in this embodiment, the position of the freeform surface corresponds to the position of the microlens array to compensate for or filter refractive deviations between peripheral refractive points of the human eye.

[0075] For ease of understanding, as shown in Figure 6, the defocus control lens has a spherical surface, with the inner side being the concave side and the outer side being the convex side. Figure 6 also illustrates the three-view structure of a peripheral defocus control lens. It consists of surface A, the side surface, and surface B. Surface A refers to the side of the lens furthest from the eye, i.e., the outer side of the substrate; surface B refers to the side of the lens closest to the eye, i.e., the inner side of the substrate. Functionally, the lens mainly consists of three parts: first, the substrate, which is the main body of the lens, primarily spherical, and corresponds to the refractive power required for prescription lenses; second, the microlens array, typically arranged in a ring on surface A, providing additional myopic defocus; and third, the freeform surface, distributed in a ring on surface B, whose refractive power is related to the relative refractive distribution of the eye, used to compensate for or filter varying peripheral refractive deviations in the eye.

[0076] The lens is primarily divided into four regions: First, the central optical region, which is achieved using a spherical substrate structure. Its refractive power meets the prescription, ensuring clear vision of the central retinal spot. Second, the A-side's annular defocus region, which contains a microlens array to provide additional myopic defocus. The area between the microlens arrays also uses a spherical substrate structure, ensuring the refractive power meets the prescription and providing comfort and adaptability. Third, the B-side's defocus compensation region, corresponding to the annular defocus region, features a freeform surface to compensate for or filter peripheral refractive errors varying from eye to eye. Fourth, the extension region, also achieved using a spherical substrate structure.

[0077] When wearing this lens, the ring-shaped area around the lens corrects or filters the individual's peripheral defocus, thereby reducing the impact of differences in the peripheral refractive distribution of the human eye on the myopic defocus caused by the multi-point microlens lens, and further improving the myopia control effect of the lens.

[0078] Further, referring to Figure 7, which is a multi-point microlens array distribution diagram of the second embodiment of the peripheral defocus control lens proposed in this application. In this embodiment, the microlens array is arranged in a ten-ring array, and the microlens array includes multiple microlenses, each of which is equidistant in the tangential direction.

[0079] Ten rings of microlenses can be arranged on one side of the microlens array. This ensures that ten equidistant microlenses are arranged along the tangent direction of the lens's horizontal x-axis. The number of rings in the microlens array can also be eleven, twelve, etc., depending on the actual situation; this embodiment does not impose any limitations on this.

[0080] Furthermore, in this embodiment, the microlens has a diameter of 1.0 mm, the center distance between adjacent microlenses is 1.5 mm, and the distance between the center of the innermost microlens in the microlens array and the center of the central optical region is 5 mm.

[0081] Furthermore, in this embodiment, the radius of the central optical region is less than 4.5 mm, and the radius of the annular region is between 4.5 mm and 20.5 mm.

[0082] Furthermore, in this embodiment, the defocusing range of the microlens is 1.0D to 5.0D.

[0083] The diameter data mentioned above can be set according to actual conditions, and this embodiment does not impose any restrictions on this.

[0084] Furthermore, in this embodiment, the number of microlenses in each ring of the ten-ring array of the microlens array is 20, 26, 32, 38, 44, 50, 56, 62, 68, and 74 from the inside out, and the microlenses in each ring are evenly and equidistantly distributed in a circular array on their respective rings.

[0085] The number of microlenses in each ring can be increased or decreased according to the actual situation to improve the comfort and accuracy of the peripheral defocus control lens. This embodiment does not impose any restrictions on this.

[0086] For ease of understanding, Figure 7 is used as an example, but this does not limit the scope of this solution. The area with a lens radius less than 4.5mm, centered on the lens center, can be considered the central optical region of the lens. Its power corresponds to the prescription and is used to ensure clear vision for the wearer. The annular region with a lens radius greater than 4.5mm and less than 20.5mm can be considered the peripheral annular region of the lens. A microlens array is arranged on one side of this region to provide myopia-specific defocus. Ten rings of microlenses can be arranged on one side, ensuring 10 equidistant microlenses are arranged in the positive x- or y-direction of the lens. The radius of the annular region and the central optical region can be 15mm. The microlens diameter can be 1.0mm, and the center-to-center distance between adjacent microlenses can be 1.5mm, meaning the annular radius of the annular region can be 1.5*9mm. The distance between the center of the innermost (first ring) microlens and the center of the lens can be 5mm. The number of microlenses in each ring can be 20, 26, 32, 38, 44, 50, 56, 62, 68, or 74 from the inside out. The microlenses in each ring are evenly and equidistantly distributed in a circular array on their respective rings. The defocus range of all microlenses can be 1.0D to 5.0D.

[0087] Furthermore, the manufacturing principle of peripheral defocus control lenses is as follows.

[0088] Referring to Figure 8, which is a refractive distribution map of the second embodiment of the peripheral defocus control lens proposed in this application, the left figure shows the absolute refractive distribution map of the human retina obtained by a refractive topography instrument. Each ring in the figure represents a 5° field of view interval, and the number represents the equivalent spherical power corresponding to that field of view. The equivalent spherical power at the center position is the equivalent spherical power of the prescription (i.e., -4.0 diopters). Subtracting the equivalent spherical power at the center position from all peripheral refractive distribution values ​​simultaneously yields the relative refractive distribution of the human retina, as shown in the right figure. This refractive distribution reflects the peripheral defocus state of the human retina after the refractive error has been corrected.

[0089] Then, based on Figure 8, the relative refractive distribution matrix and the refractive index of the lens defocus compensation area are determined. Referring to Figure 9, Figure 9 is a schematic diagram of the relative refractive distribution matrix and the refractive distribution of the lens defocus compensation area in the second embodiment of the peripheral defocus control lens proposed in this application. The peripheral refractive distribution in the right figure of Figure 8 is divided into multiple regions according to the tangential and radial directions, and the average refractive value of each region is defined as D(i,j). Where i corresponds to the number of tangential regions and j corresponds to the number of radial regions, the numbers of i and j can be adjusted. The equivalent refractive value D(i,j) of each region is equal to the average of all refractive values ​​of the corresponding region in the peripheral refractive distribution diagram in the right figure of Figure 8. After obtaining the refractive distribution matrix as shown in the left figure of Figure 9, the values ​​of the matrix are expanded from a circular distribution to a ring distribution, as shown in the right figure of Figure 9. If the defocus control lens needs to compensate for the difference in defocus of the human eye, the refractive compensation value of each region of the lens needs to be equal to the refractive value of the corresponding region of the relative refractive distribution of the human eye. If a defocus control lens needs to screen for human eye defocus, in order to maximize the myopia control effect, it is usually necessary to retain the myopic defocus in the periphery of the human eye and compensate for the hyperopic defocus in the periphery. If there is a region in the relative refractive distribution of the human eye that is less than zero (myopic defocus), the refractive value of the corresponding region of the lens is designed to be zero and no control is applied to it. If there is a region in the relative refractive distribution of the human eye that is greater than zero (hyperopic defocus), the refractive value of the corresponding region of the lens is designed to be equal to the refractive value of the relative refractive distribution to ensure that it is no longer hyperopic defocus.

[0090] Finally, the radial refractive meridian of the lens is determined. Referring to Figure 10, which is a schematic diagram of the radial refractive meridian division of the lens in the second embodiment of the peripheral defocus control lens proposed in this application, the relationship between the radial position x of a certain meridian in the lens space, the relative refractive distribution field of view θ, and the lens-eye distance d is as follows: x = 2(d × tanθ + 1.5 mm);

[0091] The relationship between the center coordinates (ξ,η) corresponding to the radii of curvature at each point on the B-side of the lens is as follows: ξ(x)=xR(x)sinθ(x);

[0092] Where R(x) is the radius of curvature at the corresponding point on the curve, and θ(x) is determined by the following formula:

[0093] The sag z(x) at that point on the lens satisfies the formula:

[0094] Let the refractive power at each point along the i-th meridian be D. i (x), according to the definition of diopter: D i (x)=(n-1) / R(x), where n is the refractive index of the lens. Based on this formula, the final sag and the corresponding curvature center positions at each point can be directly calculated from the refractive power distribution along the meridian. And D i (x) curves (as shown in Figure 10) D1(x), D2(x), D3(x), D4(x), ..., D i (x) is the profile data extracted from a certain direction on the original lens diopter distribution map.

[0095] The peripheral defocus control lens produced in this way, as shown in Figure 4, represents the defocus state of the human eye's retina. Light rays that do not pass through the microlens converge in front of and behind the retina, exhibiting both myopic defocus in front of the retina and hyperopic defocus behind the retina. By adding a freeform surface behind the lens substrate, the refractive distribution of this surface compensates for the differences in peripheral refractive power. Light rays that do not pass through the microlens converge on the retina due to peripheral refractive compensation, while light rays that pass through the microlens have the same amount of defocus due to peripheral refractive compensation. In other words, the focusing position of the compensated light rays is adjusted from either in front of or behind the retina to on the retina itself. This means that both myopic and hyperopic defocus in the peripheral retina are controlled to an emmetropic state. Combined with the microlens, the amount of myopic defocus produced by multiple microlenses will remain consistent.

[0096] Further screening can be performed, as shown in Figure 5. The dashed line at the retina in the figure represents the retinal defocus state of the human eye itself. Light rays that have not passed through the microlens converge in front of and behind the retina, resulting in both myopic defocus in front of the retina and hyperopic defocus behind the retina. Because a freeform surface is added behind the lens substrate, the refractive distribution of this freeform surface can screen and control the differences in peripheral refractive power in the human eye. For the hyperopic defocus in the dashed line at the retina, since it poses a risk of promoting myopia progression, the corresponding area of ​​the freeform surface in the lens compensates for it to a normal vision state, thus compensating for the hyperopic defocus. For the myopic defocus in the dashed line at the retina, it has an inhibitory effect on myopia progression, and the corresponding area of ​​the freeform surface in the lens has zero refractive power, allowing it to be effectively preserved. In this way, the amount of myopic defocus can be preserved to the maximum extent, and the amount of hyperopic defocus can be suppressed to the maximum extent. Furthermore, due to peripheral refractive compensation, the final amount of defocus after passing through the microlens is not less than the final design value. Therefore, based on the multi-point microlens defocusing lens, a freeform surface with a ring distribution is introduced on the rear surface of the lens. This allows for the simultaneous correction or screening of defocus at both the central and peripheral positions of the human retina. This ensures that the multi-point microlens provides the expected amount of defocus, reducing the risk of myopia progression due to hyperopic defocus. This method ensures that the defocus value at each position of the retina is not lower than the preset defocus amount, thereby achieving the preset treatment effect.

[0097] In this embodiment, the substrate has a central optical region and an annular region. The annular region includes an annular defocus area and a defocus compensation area. The central optical region is located at the center of the substrate and is used to correct central refractive errors in the human eye. The annular region surrounds the central optical region. An annular defocus area is located on the outer side of the substrate, and the microlens array is arranged within this area. A defocus compensation area is located on the inner side of the substrate, and freeform surfaces are distributed within it. The positions of the freeform surfaces correspond to the positions of the microlens array to compensate for or filter refractive deviations between peripheral refractive errors in the human eye. When wearing this lens, the annular region around the lens corrects or filters peripheral defocus, thereby reducing the impact of differences in peripheral refractive distribution on the myopic defocus caused by the multi-point microlens lens, further improving the lens's myopia control effect.

[0098] In addition, to achieve the above objectives, this application also provides a method for manufacturing a peripheral defocus control lens based on the peripheral defocus control lens of the above embodiments. Referring to FIG11, FIG11 is a flowchart of the first embodiment of the peripheral defocus control lens manufacturing method of this application.

[0099] The first embodiment of the peripheral defocus control lens manufacturing method of this application is based on Figure 11.

[0100] In this embodiment, the method for manufacturing the peripheral defocus control lens includes:

[0101] Step S10: Obtain the central refractive information of the macula at the center of the human eye's retina and the peripheral refractive information of the retina at different visual angles.

[0102] Central refractive information refers to the information about the refraction of light received at the macula in the center of the retina. The macula is a small area located in the center of the retina and plays a crucial role in the perception of high resolution, detail, and color. The way light is refracted at the macula affects our ability to perceive the details and colors of objects. Central refractive information may include information such as spherical power, astigmatism, and axis.

[0103] Peripheral refractive information refers to the refraction of light received at different locations around the retina of the human eye. The field of view refers to the angular range from the central line of sight to the peripheral line of sight, usually expressed in degrees. Light refracts differently at different parts of the field of view, which affects our ability to perceive the sharpness and shape of surrounding objects.

[0104] By adjusting the prescription of the glasses based on these changes in refractive information, optimal visual experience can be achieved in both the central and peripheral vision.

[0105] Step S20: Determine the relative refractive distribution matrix of the human eye based on the central refractive information and the peripheral refractive information.

[0106] The relative refractive distribution matrix of the human eye is determined based on the central refractive information and the peripheral refractive information.

[0107] In practice, the relative refractive distribution matrix of the human eye can be obtained by subtracting the refractive power of the central macula from the peripheral refractive power corresponding to different visual angles of the human eye.

[0108] Furthermore, in this embodiment, the central refractive information includes spherical power and astigmatism; step S20 includes: determining the central refractive power of the central macula of the human eye's retina based on the spherical power and the astigmatism; extracting peripheral refractive distribution data corresponding to different visual angles of the human eye from the peripheral refractive information; subtracting the central refractive power from the peripheral refractive distribution data to obtain the relative refractive distribution matrix of the human eye.

[0109] Spherical power and astigmatism are measures used to describe the refractive state of the eye. Spherical power describes the degree of myopia (negative value) or hyperopia (positive value), representing the eye's refractive ability, measured in diopters (D). For example, an eye with a diopter of -3.00D indicates 3 degrees of myopia. A positive value indicates hyperopia. Astigmatism describes visual problems caused by differences in the curvature of the cornea or intraocular tissues, resulting in inaccurate focusing of light within the eye. Negative numbers represent the curvature of a concave lens (astigmatism diopters), and positive numbers represent the curvature of a convex lens (astigmatism diopters). The unit of astigmatism is also diopters (D). For example, an astigmatism diopter of -1.50D indicates 1.5 degrees of astigmatism in the eye.

[0110] Typically, an eyeglass prescription includes spherical power, astigmatism correction, and axis information. Axis indicates the direction of astigmatism and is expressed in diopters, usually between 0 and 180 degrees. These spherical and astigmatism corrections, along with axis information, correct the eye's refractive state, resulting in clearer and more comfortable vision.

[0111] In practice, the refractive power of the central macula can be subtracted from the peripheral refractive power corresponding to different visual angles of the human eye to obtain the relative refractive distribution matrix of the human eye. The refractive power of the central macula of the retina is equal to the equivalent spherical power, which is numerically equal to the spherical power + 1 / 2 × astigmatism.

[0112] Step S30: Invert the relative refractive distribution matrix of the human eye to obtain the facial height matrix.

[0113] Step S40: Fabricate a peripheral defocus control lens based on the surface height matrix.

[0114] The facial height matrix is ​​obtained by matrix inversion calculation of the relative refractive distribution matrix of the human eye.

[0115] In practical implementation, referring to Figure 12, which is a schematic diagram of the lens fitting process for the defocus control lens manufacturing method of the first embodiment of this application, the specific lens fitting process is as follows:

[0116] The first step is to obtain an individual's eye prescription. This involves identifying the central refractive information of the macula in the retina through subjective or objective refraction, which is used to prescribe glasses. This information includes spherical power, astigmatism, and axis.

[0117] The second step is to obtain peripheral refractive data for the individual's eye. This is achieved using equipment such as refractive topography, wide-angle refractometers, and fenestrated refractometers to obtain the equivalent spherical power of the peripheral retina at different visual angles, which is then used as the peripheral refractive power.

[0118] The third step is to obtain the relative refractive distribution matrix of an individual's eye. The relative refractive distribution matrix of the eye is obtained by subtracting the refractive power at the central macula from the peripheral refractive power corresponding to different visual angles of the human eye. The refractive power of the central macula of the retina is equal to the equivalent spherical power, which is numerically equal to the spherical power + 1 / 2 × astigmatism.

[0119] The fourth step is to obtain the surface height matrix of the defocus control lens. This is achieved by inverting the relative refractive distribution matrix of the human eye to calculate the surface height matrix of the defocus control lens.

[0120] Step 5: Fabrication of the defocus control lens. The defocus lens is fabricated based on the lens surface height matrix.

[0121] To facilitate understanding, the manufacturing principle of peripheral defocus control lenses is described below. As shown in Figure 8, the left image is an absolute refractive distribution map of the human retina obtained by a refractive topography instrument. Each ring in the image represents a 5° field of view interval, and the number represents the equivalent spherical power corresponding to that field of view. The equivalent spherical power at the center position is the equivalent spherical power of the prescription (i.e., -4.0 diopters). Subtracting the equivalent spherical power at the center position from all peripheral refractive distribution values ​​yields the relative refractive distribution of the human retina, as shown in the right image. This refractive distribution reflects the peripheral defocus state of the human retina after refractive error correction.

[0122] Then, based on Figure 8, the relative refractive distribution matrix and the refractive index of the lens defocus compensation zone are determined. As shown in Figure 9, the peripheral refractive distribution in the right image of Figure 8 is divided into multiple regions along the tangential and radial directions. The average refractive value of each region is defined as D(i,j). Here, i corresponds to the number of tangential regions, and j corresponds to the number of radial regions; the numbers i and j can be adjusted. The equivalent refractive value D(i,j) of each region is equal to the average of all refractive values ​​in the corresponding region of the peripheral refractive distribution map in the right image of Figure 8. After obtaining the refractive distribution matrix in the left image of Figure 9, the values ​​of this matrix are expanded from a circular distribution to a ring distribution, as shown in the right image of Figure 9. If the defocus control lens needs to compensate for the difference in defocus in the human eye, the refractive compensation value of each region of the lens needs to be equal to the refractive value of the corresponding region of the relative refractive distribution in the human eye. If a defocus control lens needs to screen for human eye defocus, in order to maximize the myopia control effect, it is usually necessary to retain the myopic defocus in the periphery of the human eye and compensate for the hyperopic defocus in the periphery. If there is a region in the relative refractive distribution of the human eye that is less than zero (myopic defocus), the refractive value of the corresponding region of the lens is designed to be zero and no control is applied to it. If there is a region in the relative refractive distribution of the human eye that is greater than zero (hyperopic defocus), the refractive value of the corresponding region of the lens is designed to be equal to the refractive value of the relative refractive distribution to ensure that it is no longer hyperopic defocus.

[0123] Finally, the radial refractive meridian of the lens is determined. As shown in Figure 10, the relationship between the radial position x of a certain meridian in the lens space, the relative refractive distribution field of view θ, and the lens-eye distance d is as follows: x=2(d×tanθ+1.5mm);

[0124] The relationship between the center coordinates (ξ,η) corresponding to the radii of curvature at each point on the B-side of the lens is as follows: ξ(x)=xR(x)sinθ(x);

[0125] Where R(x) is the radius of curvature at the corresponding point on the curve, and θ(x) is determined by the following formula:

[0126] The sag z(x) at that point on the lens satisfies the formula:

[0127] Let the refractive power at each point along the i-th meridian be D. i (x), according to the definition of diopter: D i (x)=(n-1) / R(x), where n is the refractive index of the lens. Based on this formula, the final sag and the corresponding curvature center positions at each point can be directly calculated from the refractive power distribution along the meridian. And D i (x) curves (as shown in Figure 10) D1(x), D2(x), D3(x), D4(x), ..., D i (x) is the profile data extracted from a certain direction on the original lens diopter distribution map.

[0128] The peripheral defocus control lens produced in this way, as shown in Figure 4, represents the defocus state of the human eye's retina. Light rays that do not pass through the microlens converge in front of and behind the retina, exhibiting both myopic defocus in front of the retina and hyperopic defocus behind the retina. By adding a freeform surface behind the lens substrate, the refractive distribution of this surface compensates for the differences in peripheral refractive power. Light rays that do not pass through the microlens converge on the retina due to peripheral refractive compensation, while light rays that pass through the microlens have the same amount of defocus due to peripheral refractive compensation. In other words, the focusing position of the compensated light rays is adjusted from either in front of or behind the retina to on the retina itself. This means that both myopic and hyperopic defocus in the peripheral retina are controlled to an emmetropic state. Combined with the microlens, the amount of myopic defocus produced by multiple microlenses will remain consistent.

[0129] Further screening can be performed, as shown in Figure 5. The dashed line at the retina in the figure represents the retinal defocus state of the human eye itself. Light rays that have not passed through the microlens converge in front of and behind the retina, resulting in both myopic defocus in front of the retina and hyperopic defocus behind the retina. Because a freeform surface is added behind the lens substrate, the refractive distribution of this freeform surface can screen and control the differences in peripheral refractive power in the human eye. For the hyperopic defocus in the dashed line at the retina, since it poses a risk of promoting myopia progression, the corresponding area of ​​the freeform surface in the lens compensates for it to a normal vision state, thus compensating for the hyperopic defocus. For the myopic defocus in the dashed line at the retina, it has an inhibitory effect on myopia progression, and the corresponding area of ​​the freeform surface in the lens has zero refractive power, allowing it to be effectively preserved. In this way, the amount of myopic defocus can be preserved to the maximum extent, and the amount of hyperopic defocus can be suppressed to the maximum extent. Furthermore, due to peripheral refractive compensation, the final amount of defocus after passing through the microlens is not less than the final design value. Therefore, based on the multi-point microlens defocusing lens, a freeform surface with a ring distribution is introduced on the rear surface of the lens. This allows for the simultaneous correction or screening of defocus at both the central and peripheral positions of the human retina. This ensures that the multi-point microlens provides the expected amount of defocus, reducing the risk of myopia progression due to hyperopic defocus. This method ensures that the defocus value at each position of the retina is not lower than the preset defocus amount, thereby achieving the preset treatment effect.

[0130] This embodiment identifies the central refractive information of the macula at the center of the retina of an individual eye through subjective or objective refraction for lens fitting. This information includes spherical power, astigmatism, and axis. Then, using equipment such as refractive topography, a wide-angle refractometer, and a window refractometer, the equivalent spherical power of the peripheral retina at different visual angles is obtained as the peripheral refractive power. Next, the refractive power at the central macula is subtracted from the peripheral refractive power corresponding to different visual angles to obtain the relative refractive distribution matrix of the eye. The refractive power of the central macula is equal to the equivalent spherical power, numerically equal to spherical power + 1 / 2 × astigmatism. The surface height matrix of the defocus control lens is then calculated based on the relative refractive distribution matrix. Finally, the defocus lens is manufactured according to the lens surface height matrix. The peripheral defocus control lens thus created, by introducing a ring-shaped freeform surface on the rear surface of the lens based on a multi-point microlens defocus lens, can simultaneously correct or filter defocus at both the central and peripheral positions of the human retina. This allows the multi-point microlens to provide the expected amount of defocus, reducing the risk of myopia progression caused by hyperopic defocus. This method ensures that the defocus value at each position of the retina is not lower than the preset defocus amount, thereby achieving the preset treatment effect.

[0131] In this document, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or system that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or system. Unless otherwise specified, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, method, article, or system that includes that element.

[0132] The sequence numbers of the embodiments in this application are for descriptive purposes only and do not represent the superiority or inferiority of the embodiments.

[0133] Through the above description of the embodiments, those skilled in the art can clearly understand that the methods of the above embodiments can be implemented by means of software plus necessary general-purpose hardware platforms. Of course, they can also be implemented by hardware, but in many cases the former is a better implementation method. Based on this understanding, the technical solution of this application, in essence, or the part that contributes to the prior art, can be embodied in the form of a software product. This computer software product is stored in a storage medium (such as read-only memory / random access memory, magnetic disk, optical disk) and includes several instructions to cause a terminal device (which may be a mobile phone, computer, server, or network device, etc.) to execute the methods described in the various embodiments of this application.

[0134] The above are merely embodiments of this application and do not limit the patent scope of this application. Any equivalent structural or procedural transformations made using the content of this application's specification and drawings, or direct or indirect applications in other related technical fields, are similarly included within the patent protection scope of this application.

Claims

1. A peripheral defocus control lens, wherein, The peripheral defocus control lens includes: a substrate, a microlens array, and a freeform surface; The substrate is the main area of ​​the lens and has a spherical surface. The microlens array is arranged on the outer side of the substrate to provide myopic defocus; The freeform surface is distributed on the inner side of the substrate and is used to compensate for or filter refractive deviations between peripheral refractive points of the human eye.

2. The peripheral defocus control lens as described in claim 1, wherein, The substrate has a central optical region and an annular region, and the annular region includes an annular defocus region and a defocus compensation region. The substrate has a central optical region at its center, which is used to correct central refractive errors in the human eye. The annular region surrounds the central optical region; The substrate has an annular defocus area on its outer side, and the microlens array is arranged in the annular defocus area; The substrate has a defocus compensation area on its inner side, and the freeform surface is distributed in the defocus compensation area.

3. The peripheral defocus control lens as described in claim 2, wherein, The position of the freeform surface corresponds to the position of the microlens array, so as to compensate for or filter the refractive deviations between peripheral refractive points of the human eye.

4. The peripheral defocus control lens as described in claim 3, wherein, The microlens array is arranged in a ten-ring array, and the microlens array includes multiple microlenses, each of which is equidistant in the tangential direction.

5. The peripheral defocus control lens as described in claim 4, wherein, The microlens has a diameter of 1.0 mm, the center-to-center distance between adjacent microlenses is 1.5 mm, and the distance between the center of the innermost microlens in the microlens array and the center of the central optical region is 5 mm.

6. The peripheral defocus control lens as described in claim 2, wherein, The radius of the central optical region is less than 4.5 mm, and the radius of the annular region is between 4.5 mm and 20.5 mm.

7. The peripheral defocus control lens as described in claim 4, wherein, The number of microlenses in each ring of the ten-ring array of the microlens array is 20, 26, 32, 38, 44, 50, 56, 62, 68, and 74 from the inside out. The microlenses in each ring are evenly and equidistantly distributed in a circular array on their respective rings.

8. The peripheral defocus control lens as described in claim 4, wherein, The defocus range of the microlens is 1.0D to 5.0D.

9. A method for manufacturing a peripheral defocus control lens, wherein, The peripheral defocus control lens manufacturing method is applied to the peripheral defocus control lens as described in any one of claims 1-8, and the peripheral defocus control lens manufacturing method includes: To obtain central refractive information of the macula at the center of the human retina and peripheral refractive information of the periphery of the retina at different visual angles of the human eye; Based on the central refractive information and the peripheral refractive information, the relative refractive distribution matrix of the human eye is determined; The facial height matrix is ​​obtained by inverting the relative refractive distribution matrix of the human eye. The peripheral defocus control lens is fabricated based on the aforementioned surface height matrix.

10. The method for manufacturing a peripheral defocus control lens as described in claim 9, wherein, The central refractive information includes spherical power and astigmatism; determining the relative refractive distribution matrix of the human eye based on the central refractive information and the peripheral refractive information includes: Based on the spherical power and the astigmatism, determine the central refractive power at the central macula of the human eye's retina; Extract peripheral refractive distribution data corresponding to different visual angles of the human eye from the peripheral refractive information; Subtract the central refractive power from the peripheral refractive distribution data to obtain the relative refractive distribution matrix of the human eye.

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