Hyperopia correction glasses based on refractive topographic map and design method thereof

Abstract

The invention belongs to the technical field of medical instruments, and particularly relates to a pair of hyperopia correction glasses based on a refractive topographic map and a design method thereof. The pair of hyperopia correction glasses comprises a base lens, the middle part of the base lens is an out-of-focus-free area, an annular area outside the out-of-focus-free area is an out-of-focus stimulation area, the geometric center of the out-of-focus stimulation area coincides with the center of the out-of-focus-free area, and a plurality of out-of-focus correction areas are arranged on the base lens within the out-of-focus stimulation area. And a plurality of micro lenses with the same diopter are arranged in each defocus correction area. Based on the MRT peripheral defocus detection result of the patient, the individualized full-eye customization technology is adopted, accurate matching of the lens and the peripheral defocus of the retina is ensured, the defocus amount of eyeballs in different directions can be accurately adjusted through individualized customization, the eyeballs return to a comfortable area, the ideal hyperopia defocus state is formed, and the visual effect of the eyeballs is improved. The effects of promoting eye axis growth and treating hyperopia are enhanced.

Description

Technical Field

[0001] This invention belongs to the field of medical device technology, specifically relating to a hyperopia correction eyeglass based on refractive topography and its design method. Background Technology

[0002] Hyperopia, a common refractive error, is pathologically based on the fact that the equivalent optical focus of the eye's refractive system falls behind the retina. Axial hyperopia, as the main subtype, originates from delayed development of the eye's axial length, leading to a mismatch between the retinal plane and the optical focal plane. Epidemiological studies show that children with moderate to high axial hyperopia, without timely refractive correction, can develop a 35%-55% incidence of amblyopia and significantly increase the clinical risk of accommodative esotropia and impaired stereoscopic acuity. Current refractive correction schemes are based on geometric optics principles, using single-vision convex lenses for refractive compensation. While this can improve the image quality of the fovea, it fails to establish an effective biomechanical stimulation mechanism, resulting in the continued persistence of delayed axial development. Clinical follow-up data shows that these patients experience a decrease of less than 0.5D in hyperopia annually. Long-term use of glasses combined with amblyopia treatment places a heavy burden on the children and their families.

[0003] In the field of refractive development regulation, multifocal myopia defocus technology has been applied to myopia control and inhibition of axial elongation, and its effectiveness has been verified through photobiological mechanisms. Its mechanism of action involves creating a stable myopia defocus signal in the peripheral retina through aspherical optical design, which then inhibits axial elongation via the retina-sclera pathway. Multicenter clinical studies have confirmed that this technology can reduce the rate of myopia progression in adolescents by approximately 30-70%. In recent years, in particular, myopia defocus glasses that combine multispectral refractive topography (MRT) data and use dynamic zonal defocus design to inhibit axial elongation in myopic patients have achieved good results in clinical applications, with related clinical trials showing an annual myopia control rate of 75%. However, there is still a lack of breakthroughs in optical intervention systems for hyperopia treatment, and active photodynamic intervention cannot improve the anatomical basis of axial hyperopia. Summary of the Invention

[0004] The purpose of this invention is to provide a hyperopia correction eyeglass based on refractive topography and its design method, so as to solve the problems existing in the above-mentioned background art.

[0005] To achieve the above objectives, this application employs the following technical solution:

[0006] A hyperopia correction eyeglass based on refractive topography has a lens structure with two functional zones, including a base lens. The base lens is a positive lens configured according to the patient's cycloplegic refraction results, and its refractive power is determined based on the patient's hyperopia refractive power under cycloplegia. The middle part of the base lens is a non-defocus zone, the center of which ensures that it is aligned with the center of the patient's retinal macular area when the patient wears the glasses normally and looks straight ahead. The annular area outside the non-defocus zone is a defocus stimulation zone, the geometric center of which coincides with the center of the non-defocus zone. Multiple defocus correction zones are set on the base lens within the defocus stimulation zone, and multiple microlenses with the same refractive power are set in each defocus correction zone.

[0007] Furthermore, all microlenses within the defocus correction zone have the same diameter.

[0008] Furthermore, the diameter of the microlenses ranges from 100 micrometers to 1 millimeter.

[0009] A method for designing hyperopia correction glasses based on refractive topography includes the following steps:

[0010] S1. Obtain the refractive power sampling values ​​of the patient's eye equivalent image at different positions on the retina;

[0011] S2. Establish a polar coordinate system with the geometric center of the non-defocused area as the pole;

[0012] S3. Determine the polar coordinates of the center point of each correction zone within the defocused stimulation zone;

[0013] S4. Determine the refractive power of each microlens within the correction zone.

[0014] Furthermore, in step S1, the method for obtaining the refractive power sampling values ​​of the patient's eye equivalent image at different locations on the retina is as follows: sampling is performed on multiple concentric circles in a coordinate system with the center of the macula as the origin. The sampling points closest to the center of the macula are designated as the first group, and the group numbers increase sequentially from the center outwards. Sampling points in the same group are evenly distributed on the concentric circles, and the examination value at each point is the refractive power difference value relative to the refraction power. , The sampling point represents the spatial angle relative to the center of the eyeball, ranging from 0 to 90°, where m is the subscript for the sampling group. The azimuth angle of the sampling point in a Cartesian coordinate system with the center of the macula as the origin is 0 to 360°, and n is the subscript of different sampling points in the same group.

[0015] Furthermore, in step S2, a polar coordinate system is established with the geometric center of the non-defocused area as the pole, and the diameter of the non-defocused area is... Satisfying the formula:

[0016] Where VD is vertex distance, AL is axial length, CCT is corneal thickness, ACD is anterior chamber depth, and LT is lens thickness. The diameter of the macular region must be determined based on the patient's examination results.

[0017] Furthermore, in step S3, the polar coordinates of the center point of each correction zone within the defocus stimulation zone are determined. From the formula: .

[0018] Furthermore, in step S4, the refractive power of each microlens within the correction zone is determined by the following formula:

[0019] , where exp is an exponential function with the natural constant e as its base.

[0020] The beneficial effects of this invention are:

[0021] This invention innovatively combines multifocal defocus theory with multispectral refractive topography (MRT) data to propose a progressive defocus lens that is personalized based on the patient's refractive topography examination data, promoting axial elongation in patients with axial hyperopia. Based on the patient's MRT peripheral defocus test results, this invention employs individualized, full-eye customization technology to ensure precise matching between the lens and the peripheral defocus of the retina. This personalized customization can precisely adjust the amount of defocus in different areas of the eye, returning it to a comfortable zone and forming an ideal hyperopic defocus state, thereby enhancing its effect on promoting axial elongation and treating hyperopia. Attached Figure Description

[0022] Figure 1 This is a schematic diagram of the lens structure of the farsightedness correction glasses of the present invention.

[0023] Figure 2 This is the refractive topographic map of the present invention.

[0024] Figure 3 This is a diagram showing the setting of the correction zone in this invention.

[0025] Figure 4 This is the refractive topography map of the right eye in Embodiment 1 of the present invention.

[0026] Figure 5 This is the refractive topography map of the left eye in Embodiment 1 of the present invention.

[0027] Figure 6 This is the refractive topography map of the right eye in Embodiment 2 of the present invention.

[0028] Figure 7 This is the refractive topography map of the left eye in Embodiment 2 of the present invention.

[0029] Explanation of reference numerals in the attached figures:

[0030] 1. No defocus area; 2. Defocus stimulation area. Detailed Implementation

[0031] The technical solution of the present invention will be described in detail below with reference to the accompanying drawings. The following embodiments are merely exemplary and can only be used to explain and illustrate the technical solution of the present invention, and should not be construed as limiting the technical solution of the present invention.

[0032] like Figure 1 As shown, the hyperopia correction glasses designed in this invention have a lens structure with two functional zones. The base lens is a positive lens configured based on the user's cycloplegic refraction results, and its refractive power is determined according to the patient's hyperopia refractive power under cycloplegia, consistent with the principles of traditional hyperopia glasses fitting. The central part is the non-defocus zone 1, the center of which should be aligned with the center of the patient's macula when the patient is wearing glasses normally and looking straight ahead. The annular area outside the non-defocus zone 1 is the defocus stimulation zone 2, the geometric center of which coincides with the center of the non-defocus zone 1. This area has multiple defocus correction zones set on the base lens, and each correction zone has multiple microlenses with the same refractive power. The diameter of the microlenses in all correction zones is the same, ranging from 100 micrometers to 1 millimeter. The arrangement should ensure that the total coverage area of ​​the microlenses is maximized without overlap between them.

[0033] Figure 2 The image shown is a typical refractive topography test result, reflecting the refractive power sampling values ​​of the patient's eye at different locations on the retina in an equivalent imaging configuration. The sampling method typically involves sampling on multiple concentric circles within a coordinate system with the center of the macula as the origin. The sampling points closest to the center of the macula form the first group, with the group numbers increasing sequentially outwards. Sampling points within the same group are evenly distributed on the concentric circles, and the value at each point represents the difference in refractive power relative to the refraction prescription. , The sampling point is the spatial angle relative to the center of the eyeball, ranging from 0 to 90°, and m is the subscript of the sampling group. The azimuth angle of the sampling point in a Cartesian coordinate system with the center of the macula as the origin is 0 to 360°, and n is the subscript of different sampling points in the same group.

[0034] A polar coordinate system is established with the geometric center of the 1-defocused zone of the defocused glasses as the pole. The diameter of the 1-defocused zone is also considered. It should satisfy formula (1):

[0035] (1)

[0036] Where VD is vertex distance, AL is axial length, CCT is corneal thickness, ACD is anterior chamber depth, and LT is lens thickness. The diameter of the macular region must be determined based on the patient's examination results.

[0037] Figure 3 This is a schematic diagram of the correction zone setup. The total number of correction zones within defocus stimulation zone 2 is the same as the number of sampling points in the refractive topography examination. The center point of each correction zone... The polar coordinates are determined by formula (2):

[0038] (2)

[0039] The range of the m-th correction zone is a ring-shaped portion between two concentric circles of different sizes, centered at the pole. The radius of the inner concentric circle is the midpoint between the central polar diameter of this group of correction zones and the central polar diameter of the previous group of correction zones, and the radius of the outer concentric circle is the midpoint between the central polar diameter of this group of correction zones and the central polar diameter of the next group of correction zones. Specifically, the radius of the inner concentric circle defining the range of the 1-th correction zone is equal to the radius of the non-defocus zone 1, and the outer range of the last group of correction zones is defined by the edge of the base lens.

[0040] Each correction zone within the same group is a fan-shaped annular region divided into the annular part corresponding to the correction zone of this group by two rays emanating from the pole at different angles. The polar angle values ​​of the two rays are the midpoint between the central polar angle of the correction zone and the central polar angle of the two adjacent correction zones in the same group.

[0041] The refractive power of each microlens within the correction zone is determined by formula (3):

[0042] (3)

[0043] Where exp is an exponential function with the natural constant e as its base.

[0044] Example 1

[0045] The patient's right eye examination results are as follows: axial length 20.73 mm, anterior chamber depth 3.42 mm, corneal thickness 0.48 mm, lens thickness 3.2 mm, macular diameter 6.0 mm, vertex distance 12.0 mm, and the prescribed refractive power is +6.00D. The refractive topography results and defocus lens design results are as follows: Figure 4 As shown, the diameter of the defocused area of ​​the lens is 11.43 mm, and the diameter of the microlens is set to 200 micrometers.

[0046] The patient's left eye examination results were as follows: axial length 19.68 mm, anterior chamber depth 3.38 mm, corneal thickness 0.45 mm, lens thickness 3.1 mm, macular diameter 6.0 mm, vertex distance 12.0 mm, and the prescribed refractive power was +6.75D. The refractive topography results and defocus lens design results are as follows: Figure 5As shown, the diameter of the defocused area of ​​the lens is 11.72 mm, and the diameter of the microlens is set to 200 micrometers.

[0047] Example 2

[0048] The patient's right eye examination results are as follows: axial length 21.49 mm, anterior chamber depth 3.44 mm, corneal thickness 0.5 mm, lens thickness 3.2 mm, macular diameter 6.0 mm, vertex distance 12.0 mm, and the prescribed refractive power is +4.00D. The refractive topography results and defocus lens design results are as follows: Figure 6 As shown, the diameter of the defocused area of ​​the lens is 11.21 mm, and the diameter of the microlens is set to 300 micrometers.

[0049] The patient's left eye examination results were as follows: axial length 20.54 mm, anterior chamber depth 3.41 mm, corneal thickness 0.5 mm, lens thickness 3.2 mm, macular diameter 6.0 mm, vertex distance 12.0 mm, and the prescribed refractive power was +6.5D. The refractive topography results and defocus lens design results are as follows: Figure 7 As shown, the diameter of the defocused area of ​​the lens is 11.49 mm, and the diameter of the microlens is set to 300 micrometers.

[0050] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and not to limit them. Although the present invention has been described in detail with reference to preferred embodiments, those skilled in the art should understand that modifications or equivalent substitutions can still be made to the technical solutions of the present invention, and these modifications or equivalent substitutions cannot cause the modified technical solutions to deviate from the scope of the technical solutions of the present invention.

Claims

1. A hyperopia correction eyeglass based on refractive topography, characterized by a lens structure with two-level functional zones, wherein... The system includes a base lens, which is a positive lens configured based on the patient's cycloplegic refraction results. Its refractive power is determined according to the patient's hyperopic refractive power due to cycloplegia. The central part of the base lens is a non-defocus zone, the center of which ensures that it is aligned with the center of the patient's retinal macular region when the patient is wearing glasses normally and looking straight ahead. The annular area outside the non-defocus zone is a defocus stimulation zone, the geometric center of which coincides with the center of the non-defocus zone. Multiple defocus correction zones are set on the base lens within the defocus stimulation zone, and multiple microlenses with the same refractive power are set in each defocus correction zone.

2. The hyperopia correction glasses based on refractive topography according to claim 1, characterized in that, All microlenses in the defocus correction zone have the same diameter.

3. The hyperopia correction glasses based on refractive topography according to claim 1, characterized in that, The diameter of the microlenses ranges from 100 micrometers to 1 millimeter.

4. A method for designing hyperopia correction glasses based on refractive topography, characterized in that, Includes the following steps: S1. Obtain the refractive power sampling values ​​of the patient's eye equivalent image at different positions on the retina; S2. Establish a polar coordinate system with the geometric center of the non-defocused area as the pole; S3. Determine the polar coordinates of the center point of each correction zone within the defocused stimulation zone; S4. Determine the refractive power of each microlens within the correction zone.

5. The design method for hyperopia correction glasses based on refractive topography according to claim 4, characterized in that, In step S1, the method for obtaining the refractive power sampling values ​​of the patient's eye at different locations on the retina in equivalent imaging is as follows: sampling is performed on multiple concentric circles in a coordinate system with the center of the macula as the origin. The sampling points closest to the center of the macula are designated as the first group, and the group numbers increase sequentially from the center outwards. Sampling points in the same group are evenly distributed on the concentric circles, and the examination value at each point is the refractive power difference relative to the refraction power. , The sampling point represents the spatial angle relative to the center of the eyeball, ranging from 0 to 90°, where m is the subscript for the sampling group. The azimuth angle of the sampling point in a Cartesian coordinate system with the center of the macula as the origin is 0 to 360°, and n is the subscript of different sampling points in the same group.

6. The design method for hyperopia correction glasses based on refractive topography according to claim 4, characterized in that, In step S2, a polar coordinate system is established with the geometric center of the non-defocused area as the pole, and the diameter of the non-defocused area is... Satisfying the formula: Where VD is vertex distance, AL is axial length, CCT is corneal thickness, ACD is anterior chamber depth, and LT is lens thickness. The diameter of the macular region must be determined based on the patient's examination results.

7. The design method for hyperopia correction glasses based on refractive topography according to claim 4, characterized in that, In step S3, the polar coordinates of the center point of each correction zone within the defocus stimulation zone are determined. From the formula: .

8. The design method for hyperopia correction glasses based on refractive topography according to claim 4, characterized in that, In step S4, the refractive power of each microlens within the correction zone is determined by the following formula: , where exp is an exponential function with the natural constant e as its base.

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