Lens design method and lens capable of correcting high-order aberrations of human eyes

Abstract

The present invention belongs to the field of ophthalmic optics technology, and relates to a lens design method and lens that can correct high-order aberrations of the human eye. The parameters of the basic eye model are adjusted to obtain a target basic eye model; the surface shape of the front surface of the lens and the surface shape of the front surface of the cornea in the target basic eye model are optimized to obtain a fitting eye model; a paraxial surface is placed on the front surface of the fitting eye model, and the vitreous depth of the fitting eye model is adjusted to obtain a target fitting eye model and remove the paraxial surface; the rotation angle of the eyeball in the target fitting eye model is changed to obtain a target eye model at different rotation angles; with the goal that the high-order aberration values ​​of the light when imaging on the target eye model at different rotation angles after passing through the lens to be optimized are all less than or equal to a second preset threshold, the parameters of the lens to be optimized are optimized to obtain a lens that can correct high-order aberrations of the human eye. The lens that can correct high-order aberrations of the human eye provided by this solution can effectively correct high-order aberrations generated by far-axis light and light outside the optical axis field of view.

Description

Technical Field

[0001] The present invention relates to the technical field of ophthalmic optics, and in particular to a lens design method and lens capable of correcting high-order aberrations of the human eye. Background Art

[0002] The human eye, as a visual imaging system, is a complex optical system. In addition to defocus and astigmatism, the human eye's optical system also suffers from other irregular higher-order aberrations, such as spherical aberration, coma, and trefoil. For the average person, these higher-order aberrations account for approximately 17% to 20% of total refractive error. Even after traditional refractive correction, these higher-order aberrations are the primary cause of poor overall visual quality, leading to decreased visual acuity, reduced contrast sensitivity, poor night vision, and glare.

[0003] Research teams at home and abroad have made some progress in correcting higher-order aberrations of the human eye. Because the human pupil is typically small, the light entering the eye in this state is primarily paraxial. Therefore, existing lenses designed to correct higher-order aberrations only consider correcting higher-order aberrations generated by paraxial light, resulting in a relatively small correction range. However, the size of the human pupil varies under different lighting conditions. For example, in dim environments, the pupil dilates, and higher-order aberrations become more pronounced. Consequently, when the wearer's pupil diameter exceeds the effective correction range of the corrective lens, the lens's correction effect on higher-order aberrations is significantly reduced, thereby affecting the wearer's visual quality. Furthermore, when the wearer's eyeball rotates, the angle at which light enters the eye is no longer along the optical axis, and the resulting higher-order aberrations are no longer solely along the optical axis. Existing lenses designed to correct higher-order aberrations focus solely on correcting higher-order aberrations within the optical axis, ignoring the impact of higher-order aberrations generated by eye rotation on image quality.

[0004] In summary, existing correctable high-order aberration lenses are not designed to correct high-order aberrations caused by far-axis light and light outside the optical axis field of view. As a result, the correctable high-order aberration lenses have poor correction effect on high-order aberrations when the wearer has a large pupil diameter or the eyeball moves, affecting the wearer's visual quality. Summary of the Invention

[0005] To this end, the technical problem to be solved by the present invention is to overcome the problem that the correctable high-order aberration lenses in the prior art do not take into account the correction effect of high-order aberrations generated by far-axis light and light outside the optical axis field of view during design, resulting in the correctable high-order aberration lenses having poor correction effect on high-order aberrations when the wearer has a large pupil diameter or the eyeball rotates, thereby affecting the wearer's visual quality.

[0006] To solve the above technical problems, the present invention provides a lens design method capable of correcting high-order aberrations of the human eye, comprising:

[0007] Obtaining a basic eye model, adjusting the pupil diameter of the basic eye model to the pupil diameter for measuring naked eye wavefront aberration, and adjusting the curvature radius of the anterior and posterior corneal surfaces, corneal thickness, anterior chamber depth, lens thickness, vitreous depth, and axial length of the eye in the basic eye model to values ​​measured in a dark environment, to obtain a target basic eye model;

[0008] Optimizing the surface shapes of the anterior surface of the lens and the anterior surface of the cornea in the target basic eye model using a ZERN optimization function until the difference between the high-order aberration value and the target wave aberration value when light is imaged on the target basic eye model is less than a first preset threshold, thereby obtaining a fitted eye model;

[0009] placing a paraxial surface on the front surface of the fitting eye model, and adjusting the vitreous depth of the fitting eye model with the goal of minimizing the defocus aberration value on the retina when light is imaged on the fitting eye model, to obtain a target fitting eye model and remove the paraxial surface;

[0010] Changing the rotation angle of the eyeball in the target fitting eye model to obtain target eye models at different rotation angles;

[0011] A lens to be optimized is obtained, and parameters of the lens to be optimized are optimized with the goal that the high-order aberration values ​​of light when imaging on a target eye model at different rotation angles after passing through the lens to be optimized are all less than or equal to a second preset threshold value, so as to obtain a lens that can correct high-order aberrations of the human eye.

[0012] Preferably, the surface of the lens to be optimized close to the target eye model is a Zernike annular phase surface, and the surface away from the target eye model is a spherical surface;

[0013] The surface expression of the Zernike annular phase surface is:

[0014] ,

[0015] in, The Zernike annular phase plane The sag at each sampling point; represents the vertex curvature of the Zernike annular phase surface; The Zernike annular phase plane The radial distance of each sampling point from the optical axis; represents the cone coefficient of the Zernike annular phase surface; represents the number of Zernike polynomials; Indicates the The coefficients of the Zernike polynomials; Indicates the The basic aberration function of Zernike polynomials; represents the normalized radial coordinate of the Zernike annular phase plane; represents the angular coordinate of the Zernike annular phase plane.

[0016] Preferably, optimizing the parameters of the lens to be optimized includes:

[0017] The cone coefficient of the Zernike annular phase surface is adjusted using the default wavefront optimization function, and the coefficients of the 4th to 37th Zernike polynomials in the Zernike annular phase surface are adjusted using the ZERN optimization function, thereby changing the surface shape of the Zernike annular phase surface until the high-order aberration values ​​when the light passes through the lens to be optimized and is imaged on the target eye model at each rotation angle are less than or equal to the second preset threshold.

[0018] Preferably, after obtaining the lens capable of correcting high-order aberrations of the human eye, the method further comprises:

[0019] The SDVR operation function is used to adjust the tangent slope and curvature change rate of the lens capable of correcting high-order aberrations of the human eye until the difference between the first-order derivative value of the anti-curvature coordinate point and the first-order derivative value of the rotationally symmetric coordinate point of the lens capable of correcting high-order aberrations of the human eye is equal to 0, thereby obtaining an optimized lens capable of correcting high-order aberrations of the human eye.

[0020] Preferably, after obtaining the lens capable of correcting high-order aberrations of the human eye, the method further comprises:

[0021] The POWP operation function is used to optimize the refractive power distribution of the lens capable of correcting high-order aberrations of the human eye until the refractive power at a preset aperture of the lens capable of correcting high-order aberrations of the human eye is less than or equal to a preset ratio of the refractive power at the center point of the lens capable of correcting high-order aberrations of the human eye, thereby obtaining an optimized lens capable of correcting high-order aberrations of the human eye.

[0022] Preferably, the surface shape of the anterior corneal surface in the target basic eye model is a Zernike edge sag surface, which is expressed as:

[0023] ,

[0024] in, The first The sag at each sampling point; It represents the vertex curvature of the anterior corneal surface; The first The radial distance of each sampling point from the optical axis; Indicates the cone coefficient of the anterior corneal surface; Indicates the number of even-order aspheric coefficients in the anterior corneal surface; Indicates the first even aspheric surface on the anterior corneal surface coefficients; represents the number of Zernike fringe polynomials in the anterior corneal surface; The anterior corneal surface The coefficients of the Zernike marginal polynomials; The anterior corneal surface The basic aberration function of the Zernike edge polynomial; represents the normalized radial coordinate of the anterior corneal surface; Represents the angular coordinate of the anterior surface of the cornea.

[0025] Preferably, optimizing the surface shape of the front surface of the lens and the front surface of the cornea in the target basic eye model using the ZERN optimization function includes:

[0026] The ZERN optimization function is used to sequentially adjust the curvature radius of the anterior surface of the lens, the coefficients of the 4th to the 18th, and the 25th Zernike marginal polynomials in the anterior surface of the cornea, thereby changing the surface shape of the anterior surface of the lens and the surface shape of the anterior surface of the cornea until the difference between the high-order aberration value and the target wave aberration value when the light is imaged on the target basic eye model is less than a first preset threshold.

[0027] Preferably, obtaining a basic eye model includes:

[0028] Get the Liou eye model;

[0029] A thin lens is placed on the front surface of the lens in the Liou eye model to obtain a basic eye model.

[0030] The present invention further provides a lens capable of correcting high-order aberrations of the human eye. The lens capable of correcting high-order aberrations of the human eye is designed by the above-mentioned lens design method capable of correcting high-order aberrations of the human eye, and specifically comprises:

[0031] The on-axis high-order aberration correction area is a circular area with the center point of the lens capable of correcting high-order aberrations of the human eye as the center, and is used to correct the high-order aberrations of the human eye in the on-axis field of view;

[0032] The off-axis high-order aberration correction zone is a circular area outside the axial high-order aberration correction zone, and is used to correct high-order aberrations caused by the rotation of the human eye;

[0033] The processing control area is a circular area on the side of the off-axis high-order aberration correction area away from the axial high-order aberration correction area, and is used to control the aperture of the lens that can correct high-order aberrations of the human eye.

[0034] Preferably, the radius of the on-axis high-order aberration correction zone is less than or equal to 4 mm;

[0035] With the center point of the lens capable of correcting high-order aberrations of the human eye as the center of the circle, the radius of the outer ring of the off-axis high-order aberration correction area is less than or equal to 25 mm;

[0036] With the center point of the lens capable of correcting high-order aberrations of the human eye as the center of the circle, the radius of the outer ring of the processing control area is less than or equal to 40 mm.

[0037] The lens design method for correcting high-order aberrations of the human eye provided in the present application first adjusts the basic eye model based on the pupil diameter of the naked eye wave aberration and various eye parameters in a dark environment, so that the adjusted target basic eye model can accurately reflect the refraction of light entering the human eye and on various structures in the eye under a large pupil diameter, thereby using the target basic eye model to simulate the high-order aberrations generated under a large pupil diameter, so that the lens designed based on the target basic eye model can also effectively control the refraction of light and reduce high-order aberrations when the pupil is large; since the front surface of the cornea is the surface where light enters, The first major refractive interface of the human eye is also the source of most aberrations when the human eye is imaging. Therefore, the present application uses the ZERN function to optimize the surface shape of the anterior surface of the cornea, so that the difference between the high-order aberration value and the target wave aberration value when the light is imaged on the target basic eye model is less than the first preset threshold value, thereby making the imaging effect of the target basic eye model closer to the imaging effect of the human eye, and making the design of the lens that can correct the high-order aberration of the human eye more in line with the correction needs of the human eye; since the spherical power of the human eye is closely related to the axial length of the eye, when the axial length is too long or too short, it will produce deviations. The defocus aberration of the eye can be corrected by adjusting the vitreous depth, which can change the propagation path and focusing position of the light in the eye, thereby compensating for the defocus problem caused by the axial length of the eye. Therefore, the present application places a paraxial surface on the front surface of the fitting eye model to establish a focal length reference based on the optometry spherical power, to assist in correcting the defocus aberration of the fitting eye model, and to adjust the vitreous depth of the fitting eye model with the goal of minimizing the defocus aberration value on the retina when the light is imaged on the fitting eye model, so as to achieve the matching of the target fitting eye model with the human eye in terms of the spherical power of the eye, so that the target fitting eye model is more consistent with the real situation of the human eye. At the same time, in order to design a lens that can meet the correction needs of the human eye at different rotation angles, the present application constructs target eye models at different rotation angles to simulate the rotation of the human eye, and uses the target eye models at all rotation angles to jointly adjust the parameters of the lens to be optimized to obtain a lens that can correct high-order aberrations of the human eye. As a result, even when the wearer's pupil diameter is large or the eyeball rotates, the lens that can correct high-order aberrations of the human eye can still effectively correct the high-order aberrations generated by far-axis light and light outside the optical axis field of view, thereby improving the imaging quality and the wearer's visual clarity. BRIEF DESCRIPTION OF THE DRAWINGS

[0038] In order to make the content of the present invention more clearly understood, the present invention is further described in detail below based on specific embodiments of the present invention in conjunction with the accompanying drawings, wherein:

[0039] Figure 1 A flow chart of the lens design method for correcting high-order aberrations of the human eye provided in this application;

[0040] Figure 2 Schematic diagram of the structure of the lens that can correct high-order aberrations of the human eye provided in this application;

[0041] Figure 3 This is the optical path diagram of the lens provided in this application that can correct high-order aberrations of the human eye at different eye rotation angles; wherein, Figure 3 (a) is the optical path diagram of the lens that can correct high-order aberrations of the human eye when the eyeball rotates at an angle of 10°. Figure 3 (b) is the optical path diagram of the lens that can correct high-order aberrations of the human eye when the eyeball rotates at an angle of 0°. Figure 3 (c) is the optical path diagram of the lens that can correct high-order aberrations of the human eye when the eyeball rotates at an angle of -10°;

[0042] Figure 4 This is a schematic diagram of the parameters of the inner surface of the lens provided in this application that can correct high-order aberrations of the human eye; wherein, Figure 4 (a) is the sagittal cross-section of the inner surface of the lens that can correct high-order aberrations of the human eye within the full aperture of 72mm. Figure 4 (b) is the first-order derivative curve of the sagittal height cross-section of the inner surface of the lens that can correct high-order aberrations of the human eye within the full aperture of 72mm. Figure 4 (c) is the second-order derivative curve of the sagittal height cross-section of the inner surface of the lens that can correct high-order aberrations of the human eye within the full aperture of 72mm;

[0043] Figure 5 The average refractive power distribution diagram within a 40mm diameter area on the inner surface of the lens provided in this application that can correct high-order aberrations of the human eye;

[0044] Figure 6 The initial MTF curve diagram of the wearer's human eye imaging provided by this application;

[0045] Figure 7 This is the MTF curve diagram after correction using the lens capable of correcting high-order aberrations of the human eye provided by this application when the wearer's eyeball rotates at an angle of 10°;

[0046] Figure 8 This is an MTF curve diagram after correction using the lens capable of correcting high-order aberrations of the human eye provided by this application when the wearer's eye rotation angle is 0°;

[0047] Figure 9 This is the MTF curve diagram after correction using the lens capable of correcting high-order aberrations of the human eye provided by this application when the wearer's eyeball rotates at an angle of -10°;

[0048] Explanation of the accompanying drawings in the specification: 1. On-axis high-order aberration correction area; 2. Off-axis high-order aberration correction area; 3. Processing control area. DETAILED DESCRIPTION

[0049] The present invention will be further described below with reference to the accompanying drawings and specific embodiments so that those skilled in the art can better understand the present invention and implement it. However, the embodiments are not intended to limit the present invention.

[0050] See also Figure 1 , Figure 1 The present invention provides a lens design method for correcting high-order aberrations of the human eye, which specifically includes:

[0051] S10: Obtain a basic eye model, and adjust the pupil diameter of the basic eye model to the pupil diameter for measuring naked eye wavefront aberration, and adjust the curvature radius of the anterior and posterior surfaces of the cornea, corneal thickness, anterior chamber depth, lens thickness, vitreous depth, and axial length in the basic eye model to the measured values ​​in a dark environment to obtain a target basic eye model.

[0052] S20: Optimize the surface shapes of the anterior surface of the lens and the anterior surface of the cornea in the target basic eye model using the ZERN optimization function until the difference between the high-order aberration value and the target wave aberration value when the light is imaged on the target basic eye model is less than a first preset threshold, thereby obtaining a fitted eye model.

[0053] S30: placing a paraxial surface on the front surface of the fitting eye model, and adjusting the vitreous depth of the fitting eye model with the goal of minimizing the defocus aberration value on the retina when light is imaged on the fitting eye model, to obtain a target fitting eye model and remove the paraxial surface.

[0054] S40: changing the rotation angle of the eyeball in the target fitting eye model to obtain target eye models at different rotation angles.

[0055] S50: Obtain a lens to be optimized, and optimize the parameters of the lens to be optimized with the goal that the high-order aberration values ​​of the light when imaging on the target eye model at different rotation angles after passing through the lens to be optimized are all less than or equal to a second preset threshold value, so as to obtain a lens that can correct high-order aberrations of the human eye.

[0056] In a specific example of the present application, the value range of the second preset threshold is [-0.25, 0.25], and the unit is wavelength (waves).

[0057] Furthermore, obtaining the basic eye model includes:

[0058] Get the Liou eye model;

[0059] A thin lens was placed on the anterior surface of the lens in the Liou eye model to obtain a basic eye model.

[0060] Since the optical and physiological structures of the Liou eye model are very similar to those of the human eye, this application selects the Liou eye model to construct a basic eye model. By setting a thin lens on the front surface of the lens of the Liou eye model, the curvature radius of the lens can be better controlled when the parameters of the basic eye model are subsequently optimized and adjusted.

[0061] In a specific example of the present application, the thickness of the thin lens is , the refractive index is the refractive index value in the Gullstrand-Le Grand eye model. The parameters of the constructed basic eye model are shown in Table 1:

[0062] Table 1

[0063]

[0064] In Table 1, Grad represents the refractive index of the lens, which is a gradient refractive index. It consists of two parts, Grad A and Grad P, separated by a virtual surface. The expression of the virtual surface is:

[0065] ,

[0066] in, Represents the distance between Grad A and Grad P along the radial direction; Indicates the distance between Grad A and Grad P along the optical axis; ;Grad P part .

[0067] In order to enable the target basic eye model to accurately reflect the refraction of light entering the human eye and on various structures in the eye under a large pupil diameter, the target basic eye model is used to simulate the high-order aberrations generated under a large pupil diameter, so that the lens designed based on the target basic eye model can also effectively control the refraction of light and reduce high-order aberrations when the pupil is large. Therefore, this application adjusts the pupil diameter of the basic eye model to the pupil diameter for measuring naked eye wavefront aberrations in a dark environment, and at the same time gives the measurement value ranges of the curvature radius of the anterior and posterior surfaces of the cornea, corneal thickness, anterior chamber depth, lens thickness, vitreous depth and axial length in the basic eye model.

[0068] Specifically, the pupil diameter for measuring naked eye wavefront aberration in a dark environment is 4mm~8mm; the curvature radius of the anterior surface of the cornea is approximately 7.0mm~9.0mm, and the curvature radius of the posterior surface is approximately 6.0mm~8.0mm; the corneal thickness is 0.4mm~0.7mm; the anterior chamber depth is 2.6mm~4.5mm; the lens thickness is approximately 3.0mm~4.5mm; the vitreous depth is 15mm~20mm; and the axial length of the eye is 21mm~30mm.

[0069] In a specific example of this application, the pupil diameter of the target basic eye model is 5.5 mm, and other parameters are shown in Table 2:

[0070] Table 2

[0071] Human eye physiological parameters Value / mm Radius of curvature of the anterior corneal surface 8.300 Corneal posterior surface curvature radius 6.160 Corneal thickness 0.461 Anterior chamber depth 3.900 Lens thickness 3.410 Vitreous depth 19.209 Axial length 26.980

[0072] Furthermore, since the anterior surface of the cornea is the first major refractive interface for light entering the human eye and is also the source of most aberrations when the human eye forms an image, the anterior surface of the cornea is set to a Zernike edge sagittal surface in this application. Specifically, the surface is defined by an even-order aspheric surface plus an aspheric surface represented by a Zernike edge coefficient, wherein the radius of curvature of the even-order aspheric surface changes continuously from the center to the edge, and is a rotationally symmetric surface, representing the radial coordinate in units of lens length; the expression for the surface is:

[0073] ,

[0074] in, The first The sag at each sampling point; It represents the vertex curvature of the anterior corneal surface; The first The radial distance of each sampling point from the optical axis; Indicates the cone coefficient of the anterior corneal surface; Indicates the number of even-order aspheric coefficients in the anterior corneal surface; Indicates the first even aspheric surface on the anterior corneal surface coefficients; represents the number of Zernike fringe polynomials in the anterior corneal surface; The anterior corneal surface The coefficients of the Zernike marginal polynomials; The anterior corneal surface The basic aberration function of the Zernike edge polynomial; represents the normalized radial coordinate of the anterior corneal surface; Represents the angular coordinate of the anterior surface of the cornea.

[0075] Furthermore, by optimizing the surface shapes of the anterior surface of the lens and the anterior surface of the cornea using the ZERN function, the difference between the high-order aberration value and the target wave aberration value when the light is imaged on the target basic eye model is smaller than a first preset threshold value, thereby making the imaging effect of the target basic eye model closer to that of the human eye, and making the design of the lens capable of correcting high-order aberrations of the human eye more suitable for the correction needs of the human eye;

[0076] In some embodiments of the present application, optimizing the surface shapes of the anterior surface of the lens and the anterior surface of the cornea in the target basic eye model using the ZERN optimization function includes:

[0077] The ZERN optimization function is used to sequentially adjust the curvature radius of the anterior surface of the lens, the coefficients of the 4th to the 18th, and the 25th Zernike marginal polynomials on the anterior surface of the cornea, thereby changing the surface shapes of the anterior surface of the lens and the anterior surface of the cornea until the difference between the high-order aberration value and the target wave aberration value when the light is imaged on the target basic eye model is less than a first preset threshold.

[0078] Specifically, when optimizing the anterior surface of the lens and the anterior surface of the cornea, the coefficients of the Zernike marginal polynomials are adjusted sequentially from small to large in order to gradually fit the aberrations of the target basic eye model from low order to high order, so that the aberration values ​​of the optimized fitting eye model during imaging are closer to the aberration values ​​of the real human eye. At the same time, the coefficient of the 25th Zernike marginal polynomial corresponds to the high-order spherical aberration of the target basic eye model. Since the high-order spherical aberration is large and difficult to fit, the coefficient of the 25th Zernike marginal polynomial is also used as an optimization variable during fitting to control the high-order spherical aberration values ​​of the optimized fitting eye model to be closer to the high-order spherical aberration values ​​of the real human eye. Optionally, the coefficients of the Zernike marginal polynomials corresponding to the same aberration category and the same order can be adjusted simultaneously during optimization. For example, A7 and A8 both correspond to first-order coma values. During optimization, the values ​​of A7 and A8 can be adjusted simultaneously using the ZERN function.

[0079] Furthermore, the first preset threshold can be set based on actual conditions. The smaller this value, the closer the aberration data of the optimized fitted eye model during imaging is to the aberration data of the real human eye during imaging, indicating that the imaging effect of the fitted eye model is more consistent with that of the real human eye, and the designed lens is more able to meet the imaging requirements of the human eye. In some embodiments of the present application, the value range of the first preset threshold is [0, 0.02], with the unit being wavelength (waves). When the first preset threshold is 0, it indicates that the aberration of the fitted eye model during imaging is completely consistent with the aberration of the real human eye during imaging.

[0080] Table 3 shows a specific example of the present application, in which the aberration data of the fitted eye model obtained after optimizing the anterior corneal surface shape in the target basic eye model and the aberration data of the real human eye obtained by actual measurement during imaging are compared:

[0081] Table 3

[0082]

[0083] As can be seen from the table, the RMS value of the aberration data of the measured real human eye during imaging is 2.820 waves (the design wavelength is 0.55 μm), and the RMS value of the aberration data of the fitted eye model during imaging is 2.820 waves, indicating that the aberration data of the fitted eye model during imaging has completely converged to the same as the aberration data of the actual human eye during imaging.

[0084] It is worth noting that the RMS value refers to the root mean square value of the high-order aberration coefficients represented by the Zernike polynomials, and the unit is waves. Since the Zernike polynomials are an orthogonal and normalized function sequence in the unit circle domain, the coefficients of the Zernike polynomials can be directly used to describe the size of the RMS value. The specific calculation formula is: ,

[0085] in, Indicates the The coefficients of the Zernike polynomials.

[0086] Furthermore, it is also necessary to correct the relevant parameters of the fitting eye model so that the fitting eye model matches the real human eye in terms of optometry spherical power. Since the spherical power of the human eye is closely related to the axial length of the eye, defocus aberration will occur when the axial length is too long or too short. By adjusting the vitreous depth, the propagation path and focusing position of the light in the eye can be changed, thereby compensating for the defocus problem caused by the axial length of the eye. Therefore, the present application places a paraxial surface on the front surface of the fitting eye model. The paraxial surface can be regarded as an ideal thin lens to establish a focal length reference based on the spherical power of the eye to assist in correcting the defocus aberration of the fitting eye model. With the goal of minimizing the defocus aberration value on the retina when the light is imaged on the fitting eye model, the vitreous depth of the fitting eye model is adjusted to achieve matching of the target fitting eye model with the human eye in terms of spherical power of the eye, so that the target fitting eye model is more consistent with the actual situation of the human eye.

[0087] In a specific example of the present application, if the actual spherical power prescription value of a real human eye is +0.5D, the focal length of the paraxial plane is +2000mm, corresponding to the +0.5D optical power of the real human eye prescription, the vitreous depth in the fitting eye model is 19.209mm, and the vitreous depth in the target fitting eye model obtained after adjustment is 19.218mm.

[0088] Table 4 shows, in a specific example of the present application, the aberration data of the fitted eye model when imaging before adjusting the vitreous depth, and the aberration data of the target fitted eye model when imaging after adjusting the vitreous depth:

[0089] Table 4

[0090]

[0091] As can be seen from Table 4, the RMS value of the aberration data when imaging the fitted eye model before vitreous depth correction is 2.024 waves, and the RMS value of the aberration data when imaging the target fitted eye model after vitreous depth correction is 2.023 waves, indicating that the aberration data when imaging the eye model before and after vitreous depth correction remains basically unchanged and is still consistent with the aberration data when imaging the real human eye.

[0092] Furthermore, to ensure that the designed lenses meet the correction requirements of the human eye at different rotation angles, this application constructs target eye models at different rotation angles to simulate the rotation of the human eye. Specifically, by changing the rotation angle of the target fitting eye model in Zemax optical design software, multiple structures of the target fitting eye model at different rotation angles can be established, resulting in target eye models at different rotation angles. For example, the eyeball rotation angle can be 0°, 10°, 20°, 40°, or -10°, -20°, -40°, or any angle in between.

[0093] Furthermore, the target eye model at all rotation angles is used to jointly adjust the parameters of the lens to be optimized to obtain a lens that can correct high-order aberrations of the human eye. Optionally, the surface of the lens to be optimized can be a spherical surface, an aspherical surface, or a free-form surface. In some embodiments of the present application, the lens to be optimized is a combination of a spherical surface and a free-form surface, and the free-form surface is a Zernike annular phase surface, that is, the surface of the lens to be optimized close to the target eye model is a Zernike annular phase surface, and the surface away from the target eye model is a spherical surface.

[0094] Among them, the surface expression of the Zernike annular phase surface is:

[0095] ,

[0096] in, The Zernike annular phase plane The sag at each sampling point; represents the vertex curvature of the Zernike annular phase surface; The Zernike annular phase plane The radial distance of each sampling point from the optical axis; represents the cone coefficient of the Zernike annular phase surface; represents the number of Zernike polynomials; Indicates the The coefficients of the Zernike polynomials; Indicates the The basic aberration function of Zernike polynomials; represents the normalized radial coordinate of the Zernike annular phase plane; represents the angular coordinate of the Zernike annular phase plane.

[0097] Furthermore, optimizing the parameters of the lens to be optimized includes:

[0098] The cone coefficient of the Zernike annular phase surface is adjusted using the default wavefront optimization function, and the coefficients of the 4th to 37th Zernike polynomials in the Zernike annular phase surface are adjusted using the ZERN optimization function, thereby changing the surface shape of the Zernike annular phase surface until the high-order aberration values ​​when the light passes through the lens to be optimized and is imaged on the target eye model at each rotation angle are all less than or equal to the second preset threshold.

[0099] Furthermore, to ensure the processability of the lens, the lens's sagittal change also needs to be considered. Whether the lens's sagittal change is uniform depends on the continuity of its surface curvature change. Therefore, after obtaining a lens that can correct high-order aberrations of the human eye, the following also needs to be considered:

[0100] The SDVR operation function is used to adjust the tangent slope and curvature change rate of the lens that can correct high-order aberrations of the human eye until the difference between the first-order derivative value of the anti-curvature coordinate point and the first-order derivative value of the rotationally symmetric coordinate point of the lens that can correct high-order aberrations of the human eye is equal to 0, thereby obtaining the optimized lens that can correct high-order aberrations of the human eye.

[0101] Furthermore, if the refractive power of the lens changes too quickly, it will affect the visual stability of the human eye when worn, thereby affecting the wearer's comfort. Therefore, in some embodiments of the present application, after obtaining the lens capable of correcting high-order aberrations of the human eye, the following steps are further included:

[0102] The POWP operation function is used to optimize the refractive power distribution of the lens capable of correcting high-order aberrations of the human eye, until the refractive power at a preset aperture of the lens capable of correcting high-order aberrations of the human eye is less than or equal to a preset ratio of the refractive power at the center point of the lens capable of correcting high-order aberrations of the human eye, thereby obtaining an optimized lens capable of correcting high-order aberrations of the human eye.

[0103] In a specific example of the present application, the refractive index of the lens to be optimized is 1.597, the Abbe number is 40, the center thickness is 2 mm, the aperture is 72 mm, the eye relief is 13 mm, and the wearer is +0.5D. Since 4-curve plates are commonly used in the industry, the curvature radius of the spherical surface of the lens to be optimized is 147.871 mm. Then, the surface shape of the Zernike annular phase surface of the lens to be optimized is adjusted to obtain a lens that can correct high-order aberrations of the human eye, and the tangent slope and curvature change rate of the Zernike annular phase surface of the lens that can correct high-order aberrations of the human eye are adjusted. Finally, by controlling the refractive power at the 40 mm aperture of the Zernike annular phase surface to be less than or equal to 10% of the refractive power at the center point, it is ensured that the refractive power change of the lens that can correct high-order aberrations of the human eye is controlled within a small range, thereby improving the wearing comfort of the wearer. Table 5 shows the parameters of the lens that can correct high-order aberrations of the human eye:

[0104] Table 5

[0105] parameter Outer surface of glasses inner surface of glasses Surface type spherical surface Zernike annular phase plane Curvature radius / mm 147.871 167.791 Cone coefficient / -8.000 Zernike 4 / mm / <![CDATA[-7.705×10 -2 ]]> Zernike 5 / mm / <![CDATA[-6.856×10 -4 ]]> Zernike 6 / mm / <![CDATA[-9.986×10 -2 ]]> Zernike 7 / mm / <![CDATA[-4.082×10 -3 <!-- 10 -->]]> Zernike 8 / mm / <![CDATA[4.759×10 -3 ]]> Zernike 9 / mm / <![CDATA[-9.591×10 -3 ]]> Zernike 10 / mm / <![CDATA[-9.645×10 -4 ]]> Zernike 11 / mm / <![CDATA[-3.562×10 -2 ]]> Zernike 12 / mm / <![CDATA[-4.137×10 -2 ]]> ... / ... Zernike 36 / mm / <![CDATA[-4.419×10 -4 ]]> Zernike 37 / mm / <![CDATA[-5.951×10 -4 ]]>

[0106] It is worth noting that the ZERN operation function, SDVR operation function and POWP operation function used in this application are all optimization operation functions unique to Zemax software.

[0107] The present application also provides a lens designed using the method provided in the above embodiment that can correct high-order aberrations of the human eye, such as Figure 2 As shown, it specifically includes an on-axis high-order aberration correction area 1, an off-axis high-order aberration correction area 2 and a processing control area 3.

[0108] The on-axis high-order aberration correction area 1 is a circular area with the center point of the lens capable of correcting high-order aberrations of the human eye as the center, and is used to correct the high-order aberrations of the human eye in the on-axis field of view.

[0109] The off-axis high-order aberration correction zone 2 is a circular area outside the axial high-order aberration correction zone 1, and is used to correct high-order aberrations generated by the rotation of the human eye.

[0110] The processing control area 3 is a circular area on the side of the off-axis high-order aberration correction area 2 away from the axial high-order aberration correction area 1, and is used to control the aperture of the lens that can correct high-order aberrations of the human eye.

[0111] Furthermore, in some embodiments of the present application, the radius of the on-axis high-order aberration correction zone 1 is less than or equal to 4 mm.

[0112] With the center point of the lens capable of correcting high-order aberrations of the human eye as the center of the circle, the radius of the outer ring of the off-axis high-order aberration correction area 2 is less than or equal to 25 mm.

[0113] With the center point of the lens capable of correcting high-order aberrations of the human eye as the center of the circle, the radius of the outer ring of the processing control area 3 is less than or equal to 40 mm.

[0114] The correction effect of the lens for correcting high-order aberrations of the human eye provided by the present application on high-order aberrations is verified by a specific example below.

[0115] In this embodiment, the eye rotation center of the target fitting eye model is set at 14 mm behind the anterior surface of the cornea, and the eye rotation angle is controlled to 0°, 10° and -10°, thereby obtaining target eye models of 0°, 10° and -10°. The target eye model is used to adjust the surface shape, tangent slope, curvature change rate and refractive power distribution of the Zernike annular phase surface of the lens to be optimized, thereby obtaining a lens that can correct high-order aberrations of the human eye. The on-axis high-order aberration correction area of ​​the lens that can correct high-order aberrations of the human eye is a circular area with a radius of 3 mm and the midpoint of the lens as the center, the off-axis high-order aberration correction area is a circular area with a diameter greater than 6 mm to equal to 17 mm from the center of the lens, and the processing control area is a circular area with a diameter greater than 17 mm to equal to 72 mm from the center of the lens.

[0116] like Figure 3 The figure shows the optical path diagram of the lens capable of correcting high-order aberrations of the human eye obtained in this embodiment at different rotation angles, wherein: Figure 3 (a) is the optical path diagram of the lens that can correct high-order aberrations of the human eye when the eyeball rotates at an angle of 10°. The area where the central field of view light passes through the lens is a circular area with a diameter of 6mm from the center of the lens, that is, the on-axis high-order aberration correction area; Figure 3 (b) is the optical path diagram of the lens that can correct high-order aberrations of the human eye when the eyeball rotates at an angle of 0°. Figure 3 (c) is the optical path diagram of the lens that can correct the high-order aberration of the human eye when the eyeball rotates at an angle of -10°. Figure 3 (a) in the equation, Figure 3 (a) and Figure 3 In (c), the area where the central field light passes through the lens is expanded to 17 mm in diameter from the center of the lens, that is, the central field light at a rotation angle of ±10° covers the on-axis high-order aberration correction area and the off-axis high-order aberration correction area.

[0117] like Figure 4 FIG. 1 is a schematic diagram showing parameters of the inner surface of the lens obtained in this embodiment that can correct high-order aberrations of the human eye; wherein, Figure 4 (a) is the sagittal cross-section of the inner surface of the lens that can correct high-order aberrations of the human eye within the full aperture of 72mm. Figure 4 (b) is the first-order derivative curve of the sagittal height cross-section of the inner surface of the lens that can correct high-order aberrations of the human eye within the full aperture of 72mm. Figure 4 (c) is the second-order derivative curve of the sagittal height cross-section of the inner surface of the lens that can correct high-order aberrations of the human eye within the full aperture of 72mm. Figure 4It can be seen that there are no extra inflection points in the entire sagittal interface curve, and its first-order derivative and second-order derivative change continuously, indicating that the surface curvature of the lens is continuous and the lens sagittal transitions smoothly within the entire aperture.

[0118] like Figure 5 This is a diagram showing the average refractive power distribution within a 40mm diameter area on the inner surface of the lens obtained in this embodiment that can correct high-order aberrations of the human eye. As can be seen from the figure, the central refractive power of the lens is -3.55D, the refractive power at the 40mm aperture is -3.20D, and the refractive power change is 0.35D, which is 9.86% relative to the central refractive power, meeting the requirements of lens processability and wearing comfort for the human eye.

[0119] Table 6 shows the Zernike polynomial values ​​of the higher-order aberrations Z7 to Z18 when the wearer is looking straight ahead before wearing the lens capable of correcting higher-order aberrations of the human eye according to this embodiment, and the Zernike polynomial values ​​of the higher-order aberrations Z7 to Z18 when the wearer is looking straight ahead after wearing the lens capable of correcting higher-order aberrations of the human eye according to this embodiment:

[0120] Table 6

[0121]

[0122] It can be seen that under direct vision, the RMS values ​​of higher-order aberrations (coefficients of terms Z7-Z18) decreased by 41.72% compared to before wearing the lens that corrects higher-order aberrations. In particular, spherical aberration (Z9), which accounts for a large proportion of the total higher-order aberrations, decreased from -1.024 waves to -0.559 waves, a decrease of 45.41%. The absolute value of the sum of first-order coma aberrations (Z7 and Z8) decreased from 1.273 waves to 0.592 waves, a decrease of 53.50%. The trefoil aberration at 45° and 135° decreased from 0.298 waves to 0.259 waves, a decrease of 13.09%. Furthermore, other aberrations, such as second-order coma and trefoil aberrations, were already at low levels before correction, but their values ​​increased during the optimization design process due to the need to consider peripheral vision quality. However, the magnitude of these aberration coefficients is still controlled within a quarter wavelength (i.e. less than 0.25 waves), which has little impact on the overall visual quality.

[0123] like Figure 6 The figure shows the initial MTF curve of the wearer's human eye when imaging according to this embodiment. Figure 7 This is the MTF curve diagram after correction using the lens capable of correcting high-order aberrations of the human eye provided by this application when the wearer's eyeball rotates at an angle of 10°. Figure 8 This is the MTF curve diagram after correction using the lens capable of correcting high-order aberrations of the human eye provided by this application when the wearer's eyeball rotation angle is 0°. Figure 9 This is the MTF curve diagram after correction using the lens capable of correcting high-order aberrations of the human eye provided in this application when the wearer's eye rotation angle is -10°.

[0124] from Figures 6 to 9 It can be seen that in the low-frequency and medium-frequency stages (i.e., the spatial frequency range is 0~50lp / mm), whether looking straight ahead or with eye movement, the average MTF values ​​in the meridional and sagittal directions are significantly improved compared with the case of looking straight ahead without wearing lenses that can correct high-order aberrations of the human eye, with the improvement ranging from 13% to 66%. In the high-frequency stage (i.e., the spatial frequency range is 50~100lp / mm), the average MTF values ​​in the meridional and sagittal directions are also slightly improved after correction, with the improvement ranging from 1% to 3%.

[0125] Table 7 shows the MTF values ​​in the meridian and sagittal directions at different spatial frequencies before and after correction by lenses that can correct high-order aberrations of the human eye when the wearer's eyeballs rotate at angles of 10°, 0°, and -10°:

[0126] Table 7

[0127]

[0128] From the data in Table 7, it can be seen that compared with the situation of direct vision before correction, the average MTF values ​​in the meridian and sagittal directions at the low-frequency stage (spatial frequency 20lp / mm) are significantly improved after correction. Specifically, it is increased by 65.23% when the human eye is in direct vision, 51.39% when the eye is rotated 10°, and 64.93% when the eye is rotated -10°; the average MTF values ​​in the meridian and sagittal directions at the medium-frequency stage (spatial frequency 50lp / mm) are also improved to varying degrees after correction. In the case of direct vision, the improvement is 64.21%, 13.10% when the human eye is rotated 10°, and 59.40% when the human eye is rotated -10°; in the high-frequency stage (spatial frequency 80 lp / mm), although the improvement is relatively small after correction, image quality is still improved. Specifically, in direct vision, the average MTF values ​​in the meridian and sagittal directions increase by 40.71%. When the eye is rotated -10 degrees, the improvement is 2.90%. Therefore, after correcting aberrations with this lens, image quality is improved to varying degrees in direct vision and with eye movement, regardless of low, medium, or high frequencies.

[0129] In order to verify the correction effect of the lens for correcting high-order aberrations of the human eye provided in this embodiment, this embodiment also uses the design method provided in the above embodiment to design a lens that corrects only high-order aberrations of the on-axis field of view. The Zernike polynomial values ​​of aberrations Z4 to Z18 before and after correction using this lens are shown in Table 8:

[0130] Table 8

[0131]

[0132] From the data in Table 8, it can be seen that after correction with this lens, the PV value of the aberration is reduced from 9.085 waves to 2.346 waves, a decrease of 74.18%. The RMS values ​​corresponding to the coefficients of the wavefront aberrations Z4-Z18 of the human eye are reduced by 85.25%, and the RMS values ​​corresponding to the coefficients of the higher-order aberrations Z7-Z18 are reduced by 73.34%. Under the condition of a pupil of 5.5 mm, the measured Z7 (coma in the X direction), Z8 (coma in the Y direction), and Z9 (spherical aberration) are 1.098 waves, -0.175 waves, and -1.024 waves, respectively. waves, all exceeded the threshold range of normal human eye higher-order aberrations given by the testing equipment. After correction with this lens, the Zernike coefficients of these three items decreased to varying degrees. The sum of the first-order coma aberrations (Z7, Z8) decreased by 67.09% compared with before correction, and the spherical aberration (Z9) decreased by 95.90% compared with before correction. Other types of high-order aberrations were also corrected, such as the trefoil aberrations (Z10, Z11) decreased by 67.02% compared with before correction; the second-order astigmatism aberrations (Z12, Z13) decreased by 70.05% compared with before correction; and the four-leaf clover aberrations (Z17, Z18) decreased by 99.82% compared with before correction.

[0133] Furthermore, the lens was actually processed, and the wavefront aberration data on the wearer's eye axis was measured after the wearer wore the lens. This was compared with the wavefront aberration data fitted for the wearer to verify the lens's correction effect on higher-order aberrations. Table 9 shows the higher-order aberration data Z7-Z18 fitted for the wearer, the higher-order aberration data Z7-Z18 from five experiments after wearing the lens, and the average of the five experimental data:

[0134] Table 9

[0135]

[0136] From the data in Table 9, it can be seen that the total high-order aberration values ​​of the five experiments after wearing the lens have a significant decrease compared with the naked eye data: Specifically, compared with the fitted naked eye data, the total high-order aberrations of the five experimental data decreased by 19.33%, 18.31%, 23.50%, 29.71% and 25.99% respectively, and the average value of the total high-order aberrations of the five experiments decreased by 23.37%; for coma aberrations (Z7, Z8), which is the category with the largest numerical proportion among all aberrations, the coma aberrations of the five experiments with glasses decreased by 19.33%, 18.31%, 23.50%, 29.71% and 25.99% respectively. The average value decreased by 30.24% compared with the fitted naked eye data; similarly, for the spherical aberration (Z9), a larger aberration, the average value of the spherical aberration in the five experiments decreased by 14.75% compared with the fitted naked eye data; for the trefoil aberration (Z10, Z11), the average value of the five experiments decreased by 35.34% compared with the fitted naked eye data; in addition, after wearing the lens, other types of aberrations also decreased to varying degrees, proving that the lens designed using the design method provided in this application has a good positive effect on correcting high-order aberrations.

[0137] Those skilled in the art will appreciate that the embodiments of the present application may be provided as methods, systems, or computer program products. Therefore, the present application may take the form of an entirely hardware embodiment, an entirely software embodiment, or an embodiment combining software and hardware. Furthermore, the present application may take the form of a computer program product implemented on one or more computer-usable storage media (including but not limited to magnetic disk storage, CD-ROM, optical storage, etc.) containing computer-usable program code.

[0138] The present application is described with reference to the flowcharts and / or block diagrams of the methods, devices (systems), and computer program products according to the embodiments of the present application. It should be understood that each process and / or block in the flowchart and / or block diagram, as well as the combination of processes and / or blocks in the flowchart and / or block diagram, can be implemented by computer program instructions. These computer program instructions can be provided to a processor of a general-purpose computer, a special-purpose computer, an embedded processor, or other programmable data processing device to produce a machine, so that the instructions executed by the processor of the computer or other programmable data processing device generate instructions for implementing the processes in the flowchart and / or block diagram. Figure 1 a process or multiple processes and / or boxes Figure 1 A device that provides the functions specified in a block or multiple blocks.

[0139] These computer program instructions may also be stored in a computer readable memory that can direct a computer or other programmable data processing device to work in a specific manner, so that the instructions stored in the computer readable memory produce an article of manufacture comprising an instruction device, which implements the process Figure 1 a process or multiple processes and / or boxes Figure 1 The function specified in one or more boxes.

[0140] These computer program instructions can also be loaded onto a computer or other programmable data processing device so that a series of operating steps are executed on the computer or other programmable device to produce a computer-implemented process, thereby providing the instructions executed on the computer or other programmable device for implementing the process. Figure 1 a process or multiple processes and / or boxes Figure 1 The steps for the function specified in one or more boxes.

[0141] Obviously, the above embodiments are merely examples for clarity of explanation and are not intended to limit the implementation methods. Those skilled in the art will appreciate that other variations or modifications can be made based on the above description. It is not necessary and impossible to enumerate all implementation methods here. Obvious variations or modifications arising therefrom remain within the scope of protection of the present invention.

Claims

1. A method for designing a lens capable of correcting high-order aberrations of the human eye, characterized in that: include: A basic eye model is obtained, and the pupil diameter of the basic eye model is adjusted to the pupil diameter for measuring naked eye wavefront aberration. The curvature radius of the anterior and posterior surfaces of the cornea, corneal thickness, anterior chamber depth, lens thickness, vitreous depth, and axial length of the eye in the basic eye model are adjusted to values ​​measured in a dark environment to obtain a target basic eye model; wherein the surface shape of the anterior surface of the cornea in the target basic eye model is the Zernike edge sag surface, and its expression is: ， in, The first The sag at each sampling point; It represents the vertex curvature of the anterior corneal surface; The first The radial distance of each sampling point from the optical axis; Indicates the cone coefficient of the anterior corneal surface; Indicates the number of even-order aspheric coefficients in the anterior corneal surface; Indicates the first even aspheric surface on the anterior corneal surface coefficients; represents the number of Zernike fringe polynomials in the anterior corneal surface; The anterior corneal surface The coefficients of the Zernike marginal polynomials; The anterior corneal surface The basic aberration function of the Zernike edge polynomial; represents the normalized radial coordinate of the anterior corneal surface; represents the angular coordinate of the anterior surface of the cornea; Optimizing the surface shapes of the anterior surface of the lens and the anterior surface of the cornea in the target basic eye model using a ZERN optimization function until a difference between a high-order aberration value when light is imaged on the target basic eye model and a target wave aberration value is less than a first preset threshold, thereby obtaining a fitted eye model, specifically comprising: sequentially adjusting the radius of curvature of the anterior surface of the lens, coefficients of the 4th to 18th, and the 25th Zernike marginal polynomials in the anterior surface of the cornea using the ZERN optimization function, thereby changing the surface shapes of the anterior surface of the lens and the anterior surface of the cornea, until a difference between a high-order aberration value when light is imaged on the target basic eye model and a target wave aberration value is less than a first preset threshold; placing a paraxial surface on the front surface of the fitting eye model, and adjusting the vitreous depth of the fitting eye model with the goal of minimizing the defocus aberration value on the retina when light is imaged on the fitting eye model, to obtain a target fitting eye model and remove the paraxial surface; Changing the rotation angle of the eyeball in the target fitting eye model to obtain target eye models at different rotation angles; obtaining a lens to be optimized, and optimizing the parameters of the lens to be optimized with the goal that the high-order aberration values ​​of light when imaged on the target eye model at different rotation angles after passing through the lens to be optimized are all less than or equal to a second preset threshold, to obtain a lens that can correct high-order aberrations of the human eye; The surface of the lens to be optimized close to the target eye model is a Zernike annular phase surface, and the surface away from the target eye model is a spherical surface. The surface shape expression of the Zernike annular phase surface is: ， in, The Zernike annular phase plane The sag at each sampling point; represents the vertex curvature of the Zernike annular phase surface; The Zernike annular phase plane The radial distance of each sampling point from the optical axis; represents the cone coefficient of the Zernike annular phase surface; represents the number of Zernike polynomials; Indicates the The coefficients of the Zernike polynomials; Indicates the The basic aberration function of Zernike polynomials; represents the normalized radial coordinate of the Zernike annular phase plane; represents the angular coordinate of the Zernike annular phase plane; Optimizing the parameters of the lens to be optimized includes: adjusting the cone coefficient of the Zernike annular phase surface using a default wavefront optimization function, and adjusting the coefficients of the 4th to 37th Zernike polynomials in the Zernike annular phase surface using a ZERN optimization function, thereby changing the surface shape of the Zernike annular phase surface until the high-order aberration values ​​when the light passes through the lens to be optimized and is imaged on the target eye model at each rotation angle are less than or equal to a second preset threshold.

2. The method for designing a lens capable of correcting high-order aberrations of the human eye according to claim 1, wherein: After obtaining a lens that can correct high-order aberrations of the human eye, it also includes: The SDVR operation function is used to adjust the tangent slope and curvature change rate of the lens capable of correcting high-order aberrations of the human eye until the difference between the first-order derivative value of the anti-curvature coordinate point and the first-order derivative value of the rotationally symmetric coordinate point of the lens capable of correcting high-order aberrations of the human eye is equal to 0, thereby obtaining an optimized lens capable of correcting high-order aberrations of the human eye.

3. The method for designing a lens capable of correcting high-order aberrations of the human eye according to claim 1, wherein: After obtaining a lens that can correct high-order aberrations of the human eye, it also includes: The POWP operation function is used to optimize the refractive power distribution of the lens capable of correcting high-order aberrations of the human eye until the refractive power at a preset aperture of the lens capable of correcting high-order aberrations of the human eye is less than or equal to a preset ratio of the refractive power at the center point of the lens capable of correcting high-order aberrations of the human eye, thereby obtaining an optimized lens capable of correcting high-order aberrations of the human eye.

4. The method for designing a lens capable of correcting high-order aberrations of the human eye according to claim 1, wherein: The obtaining of the basic eye model comprises: Get the Liou eye model; A thin lens is placed on the front surface of the lens in the Liou eye model to obtain a basic eye model.

5. A lens capable of correcting high-order aberrations of the human eye, characterized in that: The lens capable of correcting high-order aberrations of the human eye is designed by the lens design method capable of correcting high-order aberrations of the human eye according to any one of claims 1 to 4, and specifically comprises: The on-axis high-order aberration correction area is a circular area with the center point of the lens capable of correcting high-order aberrations of the human eye as the center, and is used to correct the high-order aberrations of the human eye in the on-axis field of view; The off-axis high-order aberration correction zone is a circular area outside the on-axis high-order aberration correction zone, and is used to correct high-order aberrations caused by rotation of the human eye; The processing control area is a circular area on the side of the off-axis high-order aberration correction area away from the axial high-order aberration correction area, and is used to control the aperture of the lens that can correct high-order aberrations of the human eye.

6. The lens capable of correcting high-order aberrations of the human eye according to claim 5, wherein: The radius of the on-axis high-order aberration correction zone is less than or equal to 4 mm; With the center point of the lens capable of correcting high-order aberrations of the human eye as the center of the circle, the radius of the outer ring of the off-axis high-order aberration correction area is less than or equal to 25 mm; With the center point of the lens capable of correcting high-order aberrations of the human eye as the center of the circle, the radius of the outer ring of the processing control area is less than or equal to 40 mm.

Images