Ophthalmic defocus lenses

Abstract

The present invention relates to the field of ophthalmic technology, and proposes an ophthalmic lens capable of suppressing adverse optical phenomena. The ophthalmic defocus lens of the present invention comprises an optical zone, wherein the optical zone comprises a central optical zone and a peripheral defocus zone, and the defocus amount of the peripheral defocus zone is set according to the corrective diopter of the ophthalmic defocus lens, and the greater the absolute value of the corrective diopter of the ophthalmic defocus lens, the greater the defocus amount. Using the above present invention, an ophthalmic defocus lens is proposed, wherein the defocus amount of the ophthalmic defocus lens is designed according to different gradients of the diopter of the lens, which can fully guarantee the adequacy of the defocus design amount on the one hand, and on the other hand, it will not cause visual problems such as glare, interference, and deformation due to blindly increasing the defocus design amount, thereby improving wearing comfort.

Description

Technical Field

[0001] The present invention relates to the technical field of ophthalmology, and in particular to an ophthalmic defocus lens. Background Art

[0002] The human eye is an optical system similar to a camera. The front cornea and lens can be regarded as two optical lenses, which are responsible for imaging external objects into the eye; the retina is similar to the film of a camera, which is responsible for receiving images. When myopia occurs in the human eye, the distance between the front optical lens and the retina does not match, resulting in blurred vision. In the human eye, the main reason for the increase in myopia is the extension of the axial length of the eye, that is, the film position is too far. The latest medical research has confirmed that the extension of the eyeball depends on the peripheral defocus of the retina. According to the concept of refractive optics, the focus falls in front of the retina is called myopic defocus, and the focus falls behind the retina is called hyperopic defocus. The central retina of myopia is myopic defocus, while the peripheral retina is hyperopic defocus. The eyeball has the characteristic of relying on peripheral retinal imaging to induce eyeball development, especially for myopic teenagers under 18 years old. If the peripheral retinal imaging is hyperopic defocus, the retina will tend to grow toward the image point, and the length of the eyeball will be extended. If the peripheral retinal imaging is myopic defocus, the eyeball will stop extending. Peripheral hyperopic defocus of the retina is the main reason for the continuous increase in myopia. If modern medical methods are used to correct peripheral hyperopic defocus of the retina or artificially create peripheral myopic defocus of the retina, the continuous increase in myopia can be stopped, the cause of peripheral retinal defocus can be identified, and the occurrence and progression of myopia can be effectively prevented.

[0003] However, existing studies often confuse the defocus formed by the optical system at the front end of the human eye with the peripheral defocus of the retina. The defocus formed by the optical system means that the focal point of the central optical zone and the focal point of the peripheral optical zone are not on the same point or plane. For example, the refractive power of the peripheral optical zone is stronger, and the focal point (such as Figure 1 The focal point of the central optical zone (as shown in point B) will fall on the central optical zone (as shown in point Figure 1 However, it is uncertain whether this defocus is sufficient to form "myopic peripheral defocus" because the curvature of the retina needs to be considered in the human eye optical system. Figure 1In the figure, point A is the focal point formed by the central optical zone of the optical system, and point B is the focal point formed by the peripheral optical zone of the optical system. Point B falls before point A, showing an optical defocus characteristic with stronger refractive power, but it is still located behind the peripheral retina, which is a hyperopic defocus. In the international standard human eye model, such as the famous Navarro human eye model, it is believed that the curvature (radius of curvature) of the retina of a human eye with normal axial length is 12.3mm. The "optical defocus amount" of the optical system must be greater than the defocus amount formed by the curvature of the retina to truly form "myopic peripheral defocus". It can be seen that the formation of the desired peripheral defocus depends on the matching of the morphology of the retina with the front-end optical system. The study of the curvature characteristics of the retina is a prerequisite for scientifically viewing "myopic peripheral defocus".

[0004] With the theoretical support that myopic peripheral defocus delays the growth of the eye axis, a series of myopia control products have emerged, including orthokeratology lenses, multifocal contact lenses, defocused RGP, defocused frame glasses, etc. The design of the peripheral defocus of these products is relatively random or arbitrary. For example, after orthokeratology lenses are shaped according to the default inverse geometry design, the peripheral defocus varies with the corneal morphology and the degree of shaping (pressure), which is random under certain rules; the peripheral defocus settings of other products are also basically based on the amount that can be achieved by orthokeratology lenses, or are set to be larger than the amount that can be achieved by orthokeratology lenses.

[0005] However, the axial length of the human eye will change with age and the progression of myopia. As age increases, the axial length increases, and as myopia increases, the axial length increases. Studies have shown that the degree of axial myopia is positively correlated with the increase in axial length. The growth of the axial length will cause changes in the shape of the eyeball, from a spherical shape to an ellipsoidal shape, which will in turn bring about changes in the morphology of the retina. As the axial length increases, the retina will become steeper and the radius of curvature will gradually become smaller, such as Figure 2As shown. The optical system at the front of the human eye (including the cornea and lens) remains basically unchanged after childhood, so if the degree of myopia increases, the peripheral defocus state of the human eye will also change accordingly. At the same time, existing defocus products, such as peripheral defocus frame glasses, use the same defocus design amount for lenses with different myopia degrees. However, as mentioned above, the defocus degree of the retina itself is different for wearers with different myopia degrees (i.e., different axial lengths). The defocus amount required to correct low myopia is smaller, and the defocus amount required to correct high myopia is larger, so that the human eye can achieve the expected defocus effect after wearing optical products. Some products uniformly design the defocus amount to be very large to ensure that sufficient myopic defocus is generated. However, excessive defocus can lead to adverse optical phenomena such as glare, blurred vision, and distortion, and patients with low myopia are often more sensitive to adverse optical phenomena. Therefore, due to the lack of theoretical basis for design, the prior art may have insufficient defocus design, which reduces the treatment effect, or excessive defocus design, which causes significant interference to vision. Summary of the invention

[0006] In view of the above, an object of the present invention is to provide an ophthalmic lens capable of suppressing adverse optical phenomena.

[0007] To achieve the above-mentioned purpose, the ophthalmic defocus lens of the present invention comprises an optical zone, wherein the optical zone comprises a central optical zone and a peripheral defocus zone, the defocus amount of the peripheral defocus zone is set according to the corrective refractive power of the ophthalmic defocus lens, and the greater the absolute value of the corrective refractive power of the ophthalmic defocus lens, the greater the defocus amount.

[0008] By adopting the above invention, an ophthalmic defocus lens is proposed, wherein the defocus amount of the ophthalmic defocus lens is designed according to different gradients of the refractive power of the lens. On the one hand, the sufficiency of the defocus design amount can be fully guaranteed, and on the other hand, the defocus design amount is not blindly increased to cause visual problems such as glare, interference, and deformation, thereby improving wearing comfort.

[0009] The gradient design here means that the defocus amount of the ophthalmic defocus lens varies according to the refractive power of the lens.

[0010] As a possible implementation of the present invention, the central optical zone has a negative refractive power (to correct myopia), the peripheral defocus zone has a positive defocus amount, and the absolute value of the refractive power of the peripheral defocus zone is greater than that of the central optical zone.

[0011] The ophthalmic defocus lens of the present invention can be a frame spectacle lens worn outside the eye, and the defocus amount under different corrective diopters at a central optical zone diameter of about 20 mm is shown in the following table.

[0012] <![CDATA[ Diopter ]]> <![CDATA[ Frame mirror defocus ]]> <![CDATA[ -1.0D ]]> ≥0.80 <![CDATA[ -3.0D ]]> ≥2.25 <![CDATA[ -6.0D ]]> ≥4.65 <![CDATA[ -10.0D ]]> ≥7.75 <![CDATA[ -15.0D ]]> ≥11.60 <![CDATA[ -20.0D ]]> ≥15.40

[0013] The ophthalmic defocus lens of the present invention can be a frame spectacle lens worn outside the eye, and the defocus amount under different corrective diopters at a central optical zone diameter of about 20 mm is shown in the following table.

[0014] <![CDATA[ Diopter ]]> <![CDATA[ Frame mirror defocus ]]> <![CDATA[ Frame mirror defocus ]]> <![CDATA[ Frame mirror defocus ]]> <![CDATA[ -1.0D ]]> ≥0.80,≤1.8 ≥0.90,≤1.7 ≥1.00,≤1.6 <![CDATA[ -3.0D ]]> ≥2.25,≤3.25 ≥2.35,≤3.15 ≥2.45,≤3.05 <![CDATA[ -6.0D ]]> ≥4.65,≤5.65 ≥4.75,≤5.55 ≥4.85,≤5.45 <![CDATA[ -10.0D ]]> ≥7.75,≤8.75 ≥7.85,≤8.65 ≥7.95,≤8.55 <![CDATA[ -15.0D ]]> ≥11.60,≤12.60 ≥11.70,≤12.50 ≥11.80,≤12.40 <![CDATA[ -20.0D ]]> ≥15.40,≤16.40 ≥15.50,≤16.30 ≥15.60,≤16.20

[0015] The ophthalmic defocus lens of the present invention can be a corneal or scleral contact lens worn outside the eye, and the defocus amount under different corrective diopters at the central optical zone diameter of about 7.0 mm is shown in the following table.

[0016] <![CDATA[ Diopter ]]> <![CDATA[ Corneal or scleral contact lens defocus ]]> <![CDATA[ -1.0D ]]> ≥0.50 <![CDATA[ -3.0D ]]> ≥2.15 <![CDATA[ -6.0D ]]> ≥4.50 <![CDATA[ -10.0D ]]> ≥7.35 <![CDATA[ -15.0D ]]> ≥10.50 <![CDATA[ -20.0D ]]> ≥13.35

[0017] The ophthalmic defocus lens of the present invention can be a corneal or scleral contact lens worn outside the eye, and the defocus amount under different corrective diopters at the central optical zone diameter of about 7.0 mm is shown in the following table.

[0018] <![CDATA[ Diopter ]]> <![CDATA[ Corneal or scleral contact lens defocus ]]> <![CDATA[ Corneal or scleral contact lens defocus ]]> <![CDATA[ Corneal or scleral contact lens defocus ]]> <![CDATA[ -1.0D ]]> ≥0.50,≤1.50 ≥0.60,≤1.40 ≥0.70,≤1.30 <![CDATA[ -3.0D ]]> ≥2.15,≤3.15 ≥2.25,≤3.05 ≥2.35,≤2.95 <![CDATA[ -6.0D ]]> ≥4.50,≤5.50 ≥4.60,≤5.40 ≥4.70,≤5.30 <![CDATA[ -10.0D ]]> ≥7.35,≤8.35 ≥7.45,≤8.25 ≥7.55,≤8.15 <![CDATA[ -15.0D ]]> ≥10.50,≤11.50 ≥10.60,≤11.40 ≥10.70,≤11.30 <![CDATA[ -20.0D ]]> ≥13.35,≤14.35 ≥13.45,≤14.25 ≥13.55,≤14.15

[0019] The ophthalmic defocus lens of the present invention may be an intraocular lens implanted in the eye, wherein the intraocular lens has a defocus amount at different corrected diopters at an optical zone diameter of about 4.0 mm as shown in the following table.

[0020] <![CDATA[ Diopter ]]> <![CDATA[ Defocus of intraocular lens ]]> <![CDATA[ -1.0D ]]> ≥0.90 <![CDATA[ -3.0D ]]> ≥2.80 <![CDATA[ -6.0D ]]> ≥5.35 <![CDATA[ -10.0D ]]> ≥8.35 <![CDATA[ -15.0D ]]> ≥11.50 <![CDATA[ -20.0D ]]> ≥14.15

[0021] The ophthalmic defocus lens of the present invention can be an intraocular artificial lens implanted in the eye. The defocus amount of the intraocular lens at different corrected diopters at an optical zone diameter of about 4.0 mm is shown in the following table.

[0022] <![CDATA[ Diopter ]]> <![CDATA[ Defocus of intraocular lens ]]> <![CDATA[ Defocus of intraocular lens ]]> <![CDATA[ Defocus of intraocular lens ]]> <![CDATA[ -1.0D ]]> ≥0.90,≤1.90 ≥1.00,≤1.80 ≥1.10,≤1.70 <![CDATA[ -3.0D ]]> ≥2.80,≤3.80 ≥2.90,≤3.70 ≥2.80,≤3.60 <![CDATA[ -6.0D ]]> ≥5.35,≤6.35 ≥5.45,≤6.25 ≥5.55,≤6.15 <![CDATA[ -10.0D ]]> ≥8.35,≤9.35 ≥8.45,≤9.25 ≥8.55,≤9.15 <![CDATA[ -15.0D ]]> ≥11.50,≤12.50 ≥11.60,≤12.40 ≥11.50,≤12.30 <![CDATA[ -20.0D ]]> ≥14.15,≤15.15 ≥14.25,≤15.05 ≥14.35,≤14.95

[0023] As a possible implementation of the ophthalmic defocus lens of the present invention, the optical zone achieves defocus design through an aspherical surface, and the aspherical surface shape expression is:

[0024]

[0025] Wherein, c is the reciprocal of the radius of curvature of the base spherical surface of the optical part, y is the vertical distance from any point on the curve to the abscissa axis (Z), Q is the aspheric coefficient, A 2i is the high-order coefficient of the aspheric surface, and the aspheric surface is obtained by rotating the aspheric surface curve around the abscissa axis (Z).

[0026] As a possible implementation of the ophthalmic defocus lens of the present invention, the optical zone is composed of concentric rings with different curvature radii to achieve a defocus design.

[0027] The corrective diopter of the ophthalmic defocus lens may be 0 to -20D, 0 to -10D or 0 to -6.0D.

[0028] Explanation of terms

[0029] like Figure 3 As shown, 1 represents the front optical system of the human eye, which includes the cornea, lens, and corrective lenses (including frame glasses, corneal contact lenses, implantable lenses, etc.); 2 represents the retina of the human eye.

[0030] Refractive error: refers to the situation when the human eye does not use accommodation (i.e. does not use corrective lenses), and parallel light rays cannot form a clear image on the retina after passing through the refractive effect of the optical system of the eye, but instead form an image in front of or behind the retina, including myopia, hyperopia and astigmatism.

[0031] Refractive power is a physical quantity that measures the degree of refractive error, and its unit is diopter.

[0032] Optical defocus of the front-end optical system: refers to the difference between the central imaging point and the peripheral imaging point of the front-end optical system, such as point A and point C in the figure. A is the central imaging point, and C is the peripheral imaging point of the optical system. After the imaging points C and A are converted into diopters, the difference between the two is called "optical defocus".

[0033] Peripheral defocus of the retina: The retina has a curvature (radius of curvature) due to its own shape. If you want to achieve a "normal view" on the entire retina, that is, all points fall on the retina, the refractive power required in the central and peripheral parts is different. The central point falls on point A, and the peripheral point falls on point B. The axial distance between point A and point B (3 in the figure) is Δd described later in this specification. m , this axial distance is converted into diopter, and the difference in diopter between point A and point B is called "retinal defocus".

[0034] In optical systems, the conversion between distance and diopter is usually achieved by ray tracing using optical simulation software. BRIEF DESCRIPTION OF THE DRAWINGS

[0035] Figure 1 It is an explanatory diagram showing the difference between optical peripheral defocus and peripheral defocus relative to the retina;

[0036] Figure 2 This is a model diagram of a myopic eye and a normal eye. It can be seen that myopia causes the eye axis to grow and the retina to become steeper.

[0037] Figure 3 It is a schematic diagram for explaining the difference between the defocus of the optical system at the front end of the human eye and the defocus of the retina;

[0038] Figure 4It is an illustration of the axial ellipse coordinate system and the relative distance between the retina and the standard eye;

[0039] Figure 5 It is a graph of the axial distance from the center of the retina at different diameters;

[0040] Figure 6 It is an illustration of the linear relationship between the axial distance from the center of the retina at different diameters and the refractive error;

[0041] Figure 7 It is a schematic diagram of the amount of defocus on the retina for each refractive error;

[0042] Figure 8 It is an explanatory chart showing the linear relationship between the defocus amount and refractive error at different diameters of the retina with different refractive errors;

[0043] Fig. 9 This is an illustration of different degrees of myopia, different axial lengths, and different retinal curvatures;

[0044] Fig.10 This is a real photo of the defocus lens of the embodiment of the present invention;

[0045] Fig.11 1 is a comparison diagram (photo) of a commercially available defocus lens and a defocus lens of a product of an embodiment of the present invention, wherein (a) is a commercially available defocus lens, and (b) is a product of an embodiment of the present invention;

[0046] Fig.12 The figure shows a refractive error analysis system constructed by frame glasses and the human eye optical system. DETAILED DESCRIPTION

[0047] [First embodiment]

[0048] This embodiment relates to a modeling method of a peripheral defocus model based on retinal morphology, which mainly includes the following steps:

[0049] 1. Steps to build a human eye optical analysis system

[0050] The optical analysis system is established based on standard human eye models such as the Navarro human eye model, the Liou human eye model, the ESCUDEROSANZ large field human eye model, etc. The so-called standard human eye here refers to a normal eye without refractive error.

[0051] This embodiment uses the human eye model listed in Table 2 as an example to establish a human eye optical analysis system. However, the human eye model described in the present invention includes but is not limited to the analysis system shown in Table 2.

[0052] Table 2 Examples of optical analysis systems

[0053]

[0054] 2. Steps to build the refractive error analysis system model

[0055] The myopia and / or hyperopia degree models are added to the human eye optical analysis system constructed in the above steps to construct a refractive error analysis system model.

[0056] The construction method is as follows: insert an optical lens at a specific position in the human eye system constructed in step 1, and the specific position refers to the position of the lens in the refractive error correction method. For example, if frame glasses are used, the lens should be inserted in front of the cornea of ​​the human eye optical system, and the distance from the cornea is approximately the lens-eye distance (the distance from frame glasses to the eye), such as 12 mm; if corneal contact lenses are used, the lens should be inserted to a position where the cornea is fully in contact with the cornea, and the distance from the cornea is about 20 μm; if an intraocular lens is used, such as a method using a phakic intraocular lens, the lens should be inserted in front of the lens and behind the cornea, such as 350 μm from the rear surface of the cornea. The lens has material refractive index characteristics, lens thickness, and front and rear surface curvature radius. The lens and the human eye optical system described in step 1 together form a refractive error analysis system model.

[0057] The refractive error of the human eye is represented by the refractive power of the inserted lens, and the change in the axial length caused by the refractive error is analyzed; similarly, when the axial length changes, the amount of refractive error caused by the change in axial length can be reversely calculated by adjusting the lens parameters (such as the radius of curvature).

[0058] The defocus amount of the retina at different positions with different degrees of myopia is used as the calculation basis. The position (diameter) of the retina is projected to the position of the corresponding lens through optical refraction, and the defocus amount of the lens at the said position is calculated. For example, a retinal radius of 10mm (20mm diameter) corresponds to an optical zone diameter of about 20mm for frame glasses, a contact lens diameter of about 7.0mm, and a lens diameter of about 4.0mm.

[0059] The so-called myopia and / or hyperopia degree model here can also be called a refractive eye model, which includes parameters of human eyes with different myopia degrees and / or hyperopia degrees (i.e. different refractive errors). In addition, in the following description of this embodiment, myopia is used as an example for description.

[0060] In this embodiment, the refractive error of frame glasses is taken as an example to express the degree of refractive error (i.e., the refractive error), which is also in line with the clinical expression of refractive error. The frame glasses parameters are taken as an example of a lens with a refractive index of 1.6, a lens-eye distance of 12 mm, and a center thickness of 3.0 mm. Fig.12The figure shows a refractive error analysis system constructed by frame glasses and the human eye optical system, wherein 1 is the cornea model, 2 is the lens model, 3 is the retina model, and 4 is the inserted frame glasses model. When the human eye refractive error is 0, the front and rear surfaces of the inserted frame glasses are both flat. When refractive error occurs, the amount of refractive error can be achieved by adjusting the radius of curvature of the rear surface of 4. For example, under the refractive index and center thickness of the frame glasses, the radius of curvature of the rear surface of the -3D lens is 200mm.

[0061] 3. Calculation steps of axial length

[0062] According to the refractive error analysis system constructed in the above steps 1 and 2, the axial length of the eye under different myopia degrees (ie different refractive errors) is calculated.

[0063] Table 3 shows the axial lengths corresponding to different myopia degrees and the difference in axial lengths between myopic eyes and normal eyes under the human eye optical system constructed in step 1-2.

[0064] Table 3 Axial lengths corresponding to different degrees of myopia, and the difference in axial length between the myopic axial length and the normal axial length

[0065] Myopia Axial length Axis length difference Myopia Axial length Axis length difference 0.0 24.000 0.000 -4.5 25.617 1.617 -1.0 24.338 0.338 -5.0 25.801 1.801 -1.5 24.520 0.520 -5.5 25.985 1.985 -2.0 24.702 0.702 -6.0 26.171 2.171 -2.5 24.884 0.884 -6.5 26.356 2.356 -3.0 25.066 1.066 -7.0 26.542 2.542 -3.5 25.249 1.249 -7.5 26.728 2.728 -4.0 25.427 1.427 -8.0 26.915 2.915

[0066] 4. Steps for calculating the relative distance between the retina of the ametropic eye and the retina of the standard eye

[0067] According to the axial length obtained in step 3, calculate the relative distance between the retina of the myopic eye after the axial length has increased or the hyperopic eye after the axial length has shortened and the retina of the standard eye at different positions of the fundus (retina).

[0068] Calculation method example:

[0069] (1) The eyeball is considered as an ellipse with a major axis and a minor axis. The radius of curvature of the retina is the radius of curvature of the vertex of the major axis of the ellipse. A rectangular coordinate system is established with the center of the ellipse as the origin. The expression of the ellipse is:

[0070]

[0071] Among them, a is half the axial length of the eye, a=L / 2, L is the axial length of the eye; b is half the height of the eyeball.

[0072] (2) Calculate the height of each point on the retina of a normal eye, that is, the difference between the coordinate of point x and a at different y values. The calculation method is:

[0073]

[0074] (3) Keep the eyeball height unchanged and lengthen the eye axis, that is, keep the short axis of the ellipse unchanged and change the long axis, and calculate the height of each point of the retina under the new long axis of the ellipse, that is, calculate the height of each point of the retina of the myopic eye whose eye axis length is the length of the long axis after the elongation:

[0075]

[0076] Wherein, a'=L' / 2, L' is the axial length of the myopic eye after being elongated relative to the standard eye.

[0077] (4) Calculate the relative distance between the retina of the myopic eye and the retina of the normal eye (standard eye):

[0078] Ah=2*(h'-h)

[0079] Calculation results: (1) The relative distance between the retina of the myopic eye -1.0D and the retina of the standard eye when represented by the degree of frame glasses is shown in Table 4, where the retinal position refers to the different diameter positions of the retina, and the axial direction difference refers to the relative distance between the retina and the retina of the standard eye in the axial direction (the same is true for Tables 5 to 9 described below).

[0080] Table 4 Relative distance between the retina of myopia-1.0D and the standard eye

[0081] Retinal position / mm Axis direction difference / mm Retinal position / mm Axis direction difference / mm -11 -0.101 1 -0.001 -10 -0.076 2 -0.002 -9 -0.057 3 -0.005 -8 -0.043 4 -0.010 -7 -0.032 5 -0.015 -6 -0.023 6 -0.023 -5 -0.015 7 -0.032 -4 -0.010 8 -0.043 -3 -0.005 9 -0.057 -2 -0.002 10 -0.076 -1 -0.001 11 -0.101 0 0.000

[0082] In addition, the axial distances (i.e., the distances in the axial direction) from the center of the retina at different diameters on the retina of a frame glasses with a power of 1.0D satisfy the polynomial:

[0083] Δd=1E-06r 5 +2E-05r 4 +0.0002r 3 +1E-06r 2 +0.0006r

[0084] Wherein, Δd is the axial distance of the retina from the center point at different positions from the center point, and r is the distance (radius) of the peripheral retina from the center point.

[0085] (2) The relative distance between the retina of a -2.0D myopia frame and the standard eye, where the retinal position refers to the different diameter positions of the retina, and the axial direction difference refers to the relative distance between the retina of the standard eye and the standard eye in the axial direction.

[0086] Table 5 Relative distance between the retina of myopia-2.0D and the standard eye

[0087] Retinal position / mm Axis direction difference / mm Retinal position / mm Axis direction difference / mm -11 -0.211 1 -0.001 -10 -0.157 2 -0.005 -9 -0.119 3 -0.011 -8 -0.089 4 -0.020 -7 -0.066 5 -0.032 -6 -0.047 6 -0.047 -5 -0.032 7 -0.066 -4 -0.020 8 -0.089 -3 -0.011 9 -0.119 -2 -0.005 10 -0.157 -1 -0.001 11 -0.211

[0088] The axial distances from the retina center at different diameters of the retina for myopia of -2.0D frame glasses satisfy the polynomial:

[0089] Δd=3E-06r 5 +5E-05r 4 +0.0004r 3 +3E-06r 2 +0.0013r+0.0001

[0090] Wherein, Δd is the axial distance of the retina from the center point at different positions from the center point, and r is the distance (radius) of the peripheral retina from the center point.

[0091] (3) The relative distance between the retina of the myopic-3D eye and the standard eye on the frame glasses, where the retinal position refers to the different diameter positions of the retina, and the axial direction difference refers to the relative distance between the retina and the standard eye in the axial direction.

[0092] Table 6 Relative distance between the retina of myopia-3.0D and the standard eye

[0093] Retinal position / mm Axis direction difference / mm Retinal position / mm Axis direction difference / mm -11 -0.320 1 -0.002 -10 -0.238 2 -0.007 -9 -0.181 3 -0.017 -8 -0.136 4 -0.030 -7 -0.100 5 -0.048 -6 -0.071 6 -0.071 -5 -0.048 7 -0.100 -4 -0.030 8 -0.136 -3 -0.017 9 -0.181 -2 -0.007 10 -0.238 -1 -0.002 11 -0.320 0 0.000

[0094] Table 7 Relative distance between the retina of myopia-4.0D and the standard eye

[0095] Retinal position / mm Axis direction difference / mm Retinal position / mm Axis direction difference / mm -11 -0.428 1 -0.002 -10 -0.319 2 -0.010 -9 -0.242 3 -0.023 -8 -0.182 4 -0.041 -7 -0.134 5 -0.065 -6 -0.096 6 -0.096 -5 -0.065 7 -0.134 -4 -0.041 8 -0.182 -3 -0.023 9 -0.242 -2 -0.010 10 -0.319 -1 -0.002 11 -0.428 0 0.000

[0096] The axial distances from the retina center at different diameters of the retina with a myopia of -3.0D frame glasses satisfy the polynomial:

[0097] Δd=4E-06r 5 +8E-05r 4 +0.0006r 3 +5E-06r 2 +0.0019r+0.0002

[0098] Wherein, Δd is the axial distance of the retina from the center point at different positions from the center point, and r is the distance (radius) of the peripheral retina from the center point.

[0099] (4) The relative distance between the retina of a -4D myopic eye and the standard eye on the frame glasses, where the retinal position refers to the different diameter positions of the retina, and the axial direction difference refers to the relative distance between the retina and the standard eye in the axial direction.

[0100] The axial distances from the retina center at different diameters of the retina with a myopia of -4.0D frame glasses satisfy the polynomial:

[0101] Δd=5E-06r5 +0.0001r 4 +0.0008r 3 +6E-06r 2 +0.0026r+0.0002

[0102] Wherein, Δd is the axial distance of the retina from the center point at different positions from the center point, and r is the distance (radius) of the peripheral retina from the center point.

[0103] (5) The relative distance between the retina of a -5D myopic eye and the standard eye on the frame glasses, where the retinal position refers to the different diameter positions of the retina, and the axial direction difference refers to the relative distance between the retina and the standard eye in the axial direction.

[0104] Table 8 Relative distance between the retina of myopia-5.0D and the standard eye

[0105] Retinal position / mm Axis direction difference / mm Retinal position / mm Axis direction difference / mm -11 -0.541 1 -0.003 -10 -0.403 2 -0.013 -9 -0.305 3 -0.029 -8 -0.229 4 -0.051 -7 -0.169 5 -0.082 -6 -0.121 6 -0.121 -5 -0.082 7 -0.169 -4 -0.051 8 -0.229 -3 -0.029 9 -0.305 -2 -0.013 10 -0.403 -1 -0.003 11 -0.541 0 0.000

[0106] The axial distances from the retina center at different diameters of the retina with a myopia of -5.0D frame glasses satisfy the polynomial:

[0107] Δd=7E-06r 5 +0.0001r 4 +0.001r 3 +8E-06r 2 +0.0032r+0.0003

[0108] Among them, Δd is the axial distance of the retina from the center point at different positions from the center point, and r is the distance (radius) of the peripheral retina from the center point.

[0109] (6) The relative distance between the retina of a -6D myopic eye and the standard eye on the frame glasses, where the retinal position refers to the different diameter positions of the retina, and the axial direction difference refers to the relative distance between the retina and the standard eye in the axial direction.

[0110] Table 9 Relative distance between the retina of myopia-6.0D and the standard eye

[0111] Retinal position / mm Axis direction difference / mm Retinal position / mm Axis direction difference / mm -11 -0.652 1 -0.004 -10 -0.485 2 -0.015 -9 -0.367 3 -0.034 -8 -0.276 4 -0.062 -7 -0.204 5 -0.099 -6 -0.145 6 -0.145 -5 -0.099 7 -0.204 -4 -0.062 8 -0.276 -3 -0.034 9 -0.367 -2 -0.015 10 -0.485 -1 -0.004 11 -0.652 0 0.000

[0112] The axial distances from the retina center at different diameters on the retina of a frame glasses with myopia of -6.0D satisfy the polynomial:

[0113] Δd=8E-06r 5 +0.0002r 4 +0.0012r 3 +9E-06r 2+0.0039r+0.0003

[0114] Wherein, Δd is the axial distance of the retina from the center point at different positions from the center point, and r is the distance (radius) of the peripheral retina from the center point.

[0115] in addition, Figure 5 The axial distances from the center of the retina at different diameters under the above-mentioned various myopia conditions are shown in FIG. It may be necessary to explain that since myopia is used as an example for explanation here, its refractive error is represented by a negative value, so in order to adapt, the above-mentioned axial distance is also represented by a negative value.

[0116] In summary, under a certain refractive error state, the axial distances from the center of the retina at different diameters on the retina conform to the polynomial model:

[0117]

[0118] Among them, Δd is the axial distance of the retina from the center point at different positions from the center point, r is the distance (radius) of the peripheral retina from the center point, and a i All are coefficients.

[0119] according to Figure 5 The results shown or the above polynomial model can be obtained Figure 6 The relationship between the axial distance and the change of refractive error is shown in the figure. Figure 6 As shown in the figure, the axial distance from the center of the retina at different diameters (i.e. different radial positions) on the retina is linearly related to the refractive error. That is to say, for ametropia (myopia and hyperopia), the axial distance from a point on the peripheral area of ​​the retina to the center of the retina is linearly related to the refractive error (diopter) of the ametropia eye. The greater the refractive error of the ametropia eye, the greater the axial distance. In addition, Figure 6 The figure shows the situation of myopia. It goes without saying that the same linear relationship also exists for hyperopia. Figure 6 In the case of myopia, the degree of refractive error (degree) is represented by negative values. Therefore, in order to adapt and make it easier to understand the above linear relationship, the axial distance and radial position are also represented by negative values. Therefore, the so-called "size" here is measured by absolute values.

[0120] Reference Figure 6 , the axial distance between a certain point in the periphery and the center of the retina is linearly related to the degree of refractive error:

[0121]

[0122] where Δd mis the axial distance between the retina with a radius of m and the center of the retina, is the refractive error of the retina (diopter), and f and g are coefficients.

[0123] In this embodiment, when m is from 0 to -11, f and g are shown in Table 10.

[0124] Table 10 Coefficient of relationship between the axial distance between a certain point in the periphery and the center of the retina and the degree of refractive error

[0125] Retinal position m / mm f g -11 0.11 0.0094 -10 0.0819 0.007 -9 0.062 0.0053 -8 0.0466 0.004 -7 0.0344 0.0029 -6 0.0245 0.0021 -5 0.0167 0.0014 -4 0.0105 0.0009 -3 0.0058 0.0005 -2 0.0026 0.0002 -1 0.006 5E-05 0 0 0

[0126] 5. Defocus calculation steps

[0127] Calculate the degree of frame glasses (i.e. the required defocus amount) corresponding to different positions of the retina under different myopia degrees.

[0128] In the optical analysis system constructed in step 2, the length of the vitreous cavity is changed according to the axial lengths of different myopia degrees obtained in step 3, so that the length of the human eye optical system conforms to the axial length under the myopia degree, and focusing is performed with the degree of frame glasses as the optimization condition to obtain the degrees of frame glasses corresponding to different axial lengths, and the refractive power difference of the position of the retina relative to the center of the retina under each myopia degree is obtained, thereby obtaining the defocus distribution of the retina with different refractive errors.

[0129] The results are as follows:

[0130] (1) Retinal refractive power distribution for myopia of -1D

[0131] Table 11 Distribution of the difference between retinal refraction and central refractive power for myopia of -1D

[0132] Retinal position / mm Diopter difference / D Retinal position / mm Diopter difference / D -11 -0.275 -5 -0.042 -10 -0.209 -4 -0.026 -9 -0.157 -3 -0.015 -8 -0.118 -2 -0.006 -7 -0.087 -1 0.000 -6 -0.062 0 0.000

[0133] The difference between the peripheral and central refractive power of the retina for a refractive error of -1D fits the polynomial:

[0134] ΔD1=7E-07r 5 -3E-06r 4 -0.0001r 3 -0.0025r 2 -0.0015r+0.0002

[0135] (2) Retinal refractive power distribution for myopia of -2D

[0136] Table 12 Distribution of the difference between retinal refraction and central refractive power for myopia of -2D

[0137] Retinal position / mm Diopter difference / D Retinal position / mm Diopter difference / D -11 -0.581 -5 -0.088 -10 -0.432 -4 -0.055 -9 -0.330 -3 -0.005 -8 -0.248 -2 0.000 -7 -0.182 -1 0.000 -6 -0.138 0 0.000

[0138] Refractive error - The difference between the peripheral and central refractive power of the retina in 2D fits the polynomial:

[0139] ΔD2=1E-05r 5 +0.0002r 4 +0.0013r 3 -0.0033r 2 -0.0114r-0.0019

[0140] (3) Retinal refractive power distribution for myopia of -3D

[0141] Table 13 Distribution of the difference between retinal refraction and central refractive power for myopia of -3D

[0142] Retinal position / mm Diopter difference / D Retinal position / mm Diopter difference / D -11 -0.880 -5 -0.133 -10 -0.656 -4 -0.084 -9 -0.497 -3 -0.047 -8 -0.374 -2 -0.020 -7 -0.276 -1 -0.005 -6 -0.196 0 0.000

[0143] Refractive error - The difference between the peripheral and central refractive power of the retina in 3D fits the polynomial:

[0144] ΔD3=1E-05r 5 +0.0002r 4 +0.0016r 3 -0.0001r 2 +0.005r+0.0005

[0145] (4) Retinal refractive power distribution for myopia of -4D

[0146] Table 14 Distribution of the difference between retinal refraction and central refractive power for myopia of -4D

[0147] Retinal position / mm Diopter difference / D Retinal position / mm Diopter difference / D -11 -1.177 -5 -0.179 -10 -0.877 -4 -0.112 -9 -0.666 -3 -0.063 -8 -0.500 -2 -0.027 -7 -0.369 -1 0.000 -6 -0.275 0 0.000

[0148] The difference between the peripheral and central refractive power of the retina for a refractive error of 4D fits the polynomial:

[0149] ΔD4=1E-05r 5 +0.0002r 4 +0.0013r 3 -0.0048r 2 -0.0006r+0.0012

[0150] (5) Retinal refractive power distribution for myopia of -5D

[0151] Table 15 Distribution of the difference between retinal refraction and central refractive power for myopia of -5D

[0152] Retinal position / mm Diopter difference / D Retinal position / mm Diopter difference / D -11 -1.485 -5 -0.226 -10 -1.107 -4 -0.140 -9 -0.839 -3 -0.080 -8 -0.633 -2 -0.036 -7 -0.465 -1 -0.008 -6 -0.333 0 0.000

[0153] Refractive error - The difference between the peripheral and central refractive power of the retina for 5D fits the polynomial:

[0154] ΔD5=2E-05r 5 +0.0004r 4 +0.003r 3 +0.0009r 2 +0.0102r+0.0011

[0155] (6) Retinal refractive power distribution for myopia of -6D

[0156] Table 16 Distribution of the difference between retinal refraction and central refractive power for myopia of -6D

[0157] Retinal position / mm Diopter difference / D Retinal position / mm Diopter difference / D -11 -1.788 -5 -0.275 -10 -1.333 -4 -0.171 -9 -1.017 -3 -0.095 -8 -0.770 -2 -0.042 -7 -0.561 -1 -0.011 -6 -0.400 0 0.000

[0158] The difference between the peripheral and central refractive power of the retina for a refractive error of -6D fits the polynomial:

[0159] ΔD6=2E-05r 5 +0.0005r 4 +0.0039r 3 +0.0022r 2 +0.0136r+0.0012

[0160] In summary, under a certain refractive error state, the difference between the peripheral and central refractive power of the retina conforms to the polynomial model:

[0161]

[0162] Where ΔD is the difference in refractive error between a point on the periphery of the retina and the center point when the light is focused on that point, r is the distance from the periphery of the retina to the center point, and A is i All are coefficients.

[0163] Figure 7 is a schematic diagram of the amount of defocus on the retina for each refractive error. Figure 7 As shown, the farther from the center of the retina, the greater the defocus amount. Since myopia is used as an example, the diopter is a negative value. To adapt and facilitate understanding, the retinal position and defocus amount are also expressed as negative values. Table 17 summarizes the defocus amount on the retina of each refractive error in the implementation method.

[0164] Table 17 Defocus amount on the retina for each refractive error (expressed as positive value)

[0165] Myopia Retinal position 5mm Retina position 10mm -1.0D 0.04D 0.21D -2.0D 0.09D 0.43D -3.0D 0.13D 0.66D -4.0D 0.18D 0.88D -5.0D 0.23D 1.11D -6.0D 0.28D 1.33D

[0166] The defocus amount of the retina with different refractive errors at different diameters is linearly related to the refractive error, such as Figure 8shown.

[0167] The difference in refractive error between a certain point in the periphery and the central point of the retina is linearly related to the degree of refractive error:

[0168]

[0169] Where ΔD m is the difference in refractive error between the point with radius m on the retina and the center of the retina. is the refractive error of the retina, and k and b are coefficients.

[0170] In this embodiment, when m ranges from 0 to -11, k and b are shown in Table 18.

[0171] Table 18 The coefficient of linear relationship between the difference in refractive error between a certain point in the periphery of the retina and the central point and the degree of refractive error

[0172] Retinal position m / mm k b -11 0.3021 0.0264 -10 0.2247 0.0174 -9 0.1713 0.0154 -8 0.1298 0.0138 -7 0.0947 0.0083 -6 0.0673 0.0016 -5 0.0464 0.0052 -4 0.0287 0.0025 -3 0.0183 0.0133 -2 0.0083 0.0072 -1 0.0021 0.0033 0 0 0

[0173] The modeling method of this embodiment is used to construct a retinal peripheral defocus model, and corrective lenses such as frame glasses are designed based on this. It is possible to provide appropriate retinal peripheral defocus for various refractive errors, thereby ensuring the correction effect. At the same time, it is possible to suppress adverse optical phenomena such as glare, blurred vision, distortion, etc. caused by excessive defocus, thereby improving wearing comfort.

[0174] [Second embodiment]

[0175] This embodiment is based on the technical concept in the first embodiment, and provides an ophthalmic lens and a design method thereof, wherein the ophthalmic lens has a continuously changing refractive power in the radial direction, and a gradient defocus amount is designed according to different lens diopters during design, including but not limited to frame glasses, contact lenses, various corneal contact lenses, scleral contact lenses, intraocular lenses, etc., for delaying the progression of myopia or hyperopia. The retinal defocus amount formed by the optical defocus amount of the ophthalmic lens should be designed to be no less than the retinal defocus amount shown in Tables 11 to 16, or substantially equal to the retinal defocus amount shown in Tables 11 to 16 during design.

[0176] Existing defocus products, such as peripheral defocus frame glasses, have the same defocus design for lenses with different myopia levels. However, as mentioned above, Fig. 9Wearers with different degrees of myopia (i.e. different axial lengths) have different degrees of retinal defocus. Low myopia requires a smaller amount of defocus, while high myopia requires a larger amount of defocus, so that the human eye can achieve the expected defocus effect after wearing optical products. Some products uniformly design the defocus amount to be very large to ensure sufficient myopic defocus. However, excessive defocus can lead to adverse optical phenomena such as glare, blurred vision, and distortion, and patients with low myopia are often more sensitive to adverse optical phenomena. Therefore, due to the lack of design basis, existing methods may result in insufficient defocus design, reducing the treatment effect, or excessive defocus design, causing significant interference to vision.

[0177] Under the guidance of the design concept of the present invention, for the retinal defocus model based on the standard human eye, the optical lens at 5mm and 10mm on the retina and different myopia degrees should meet the defocus design amount greater than the defocus amount shown in Tables 11 to 16.

[0178] The ophthalmic defocus lens of this embodiment includes an optical zone, which includes a central optical zone and a peripheral defocus zone. The defocus amount of the peripheral defocus zone is set according to the corrective refractive power of the ophthalmic defocus lens, and the greater the absolute value of the corrective refractive power of the ophthalmic defocus lens, the greater the defocus amount.

[0179] In this embodiment, the central optical zone has a negative refractive power (to correct myopia), the peripheral defocus zone has a positive defocus amount, and the absolute value of the refractive power of the peripheral defocus zone is greater than that of the central optical zone.

[0180] Taking the design of frame glasses as an example, the lens is composed of front and back surfaces. Optionally, the total diameter of the lens is 80mm, the center thickness is 3mm, and the material refractive index is 1.55. The radius of curvature of the front surface of the optical zone is 7.724, the radius of curvature of the back surface is 5.954, and the back surface is an aspherical surface. The peripheral defocus is achieved by the aspherical surface. The surface shape expression is:

[0181]

[0182] Among them, c is the reciprocal of the radius of curvature of the basic spherical surface of the optical part, y is the vertical distance from any point on the curve to the horizontal axis (Z), Q is the aspheric coefficient, A2i is the aspheric high-order coefficient, and the aspheric surface is obtained by rotating the aspheric curve around the horizontal axis (Z).

[0183] The defocus amount of the defocus lens can make human eyes with different refractive states all be in a myopic defocus state, and will not affect wearing comfort due to excessive defocus amount.

[0184] The defocus of the ophthalmic lens can also be achieved in the form of regional refraction, with different concentric rings distributed on the lens, each ring having a gradually changing radius of curvature, so that the absolute value of the optical defocus of the lens in different regions is slightly greater than the defocus shown in Tables 11 to 16. The defocus of the ophthalmic lens varies with the gradient of the lens diopter, and the higher the diopter, the greater the defocus.

[0185] Optionally, the defocus amount of the ophthalmic lens varies with the lens diopter gradient, and the higher the diopter, the greater the defocus amount.

[0186] Optionally, when the diameter of the frame glasses is about 20 mm, the diameter of the corneal contact lens is about 7.0 mm, and the diameter of the lens is about 4.0 mm, the minimum defocus amount and the defocus amount range that the lens should achieve are shown in Tables 19-1 to 19-4. It is worth noting that the minimum defocus amount corresponding to other diopters between the listed diopters are also between the listed minimum defocus amount values, and the overall trend is a monotonous change that the higher the corrected diopters of the ophthalmic defocus lens (i.e., the more negative the diopters of the lens), the greater the minimum defocus amount that needs to be achieved.

[0187] Table 19-1 Minimum and maximum defocus values ​​required for various types of lenses at different corrected diopters / unit D

[0188]

[0189] Table 19-2 Defocus range required for frame lenses at different corrective diopters / unit D

[0190] <![CDATA[ Diopter ]]> <![CDATA[ Frame mirror defocus ]]> <![CDATA[ Frame mirror defocus ]]> <![CDATA[ Frame mirror defocus ]]> <![CDATA[ -1.0D ]]> ≥0.80,≤1.8 ≥0.90,≤1.7 ≥1.00,≤1.6 <![CDATA[ -3.0D ]]> ≥2.25,≤3.25 ≥2.35,≤3.15 ≥2.45,≤3.05 <![CDATA[ -6.0D ]]> ≥4.65,≤5.65 ≥4.75,≤5.55 ≥4.85,≤5.45 <![CDATA[ -10.0D ]]> ≥7.75,≤8.75 ≥7.85,≤8.65 ≥7.95,≤8.55 <![CDATA[ -15.0D ]]> ≥11.60,≤12.60 ≥11.70,≤12.50 ≥11.80,≤12.40 <![CDATA[ -20.0D ]]> ≥15.40,≤16.40 ≥15.50,≤16.30 ≥15.60,≤16.20

[0191] Table 19-3 Defocus range required for contact lenses at different corrective diopters / unit D

[0192] <![CDATA[ Diopter ]]> <![CDATA[ Corneal or scleral contact lens defocus ]]> <![CDATA[ Corneal or scleral contact lens defocus ]]> <![CDATA[ Corneal or scleral contact lens defocus ]]> <![CDATA[ -1.0D ]]> ≥0.50,≤1.50 ≥0.60,≤1.40 ≥0.70,≤1.30 <![CDATA[ -3.0D ]]> ≥2.15,≤3.15 ≥2.25,≤3.05 ≥2.35,≤2.95 <![CDATA[ -6.0D ]]> ≥4.50,≤5.50 ≥4.60,≤5.40 ≥4.70,≤5.30 <![CDATA[ -10.0D ]]> ≥7.35,≤8.35 ≥7.45,≤8.25 ≥7.55,≤8.15 <![CDATA[ -15.0D ]]> ≥10.50,≤11.50 ≥10.60,≤11.40 ≥10.70,≤11.30 <![CDATA[ -20.0D ]]> ≥13.35,≤14.35 ≥13.45,≤14.25 ≥13.55,≤14.15

[0193] Table 19-4 The defocus range that needs to be achieved by intraocular lenses at different corrective diopters / unit D

[0194] <![CDATA[ Diopter ]]> <![CDATA[ Defocus of intraocular lens ]]> <![CDATA[ Defocus of intraocular lens ]]> <![CDATA[ Defocus of intraocular lens ]]> <![CDATA[ -1.0D ]]> ≥0.90,≤1.90 ≥1.00,≤1.80 ≥1.10,≤1.70 <![CDATA[ -3.0D ]]> ≥2.80,≤3.80 ≥2.90,≤3.70 ≥2.80,≤3.60 <![CDATA[ -6.0D ]]> ≥5.35,≤6.35 ≥5.45,≤6.25 ≥5.55,≤6.15 <![CDATA[ -10.0D ]]> ≥8.35,≤9.35 ≥8.45,≤9.25 ≥8.55,≤9.15 <![CDATA[ -15.0D ]]> ≥11.50,≤12.50 ≥11.60,≤12.40 ≥11.50,≤12.30 <![CDATA[ -20.0D ]]> ≥14.15,≤15.15 ≥14.25,≤15.05 ≥14.35,≤14.95

[0195] The diameter of the optical zone of the lens (frame glasses have a diameter of about 20mm, corneal contact lenses have a diameter of about 7.0mm, and crystalline lens has a diameter of about 4.0mm) corresponding to the position of the retina with a radius of 10mm (20mm diameter). Among them, frame glasses have a certain distance from the human eye, called the lens-eye distance, which is generally 12mm; corneal / scleral contact lenses are in direct contact with the cornea; phakic intraocular lenses are generally 2.5-3.5mm away from the cornea; cataract intraocular lenses are generally 3.5-5mm away from the cornea. The corresponding calculations are made according to the different positions of these optical lenses in the eye and the refractive conditions.

[0196] Among them, the refractive power of the lens adopts the thin lens calculation formula commonly used in the industry:

[0197]

[0198] Φ is the lens diopter, is the diopter of the front surface of the lens, is the diopter of the back surface of the lens, d is the thickness of the lens, and n is the refractive index of the lens.

[0199]

[0200] Where n' is the refractive index of the environment medium, R a , R p are the curvature radii of the front and rear surfaces, respectively.

[0201] The refractive power and defocus of the lens are calculated in the application environment of the lens, such as frame glasses, corneal contact lenses, etc., the application environment is air, and the medium refractive index is 1; for intraocular lenses, the application environment is inside the eye, the medium is intraocular fluid, and the medium refractive index is 1.336.

[0202] By adopting the above embodiment, a defocus lens for an ophthalmic product is proposed, wherein the defocus amount of the defocus lens is designed according to different gradients of the refractive power of the lens. On the one hand, the sufficiency of the defocus design amount can be fully guaranteed, and on the other hand, visual problems such as glare, interference, and deformation caused by blindly increasing the defocus design amount are avoided, thereby improving wearing comfort.

[0203] Fig.10 This is a real photo of the defocus lens designed according to this embodiment, and the defocus state of the lens can be clearly observed.

[0204] Fig.11The following are the actual imaging comparison diagrams (photos) of the defocus lens designed according to the present embodiment and similar products on the market. As shown in (a), the defocus design of similar products on the market is extremely large, and the image plane is blurred and distorted at all points around, which seriously affects the wearer's wearing experience and has adverse effects on sports vision and field of view. As shown in (b), the lens of the present invention can achieve defocusing under the above defocus design while ensuring that the wearer's visual quality is not disturbed to the greatest extent.

[0205] [Example 1]: Frame glasses, i.e., ophthalmic lenses worn outside the eyes at a certain distance from the cornea of ​​the eyes and having a certain refractive power, are used to correct refractive errors of the human eye.

[0206] The lens consists of a front surface and a back surface, with a center thickness of 3 mm and a material refractive index of 1.55. The front surface of the optical zone is a spherical surface, and the back surface is an aspherical surface. The aspherical surface shape expression is:

[0207]

[0208] Wherein, c is the reciprocal of the radius of curvature of the base spherical surface of the optical part, y is the vertical distance from any point on the curve to the abscissa axis (Z), Q is the aspheric coefficient, A 2i is the coefficient of the high-order term of the aspheric surface, and the aspheric surface is obtained by rotating the aspheric curve around the abscissa axis (Z). The lens parameters are shown in Table 20, where Ra refers to the radius of curvature of the front surface of the lens, Rp refers to the radius of curvature of the back surface of the lens, and CT refers to the center thickness of the lens.

[0209] Table 20 Design parameters of defocused frame glasses

[0210] Diopter / D Ra / mm Rp / mm CT / mm Q <![CDATA[A4]]> <![CDATA[A6]]> <![CDATA[A8]]> -1.00 901.5 341.192 3.0 40.0 8.955E-05 -1.947E-06 -1.501E-08 -3.00 170.4 87.763 3.0 -55.0 8.955E-05 -1.947E-06 -1.501E-08 -6.00 84.4 43.387 3.0 -21.8 8.955E-05 -1.947E-06 -1.501E-08 -10.00 53.8 26.659 3.0 -10.5 8.955E-05 -1.947E-06 -1.501E-08 -15.00 53.8 21.374 3.0 -10.67 8.955E-05 -1.947E-06 -1.501E-08 -20.00 53.8 17.838 3.0 -10.1 8.955E-05 -1.947E-06 -1.501E-08

[0211] Under the stated parameters, the defocus of the lens at a diameter of 20 mm is shown in Table 21.

[0212] Table 21 Lens defocus

[0213] Myopia Lens defocus -1.0D 0.80 -3.0D 2.25 -6.0D 4.65 -10.0D 7.75 -15.0D 11.6 -20.0D 15.4

[0214] The defocus amount of the defocus lens can make human eyes with different refractive states all be in a myopic defocus state, and will not affect wearing comfort due to excessive defocus amount.

[0215] [Example 2]: Frame glasses, the lens is composed of front and back surfaces, the total diameter of the lens is 80mm, the center thickness is 3mm, and the material refractive index is 1.60. The front surface of the optical zone is a spherical surface, and the radius of curvature is shown in Table 22. Three concentric rings with different radii of curvature are distributed on the back surface lens, and each ring is formed by a spherical surface. The center of the back surface of the lens with high, medium and low refractive powers, the second ring, the third ring curvature radius and the defocus amount of the lens at a diameter of 20mm are shown in Table 22.

[0216] Table 22 Lens parameters and defocus

[0217]

[0218]

[0219] The defocus amount of the ophthalmic lens varies with the lens diopter gradient, and the higher the diopter, the greater the defocus amount.

[0220] [Example 3]: Contact lens, the lens consists of front and back surfaces, the total diameter of the lens is 14.0mm, the center thickness is 0.1mm, and the material refractive index is 1.43. The radius of curvature of the back surface is 8.5mm, the back surface is spherical, and the front surface is aspherical. The surface shape expression is:

[0221]

[0222] Wherein, c is the reciprocal of the radius of curvature of the base spherical surface of the optical part, y is the vertical distance from any point on the curve to the abscissa axis (Z), Q is the aspheric coefficient, A 2i is the coefficient of the high-order term of the aspheric surface, and the aspheric surface is obtained by rotating the aspheric curve around the abscissa axis (Z). The lens parameters are shown in Table 23.

[0223] Table 23 Design parameters of defocused contact lenses

[0224] Diopter / D Ra / mm Rp / mm CT / mm Q <![CDATA[A4]]> <![CDATA[A6]]> <![CDATA[A8]]> -1.00 8.705 8.5 0.1 0.125 6.281E-006 -1.989E-008 -1.545E-009 -3.00 9.071 8.5 0.1 0.585 6.281E-006 -1.989E-008 -1.545E-009 -6.00 9.682 8.5 0.1 1.380 6.281E-006 -1.989E-008 -1.545E-009 -10.00 106.6 8.5 0.1 2.680 6.281E-006 -1.989E-008 -1.545E-009 -15.00 12.130 8.5 0.1 5.050 6.281E-006 -1.989E-008 -1.545E-009 -20.00 14.113 8.5 0.1 8.730 6.281E-006 -1.989E-008 -1.545E-009

[0225] Under the stated parameters, the defocus of the lens at a diameter of 7 mm is shown in Table 24.

[0226] Table 24 Lens defocus

[0227] Myopia Lens defocus -1.0D 0.50 -3.0D 2.15 -6.0D 4.50 -10.0D 7.35 -15.0D 10.50 -20.0D 13.35

[0228] [Example 4]: RGP, the lens is composed of front and back surfaces, the total diameter of the lens is 10.6mm, the center thickness is 0.15mm, and the material refractive index is 1.43. The back surface of the optical zone is a spherical surface with a curvature radius of 7.8mm. Three concentric rings with different curvature radii are distributed on the front surface lens, and each ring is formed by a spherical surface. The center of the back surface of the lens with high, medium and low refractive powers, the second ring, the third ring curvature radius and the defocus amount of the lens at a diameter of 7mm are shown in Table 25.

[0229] Table 25 Lens parameters and defocus

[0230]

[0231] The defocus amount of the ophthalmic lens varies with the lens diopter gradient, and the higher the diopter, the greater the defocus amount.

[0232] [Example 5]: A phakic intraocular lens, the lens is composed of front and back surfaces, the total diameter of the lens optical zone is 6.0 mm, the center thickness is 0.2 mm, and the material refractive index is 1.50. The front surface of the optical zone is a plane, and the back surface is an aspherical surface. The surface shape expression is:

[0233]

[0234] Wherein, c is the reciprocal of the radius of curvature of the basic spherical surface of the optical part, y is the vertical distance from any point on the curve to the horizontal axis (Z), Q is the aspheric coefficient, A2i is the coefficient of the high-order term of the aspheric surface, and the aspheric surface is obtained by rotating the aspheric curve around the horizontal axis (Z) with symmetry. The lens parameters are shown in Table 26.

[0235] Table 26 High, medium and low aspheric coefficients

[0236] Diopter / D Rp / mm Q A4 A6 A8 -1.00 -71.96 2745 -1.631E-005 -7.601E-005 2.079E-005 -3.00 -585.97 -1.000E-004 -1.135E-003 1.748E-005 -2.052E-007 -6.00 24.42 66.5 -5.003E-003 2.296E-004 -1.422E-005 -10.00 16.40 22.20 -5.003E-003 2.296E-004 -1.422E-005 -15.00 14.00 0.8 -5.003E-003 2.296E-004 -1.422E-005 -20.00 9.81 -23.000 -5.288E-003 1.019E-004 2.095E-005

[0237] Under the stated parameters, the defocus of the lens at a diameter of 4 mm is shown in Table 27.

[0238] Table 27 Lens defocus

[0239] Myopia Lens defocus -1.0D 0.90 -3.0D 2.80 -6.0D 5.35 -10.0D 8.35 -15.0D 11.50 -20.0D 14.15

[0240] It is worth noting that in the first to third embodiments described above, the diopter of the lens and the minimum defocus amount are described by taking the diopter of the lens as -1.0D, -3.0D, -6.0D, -10.0D, -15.0D, and -20.0D as examples. However, the scheme described in the present invention is not limited to the above-listed values. Other values ​​not listed, such as greater than -1.0D, other diopters between the listed diopter values, and less than -20.0D, have corresponding minimum defocus values ​​that are respectively less than the minimum defocus value corresponding to -1.0D, between the listed minimum defocus values, and greater than the minimum defocus value corresponding to -20.0D. The main purpose of the present invention is to protect that the corrected diopter of the lens and the minimum defocus amount to be achieved as a whole present a trend that the higher the corrected diopter of the ophthalmic defocus lens (i.e., the more negative the diopter value of the lens) is, the greater its minimum defocus amount is.

[0241] [Third embodiment]

[0242] The present embodiment relates to an ophthalmic defocus lens design method and device based on the technical ideas in the above-mentioned embodiments. The ophthalmic defocus lens design method and device can be implemented by a computer (computing device) having a processor and a memory. The memory stores program instructions. When the program instructions are executed, the processor executes the steps of the ophthalmic defocus lens design method or exerts the function of the ophthalmic defocus lens design device.

[0243] The method and device involved in this embodiment are described in detail below. The method and device are implemented based on the above embodiment, so they are only briefly described. For the omitted parts, please refer to the above embodiment.

[0244] This embodiment provides an ophthalmic defocus lens design device, which designs an ophthalmic defocus lens according to a peripheral defocus model based on retinal morphology. The peripheral defocus model based on retinal morphology is constructed by the following modeling method, which includes the following steps:

[0245] A refractive error analysis system model building step, building a refractive error analysis system including a standard human eye model and a myopia and / or hyperopia degree model;

[0246] The step of calculating the axial length of the eye is to calculate the axial length of the eye under different refractive errors according to the refractive error analysis system model shown;

[0247] a retinal relative distance calculation step, calculating the relative distance between the retina of the ametropic eye and the retina of the standard eye at different fundus positions at different axial lengths calculated in the axial length calculation step;

[0248] The defocus amount calculation step calculates the degree of vision correction lens corresponding to different positions of the retina under different degrees of myopia and / or hyperopia based on the relative distance obtained in the retinal relative distance calculation step, so as to obtain the defocus amount distribution of the retina with different refractive errors.

[0249] Optionally, in the retinal relative distance calculation step, the shapes of the ametropic eye and the standard eye are characterized by an ellipse, and the major axis of the ellipse represents the axial length of the eye, so as to calculate the relative distance between the retina of the ametropic eye and the retina of the standard eye.

[0250] Optionally, the relative distance between the retina of the ametropic eye and the retina of the standard eye is calculated as follows:

[0251] (1) The eyeball is considered as an ellipse with a major axis and a minor axis. The radius of curvature of the retina is the radius of curvature of the vertex of the major axis of the ellipse. A rectangular coordinate system is established with the center of the ellipse as the origin. The expression of the ellipse is: 2 / a 2 +y 2 / b 2 =1, where a is half the axial length of the eye, a=L / 2, L is the axial length of the eye; b is half the height of the eyeball;

[0252] (2) The height of each point on the retina is the difference between the coordinate of point x and a at different y values. The calculation method is:

[0253] (3) Keep the eyeball height unchanged and lengthen the eye axis, that is, keep the minor axis of the ellipse unchanged and change the major axis. Calculate the height of each point on the retina under the new major axis of the ellipse: Among them, a'=L' / 2, L' is the axial length of the eye that is elongated after myopia;

[0254] (4) Calculate the relative distance between the retina and the standard eye: Δh = 2*(h'-h).

[0255] In addition, this embodiment also provides an ophthalmic defocus lens design device, which calculates the defocus distribution at different positions of the retina according to the retinal curvature model of the ametropia eye, and designs an ophthalmic defocus lens according to the defocus distribution.

[0256] The retinal curvature model of the ametropia eye is that the axial distance of the retina at different positions from the center point satisfies the polynomial:

[0257]

[0258] Among them, Δd is the axial distance of the retina from the center point at different positions, r is the distance of the peripheral retina from the center point, a iAll are coefficients.

[0259] Alternatively, the axial distance between a point in the peripheral region of the retina and the center is linearly related to the degree of refractive error:

[0260]

[0261] where Δd m is the axial distance between the retina with a radius of m and the center of the retina, is the refractive error of the retina, and f and g are coefficients.

[0262] In addition, this embodiment also provides an ophthalmic defocus lens design device, which calculates the defocus distribution at different positions of the retina according to the retinal defocus distribution model of myopia, and designs an ophthalmic defocus lens according to the defocus distribution. The defocus distribution model describes the mathematical relationship between the refractive error of the retina periphery and the refractive error of the central retina, and satisfies the following formula:

[0263]

[0264] Where ΔD is the difference in refractive error between a point on the periphery of the retina and the center point when the light is focused on that point, r is the distance from the periphery of the retina to the center point, and A is i All are coefficients.

[0265] Optionally, the difference in refractive error between a point on the peripheral region of the retina and a central point is linearly related to the degree of refractive error:

[0266]

[0267] Where ΔD m is the difference in refractive error between the point with radius m on the retina and the center of the retina. is the refractive error of the retina, and k and b are coefficients.

[0268] Beneficial Effects

[0269] By adopting the above implementation mode, a peripheral defocus model and modeling method based on retinal morphology, and a retinal morphology and defocus distribution model based on the standard human eye are proposed, so that the design of ophthalmic defocus products has a basis and method to follow, which solves the blind design status in the industry. By designing ophthalmic defocus lenses by using the models and modeling methods, ophthalmic defocus lens design methods and devices, computing devices, computer-readable storage media, etc. in the above implementation modes, on the one hand, the adequacy of the defocus design amount can be fully guaranteed, and on the other hand, visual problems such as glare, interference, and deformation caused by blindly increasing the defocus design amount are avoided, thereby improving wearing comfort.

Claims

1. An ophthalmic defocus lens, comprising an optical zone, wherein the optical zone comprises a central optical zone and a peripheral defocus zone, characterized in that: The defocus amount of the peripheral defocus zone is set according to the corrective diopter of the ophthalmic defocus lens, and the greater the absolute value of the corrective diopter of the ophthalmic defocus lens, the greater the defocus amount. The peripheral defocus zone has a positive defocus amount, and the absolute value of the diopter of the peripheral defocus zone is greater than that of the central optical zone, For frame spectacle lenses worn outside the eye, the defocus values ​​at different corrected diopters at a central optical zone diameter of about 20 mm are shown in the following table: 。 2. An ophthalmic defocus lens, which is a corneal or scleral contact lens worn outside the eye, comprising an optical zone, wherein the optical zone comprises a central optical zone and a peripheral defocus zone, characterized in that: The defocus amount of the peripheral defocus zone is set according to the corrective diopter of the ophthalmic defocus lens, and the greater the absolute value of the corrective diopter of the ophthalmic defocus lens, the greater the defocus amount. The peripheral defocus zone has a positive defocus amount, and the absolute value of the diopter of the peripheral defocus zone is greater than that of the central optical zone. The defocus amount of the ophthalmic defocus lens at different corrected diopters at a diameter of about 7.0 mm in the central optical zone is shown in the following table. 。 3. An ophthalmic defocus lens, which is an intraocular artificial lens implanted in the eye, comprises an optical zone, wherein the optical zone comprises a central optical zone and a peripheral defocus zone, wherein: The defocus amount of the peripheral defocus zone is set according to the corrective diopter of the ophthalmic defocus lens, and the greater the absolute value of the corrective diopter of the ophthalmic defocus lens, the greater the defocus amount. The peripheral defocus zone has a positive defocus amount, and the absolute value of the diopter of the peripheral defocus zone is greater than that of the central optical zone. The defocus amount of the intraocular lens at different corrected diopters at an optical zone diameter of about 4.0 mm is as shown in the following table. 。 4. The ophthalmic defocus lens according to any one of claims 1 to 3, characterized in that: The optical zone achieves defocus design through an aspherical surface, and the aspherical surface shape expression is: Where c is the reciprocal of the radius of curvature of the optical base spherical surface, y is the vertical distance from any point on the curve to the horizontal axis (Z), Q is the aspheric coefficient, A 2i is the high-order coefficient of the aspheric surface, and the aspheric surface is obtained by rotating the aspheric surface curve around the abscissa axis (Z).

5. The ophthalmic defocus lens according to any one of claims 1 to 3, characterized in that: The optical zone is composed of concentric rings with different curvature radii to achieve a defocus design.

6. The ophthalmic defocus lens according to any one of claims 1 to 3, characterized in that: The corrective diopter of the ophthalmic defocus lens is 0 to -20D, 0 to -10D or 0 to -6.0D.

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