Ophthalmic lenses with critical light addition positions

Abstract

The present disclosure relates to an ophthalmic lens having a critical positive power position, and more particularly to an ophthalmic lens for preventing the occurrence of myopia or delaying the progression of myopia. Along the direction from the center to the edge of the optical zone of the ophthalmic lens, a first specified power P1 and a prescription power P0 are sequentially provided; wherein, the first specified power P1 is the prescription power P0 plus a first additional power P A1 , and the distance r1 of the first specified power P1 from the optical center of the lens is 0.75 - 0.95 mm, the distance r0 of the prescription power from the optical center of the lens is 2.5 - 3.5 mm, and the power between the first specified power and the prescription power changes gradually in a specified manner. By performing positive power treatment at a specific position of the lens, after the narrow light beam passing through the specific position passes through the center of the pupil, it will irradiate the area within the range of 10 degrees to 20 degrees beside the center of the retinal macula. Myopic defocus within this area range has a better myopia control effect.

Description

Technical Field

[0001] The present disclosure relates to ophthalmic lenses, and more particularly, to an ophthalmic lens having a critical addition position, which is used to prevent the occurrence of myopia or delay the development of myopia. Background Art

[0002] The human eye has a complex optical system, including: cornea, anterior chamber (aqueous humor), iris (pupil), vitreous body, retina, etc. Through the refraction imaging of the three interfaces of air - cornea, aqueous humor - lens, and lens - vitreous body, the human eye can form an inverted image on the retina, where the ciliary muscle plays a focusing role by changing the curvature of the lens. In order to form a clear image perception, the optical system of the eye should produce an image focused on the retina. When the on - axis image is focused in front of or behind the fovea centralis of the retina due to various reasons, resulting in blurred vision, the commonly known optical disorders are formed: myopia or hyperopia. The eye may also have other visual defects, such as astigmatism or higher - order optical aberrations such as spherical aberration, coma aberration, etc.

[0003] Among various visual defects, the incidence of myopia is increasing year by year globally, especially among teenagers. It is estimated that by 2050, the global myopic population will reach approximately 5 billion. Myopia may develop into high myopia, and high myopia is closely related to the risk of various ophthalmic diseases, such as retinal detachment, cataract, macular hemorrhage and macular degeneration, glaucoma, etc. The age range of 0 - 12 years is the sensitive period of visual development. At birth, the human eye is generally hyperopic, that is, the axial length of the eyeball is too short relative to its optical power. The eye axis gradually grows with age, and its elongation process is controlled by a feedback mechanism usually called the emmetropization process. During the emmetropization process, the eye axis grows under the control of the position of the focus relative to the retina, but it cannot grow shorter. Therefore, it has been proposed that the progression of myopic refractive error can be controlled by positioning the focus in front of the retina.

[0004] Generally, the best - focused surface formed by light rays incident at different field angles is called the Petzval surface. When the Petzval surface is in front of the retina, it is called myopic defocus, and vice versa is called hyperopic defocus. The Petzval surface produced by a conventional single - focus spherical lens is spherical, while the eyeball is generally ellipsoidal. Therefore, the peripheral Petzval surface is located behind the retina, forming hyperopic defocus and promoting the progression of myopic refractive error. Currently, the mainstream design concept of myopia prevention and control lenses is center - for - distance (CD), that is, the central area of the lens has a prescription power for correcting distance vision, and the periphery is an area with a positive addition power, which is used to form myopic defocus in front of the retina, so as to achieve the effect of inhibiting or slowing down the growth of the eye axis.

[0005] For example, CN110068937A discloses an ophthalmic lens having an optically non-concentric region for myopia control. The lens includes a central region, at least one treatment region, and a transition region therebetween. The central region has a negative optical power for myopia vision correction, while the treatment region minimizes the generation of a focal point behind the retinal plane of the wearer's eye through a positive additional optical power.

[0006] CN207867163U discloses a myopia control lens with peripheral defocus formed by an aspherical surface. The lens includes a central optical region and a peripheral optical region surrounding the central optical region. The central optical region is used to form a clear image on the retina, while the peripheral optical region has an aspherical outer surface and causes the passing light to form a peripheral defocus image region in front of the retina of the eye.

[0007] CN104136964B discloses a multifocal optical lens that can be used to treat presbyopia or myopia progression. The lens includes a central optical region and a peripheral optical region that generate different focal points, providing a central refractive power for distant vision and a peripheral refractive power for near vision, respectively.

[0008] E.L. Smith III et al. (Eccentricity-dependent effects of simultaneous competing defocus on emmetropization in infant rhesus monkeys, Vision Research, 17(3):32 - 40, 2020) used a bifocal lens (a central zero diopter region and a concentric annular diopter region with alternating +3D and zero diopters around it). By controlling the diameter of the central zero diopter region, objects above a certain eccentricity are imaged only through the bifocal peripheral region. It was thus found that compared with myopic defocus applied at a larger eccentricity, the competing myopic defocus signal applied near the fovea has a stronger and more consistent effect on slowing the axial growth of the eye axis.

[0009] However, the myopia prevention and control effects of existing lenses are not satisfactory. Therefore, there is a need for a new lens design that has the effect of preventing myopia occurrence or delaying myopia development. Summary of the Invention

[0010] The present invention provides an ophthalmic lens. Along the direction from its center to the edge in the optical region, a first specified optical power P1 and a prescription optical power P0 are successively provided; wherein, the first specified optical power P1 is the prescription optical power P0 plus a first additional optical power P A1and the distance r1 from the first specified diopter P1 to the optical center of the lens is 0.75 - 0.95 mm, the distance r0 from the prescribed diopter P0 to the optical center of the lens is 2.5 - 3.5 mm, and the diopter between r1 and r0 varies gradually in a specified manner.

[0011] In some embodiments, an incident light beam parallel to the optical axis of the ophthalmic lens, after passing through the first specified diopter P1, irradiates an area within 15 degrees beside the center of the macula of the retina.

[0012] In some embodiments, the first additional diopter P A1 is selected from +1.00D to +6.00D, preferably +1.20D to +5.00D, more preferably +1.50D to +4.00D, and most preferably +2.00 to +3.00D.

[0013] In some embodiments, within the area between r0 and the edge of the optical zone, the diopter of the lens is constant at the prescribed diopter P0.

[0014] In some embodiments, a second specified diopter P2 is further provided between the center of the optical zone and the first specified diopter, and the second specified diopter P2 is the prescribed diopter P0 plus a second additional diopter P A2 and the distance r2 from the second specified diopter P2 to the optical center of the lens is 0.47 - 0.67 mm; the diopter between r2 and r1 varies gradually in a specified manner.

[0015] In some embodiments, an incident light beam parallel to the optical axis of the ophthalmic lens, after passing through the second specified diopter P2, irradiates an area within 10 degrees beside the center of the macula of the retina.

[0016] In some embodiments, the second additional diopter P A2 is the same as or different from the first additional diopter P A1 and is selected from +1.00D to +8.00D, preferably +1.20D to +7.00D, more preferably +1.50D to +6.00D, and most preferably +2.00 to +4.00D.

[0017] In some embodiments, a third specified diopter P3 is further provided between the first specified diopter P1 and the prescribed diopter P0, and the third specified diopter P3 is the prescribed diopter P0 plus a third additional diopter P A3 and the distance r3 from the third specified diopter P3 to the optical center of the lens is 1.05 - 1.25 mm, and the diopter between r1 and r3, and between r3 and r0 varies gradually in a specified manner.

[0018] In some embodiments, an incident light beam parallel to the optical axis of the ophthalmic lens, after passing through the third specified diopter P3, irradiates an area within 20 degrees beside the center of the macula of the retina.

[0019] In some embodiments, the third additional dioptric power P A3 is greater than 0 and less than the first additional dioptric power P A1 .

[0020] In some embodiments, the dioptric power at the optical center of the lens is selected from P0 to P0 + 8.00 D.

[0021] In some embodiments, the ophthalmic lens is a contact lens, a scleral lens, or a corneal inlay.

[0022] In some embodiments, the ophthalmic lens further comprises one or more stabilization features.

[0023] The technical solution provided by the present invention adopts a center-for-near (CN) design, sets the prescription dioptric power at the outer periphery of the optical zone of the lens, and also performs additional power treatment at specific positions. On the one hand, this avoids the situation where the peripheral Petzval surface is located behind the retina, and on the other hand, it ensures that myopic defocus is generated in the area within 20 degrees beside the center of the retinal macula. The combined action of the two mechanisms enables the lens of the present invention to have an unexpected myopia control effect. BRIEF DESCRIPTION OF THE DRAWINGS

[0024] Figure 1 is a schematic diagram of a lens used in the prior art for preventing myopia occurrence and controlling myopia progression;

[0025] Figure 2 shows the working principle diagram of the lens of the present invention when setting the first specified dioptric power P1;

[0026] Figure 3 shows the curve of the dioptric power of the lens varying with distance when setting the first specified dioptric power P1;

[0027] Figure 4 shows another curve of the dioptric power of the lens varying with distance when setting the first specified dioptric power P1;

[0028] Figure 5 shows yet another curve of the dioptric power of the lens varying with distance when setting the first specified dioptric power P1;

[0029] Figure 6 shows yet another curve of the dioptric power of the lens varying with distance when setting the first specified dioptric power P1, the second specified dioptric power P2, and the third specified dioptric power P3;

[0030] Figure 7 shows the peripheral defocus diopter curve of an existing CD lens after setting the specified dioptric power;

[0031] Figure 8Shows the peripheral defocus diopter curve diagram after setting a specified diopter in the ophthalmic lens provided by the present invention. Detailed implementation mode

[0032] The exemplary embodiments of the present invention will be described below with reference to the accompanying drawings. Unless otherwise defined, all technical and / or scientific terms used herein have the same meaning as commonly understood by those of ordinary skill in the art to which this application belongs.

[0033] Figure 1 Shows a schematic diagram of an optical lens disclosed in CN207867163U, as a representative example of the prior art design adopting peripheral defocus. Among them, the optical lens 1 includes a central optical zone 11 and a peripheral optical zone 12, and the negative diopter of the peripheral optical zone is lower than that of the central optical zone. The light passing through the central optical zone forms a focal point 211 on the retina, thereby forming a clear image, while the light passing through the peripheral optical zone forms a focal point 212 in front of the retina.

[0034] Figure 2 Shows the working principle diagram when the first specified diopter P1 is set for the lens of the present invention. As Figure 2 shown, the first specified diopter P1 and the prescription diopter P0 are sequentially provided in the optical zone of the lens along the direction from its center to the edge; among them, the first specified diopter P1 is a "key plus power position" of the lens, the diopter at this position is the specified diopter, and the form of the diopter change from this position to the prescription diopter position is the specified form. In the case of the present invention, the prescription diopter is 0 or a negative diopter that provides the best corrected vision for myopic patients. This diopter is specifically determined by a doctor or an optometrist. In addition, in the optical zone of the lens of the present invention, the diopter is symmetrically distributed around the center of the optical zone, and the drawings only show the situation on one side in an exemplary manner.

[0035] Specifically, the first specified diopter P1 is the prescription diopter P0 plus the first additional diopter P A1 . Among them, the first additional diopter P A1Selected from +1.00D to +6.00D, preferably +1.20D to +5.00D, more preferably +1.50D to +4.00D, and most preferably +2.00 to +3.00D. For example, it can be selected from +2.25D, +2.50D, +2.75D, +3.25D, +3.50D, +3.75D, +4.25D, +4.50D, +4.75D, +5.25D, +5.50D, +5.75D, etc. And the distance r1 from the first specified diopter P1 to the optical center of the lens is 0.75 - 0.95mm, preferably 0.80 - 0.90mm, still preferably 0.85mm, for example 0.75, 0.76, 0.77, 0.78, 0.79, 0.80, 0.81, 0.82, 0.83, 0.84, 0.85, 0.86, 0.87, 0.88, 0.89, 0.90, 0.91, 0.92, 0.93, 0.94, 0.95, 0.96, 0.97mm.

[0036] As Figure 2 shown, the incident light beam parallel to the optical axis of the lens, after passing through the first specified diopter, irradiates on a specified area beside the center of the macula of the retina. In the case of the present invention, the angle α by which it deviates from the optical axis is called the eccentricity, or the angle beside the center of the macula of the retina. The incident light beam parallel to the optical axis of the lens, after passing through the first specified diopter, irradiates on an area within 15 degrees (i.e., α = 15°) beside the center of the macula of the retina. Myopic defocus within the peripheral 20 - degree range beside the center of the macula of the retina has a more excellent myopia control effect, among which, myopic defocus produces the strongest myopia control effect at the 15 - degree position.

[0037] There is no particular limitation on the change in diopter between the center of the optical zone and the first specified diopter P1. Figure 3 shows the curve graph of the change in diopter of the lens with distance when setting the first specified diopter P1, where the change in diopter between the first specified diopter P1 and the center of the optical zone is a natural continuation of the change in diopter between the prescription diopter and the first specified diopter; Figure 4 shows another curve graph of the change in diopter of the lens with distance when setting the first specified diopter P1; Figure 5 shows yet another curve graph of the change in diopter of the lens with distance when setting the first specified diopter P1.

[0038] As Figures 3 to 5 shown, the distance r0 from the prescription diopter P0 to the optical center of the lens is 2.5 - 3.5mm, preferably, the distance r0 is 2.75mm, and the diopter between the first specified diopter P1 and the prescription diopter P0 gradually changes in a specified manner, and this change in optical power satisfies the following formula:

[0039] P(r) = P0 + f A1 (r - r1)+PA1

[0040] where r is the distance to the optical center of the lens, and f A1 is a first-degree polynomial, second-degree polynomial, or Nth-degree polynomial of r, r1 is the distance from the first specified power P1 to the optical center of the lens, P0 is the prescribed power, and P A1 is the first additional power; satisfying P(r1) = P0 + P A1 .

[0041] As an example, taking 0.85 mm from the center of the contact lens as the key plus power position (i.e., r1 = 0.85 mm), and P0 = -3 D, P A1 = +2.5 D, the power calculation method between the first specified power P1 and the prescribed power P0 can be any of the following:

[0042] First-degree curve

[0043] P(r) = -3 - 1.316(r - 0.85) + 2.5 (Equation I)

[0044] Second-degree curve

[0045] P(r) = -3 - 0.365(r - 0.85) 2 - 0.6205(r - 0.85) + 2.5 (Equation II)

[0046] Or

[0047] P(r) = -3 - 0.692(r - 0.85) 2 + 2.5 (Equation III)

[0048] Third-degree curve

[0049] P(r) = -3 - 0.364(r - 0.85) 3 + 2.5 (Equation IV)

[0050] Or

[0051] P(r) = -3 - 0.378(r - 0.85) 3 + 0.025(r - 0.85) 2 + 2.5 (Equation V)

[0052] In an embodiment of the present invention, within the region between the prescribed diopter and the edge of the optical zone, the diopter of the lens remains constant at the prescribed diopter. The ophthalmic lens of the present invention can be a contact lens, a scleral lens, or a corneal inlay. Among them, in various ophthalmic lenses, the diameter of the optical zone of the lens is generally 7.0 - 12.0 mm. Those skilled in the art can understand that the size of the optical region of the ophthalmic lens depends on the palpebral fissure height and pupil diameter of the wearer. Therefore, those skilled in the art can select an appropriate size of the optical zone according to needs.

[0053] As Figures 3 to 5 shown, the diopter between the optical center of the lens and the first specified diopter P1 is not restricted and can be set according to the lens performance. Among them, the diopter of the optical center of the lens can be any value between P0 and P0 + 8.00 D. The change mode of the diopter between the optical center of the lens and the first specified diopter can be a gradual change, a stepped change, or a constant value, etc. The preferred mode is a gradual change (as Figures 3 to 5 shown), or constantly equal to the first specified diopter. Because a sudden change in the optical power makes processing difficult and may cause a sudden change in the surface morphology. A sudden change in the optical power or the surface morphology of the lens generates scattering or diffraction in the mutation region, but the scattering may cause diffused light to irradiate the macula area, generating halos, light spots, and reducing the contrast sensitivity.

[0054] In an embodiment of the present invention, there can be more than one "key power addition position" on the lens. More power addition positions can also be set on the lens, and the power addition amount at the power addition positions can be set. Here, taking three power addition positions as an example, that is, a second specified diopter and a third specified diopter are added to the lens.

[0055] As Figure 6 shown, a second specified diopter P2 can also be provided between the center of the optical zone and the first specified diopter. The second specified diopter P2 is the prescription diopter P0 plus the second additional diopter P A2 . Among them, the second additional diopter P A2 and the first additional diopter P A1The same or different, selected from +1.00D to +8.00D, preferably +1.20D to +7.00D, more preferably +1.50D to +6.00D, and most preferably +2.00 to +4.00D. For example, it can be selected from +2.25D, +2.50D, +2.75D, +3.25D, +3.50D, +3.75D, +4.25D, +4.50D, +4.75D, +5.25D, +5.50D, +5.75D, etc. And the distance r2 from the second specified diopter P2 to the optical center of the lens is 0.47 - 0.67mm, preferably 0.50 - 0.64mm, still preferably 0.57mm, such as 0.47, 0.48, 0.49, 0.50, 0.51, 0.52, 0.53, 0.54, 0.55, 0.56, 0.57, 0.58, 0.59, 0.60, 0.61, 0.62, 0.63, 0.64, 0.65, 0.66, 0.67mm. The incident light beam parallel to the optical axis of the ophthalmic lens irradiates the area within 10 degrees beside the center of the macula of the retina after passing through the second specified diopter P2. Similarly, there is no particular limitation on the change in diopter between the center of the optical zone and the second specified diopter P2. In the preferred case, the diopter between the center of the optical zone and r2 is constant at the second specified diopter P2.

[0056] A third specified diopter P3 can also be provided between the first specified diopter P1 and the prescription diopter P0. The third specified diopter P3 is the prescription diopter P0 plus the third additional diopter P A3 . Among them, the third additional diopter P A3 is greater than 0 and less than the first additional diopter P A1 . And the distance r3 from the third specified diopter P3 to the optical center of the lens is 1.05 - 1.25mm, preferably 1.10 - 1.20mm, still preferably 1.15mm, such as 1.05, 1.06, 1.07, 1.08, 1.09, 1.10, 1.11, 1.12, 1.13, 1.14, 1.15, 1.16, 1.17, 1.18, 1.19, 1.20, 1.21, 1.22, 1.23, 1.24, 1.25mm. The incident light beam parallel to the optical axis of the ophthalmic lens irradiates the area within 20 degrees beside the center of the macula of the retina after passing through the third specified diopter P3.

[0057] The diopter between the second specified diopter P2 and the first specified diopter P1 gradually changes in a specified manner, and this gradual change in optical power satisfies the following formula:

[0058] P(r) = P0 + f A2 (r - r2) + P A2

[0059] where r is the distance to the optical center of the lens, fA2 is a first-degree polynomial, second-degree polynomial, or N-degree polynomial of r, r2 is the distance from the second specified dioptric power P2 to the optical center of the lens, P0 is the prescribed dioptric power, and P A2 is the second additional dioptric power.

[0060] As Figure 6 shown, the dioptric power between the first specified dioptric power P1 and the third specified dioptric power P3 changes gradually in a specified manner, and this gradual change in the optical power satisfies the following formula:

[0061] P(r) = P0 + f A1 (r - r1) + P A1

[0062] where r is the distance to the optical center of the lens, and f A1 is a first-degree polynomial, second-degree polynomial, or N-degree polynomial of r, r1 is the distance from the first specified dioptric power to the optical center of the lens, P0 is the prescribed dioptric power, and P A1 is the first additional dioptric power; and the dioptric power between the third specified dioptric power P3 and the prescribed dioptric power P0 changes gradually in a specified manner, and the dioptric power satisfies the following formula:

[0063] P(r) = P0 + f A3 (r - r3) + P A3

[0064] where r is the distance to the optical center of the lens, and f A3 is a first-degree polynomial, second-degree polynomial, or N-degree polynomial of r, r3 is the distance from the third specified dioptric power P3 to the optical center of the lens, P0 is the prescribed dioptric power, and P A3 is the third additional dioptric power.

[0065] Thus, in the embodiments of the present invention, by additionally providing the second specified dioptric power P2 and the third specified dioptric power P3 on the lens, myopic defocus is generated in a wider range beside the center of the retinal macula, thereby providing a stable myopia control effect. It should be emphasized that this embodiment only takes three additional power positions as an example, but is not limited to the above three additional power positions, and the lens can be provided with different additional powers according to actual use and performance requirements.

[0066] The technical solution provided by the present invention performs additional power processing at specific positions on the lens, that is, specifies the dioptric power at specific positions. After the narrow light beam passing through the specific position passes through the pupil center, it will irradiate the area within 10 degrees to 20 degrees beside the center of the retinal macula. Myopic defocus within this area range has a better myopia control effect. Therefore, as much myopic defocus as possible should be generated at 10 to 20 degrees, and 15 degrees is the most important. To reflect the advantages of the lens of the present invention, the inventor adopted the following simulation method to compare the lens of the prior art with the lens of the present invention.

[0067] Simulation method

[0068] As described by Liou et al. (Hwey-Lan Liou and Noel A. Brennan, "Anatomically accurate, finite model eye for optical modeling," J. Opt. Soc. Am. A 14, 1684-1695 (1997)), the Liou & Brennan model eye was established in OpticStudio Zemax, and corresponding optical surfaces were added to the simulated eye according to the optical power of P(r) = P0 + SA * r^2 to simulate the corresponding contact lens.

[0069] Calculate the Zernike function coefficients at different field angles in OpticStudio Zemax, Zernike vsField, obtain the parameters of z4, z11, z22, z6, z12, z24 and the exit pupil diameter among them, and substitute them into the following formula to calculate the defocus diopter at different field angles.

[0070]

[0071] Result

[0072] Existing technology lenses are usually CD-designed. For example, a prescription power of -3D is set in the center. With SA = 0.33 D / mm, according to P(r) = P0 + SA * r^2, the power is increased by 0.24 D at 0.85 mm and 0.33 * 3^2 = 3 D at 3 mm. Figure 7 The change curve graph after setting the specified power in the existing CD lens is shown. As Figure 7 shown, through calculation, it can be known that within the 15-degree area beside the center of the retinal macula, only -0.24 D of myopic defocus is generated. Therefore, a better myopia control effect cannot be achieved.

[0073] For the ophthalmic lens in the embodiment of the present invention, a prescription power of -3D is set around the optical zone of the lens, and a first additional power P A1 of 2.76 D is set at 0.85 mm from the center of the ophthalmic lens. Therefore, the first specified power P1 is -0.24 D, and then the power is gradually increased from the prescription power to the first specified power and then towards the center of the ophthalmic lens. Figure 8 The peripheral defocus diopter curve graph after setting the specified power in the ophthalmic lens provided by the present invention is shown. As Figure 8As shown, within the 15-degree region beside the center of the retinal macula, a myopic defocus of -3.06D is generated. Therefore, the ophthalmic lens provided by the embodiment of the present invention has a better myopia control effect.

[0074] Example

[0075] In a preliminary study involving a group of 5 myopic patients, the effect of the lens of the present invention on delaying myopia progression was tested. The average age of the patients was 11 years. The base curve radius of the contact lenses used was 8.6 mm, and the diameter was 14.5 mm. Among them, the radius of the optical zone was 3.5 mm, and +2.50D of additional power was added at 0.85 mm. At the start of the experiment, the average spherical refractive power of the lenses used was -2.60D. The patients wore the lenses of the present invention every day, had an examination every 3 months and replaced the lenses with new ones. After wearing for 12 months, the average spherical lens was -2.90D, and the myopia degree progression was -0.30D.

[0076] According to the literature (Walline JJ et al. Effect of High Add Power, Medium Add Power, or Single-Vision Contact Lenses on Myopia Progression in Children: The BLINK Randomized Clinical Trial. JAMA. 2020; 324(6):571-580), under the same monitoring conditions, in the control of myopia with different additional power degrees of CD lens design, the average myopia progression in the +2.50D group was -0.60D per year, the average myopia progression in the +1.5D group was -0.89D per year, and the average myopia progression of the single-focus contact lenses in the control group was -1.05D per year. It can be seen that the correction method provided by the embodiment of the present invention is superior to the existing CD lens correction method.

[0077] Those skilled in the art will understand that the invention described herein can be varied and modified in addition to the specifically described content. The present invention is not limited to the specific structures described and shown herein, but includes all such variations and modifications that fall within its spirit and scope. Those skilled in the art can make any combination of any two or more of the features, structures or parts separately or jointly presented in this specification without departing from the essence and scope of the present invention.

Claims

1. An ophthalmic lens having a critical light addition position, characterized in that: The optical zone is provided with a first designated focal power P1 and a prescription focal power P0 in sequence from the center to the edge thereof; The first designated focal length P1 is the prescription focal length P0 plus the first additional focal length P A1 , and the distance r1 from the first designated focal power P1 to the optical center of the lens is 0.75-0.95 mm, The distance r0 between the prescription focal power P0 and the optical center of the lens is 2.75-3.5 mm. In the area from r0 to the optical center of the lens, the focal power of the ophthalmic lens is greater than the prescription focal power P0. The focal power between r1 and r0 changes gradually in a specified manner. The gradual change of focal length between r1 and r0 satisfies the following formula: P(r)=P0+f A1 (r-r1)+P A1 Where r is the distance to the optical center of the lens, f A1 is a linear polynomial, quadratic polynomial, or Nth-degree polynomial in r.

2. The ophthalmic lens according to claim 1, characterized in that An incident light beam parallel to the optical axis of the ophthalmic lens irradiates an area within 15 degrees around the center of the retinal macula after passing through a first specified focal power P1.

3. The ophthalmic lens according to claim 1 or 2, characterized in that: The first additional power PA1 is selected from +1.00D to +6.00D.

4. The ophthalmic lens according to claim 3, characterized in that The first additional power PA1 is selected from +1.20D to +5.00D.

5. The ophthalmic lens according to claim 4, characterized in that The first additional power PA1 is selected from +1.50D to +4.00D.

6. The ophthalmic lens according to claim 5, characterized in that The first additional power PA1 is selected from +2.00 to +3.00D.

7. The ophthalmic lens according to claim 1 or 2, characterized in that: In the region between r0 and the edge of the optical zone, the focal power of the lens is constant at the prescribed focal power P0.

8. The ophthalmic lens according to claim 1 or 2, characterized in that: A second designated focal power P2 is provided between the center of the optical zone and the first designated focal power. The second designated focal power P2 is the prescription focal power P0 plus the second additional focal power P A2 , and the distance r2 from the second specified focal power P2 to the optical center of the lens is 0.47-0.67 mm; the focal power between r2 and r1 changes gradually in a specified manner, The gradual change of focal length from r2 to r1 satisfies the following formula: P(r)=P0+f A2 (r-r2)+P A2 Among them, f A2 is a linear polynomial, quadratic polynomial, or Nth-degree polynomial in r.

9. The ophthalmic lens according to claim 8, characterized in that The incident light beam parallel to the optical axis of the ophthalmic lens irradiates an area within 10 degrees around the center of the retinal macula after passing through the second specified focal power P2.

10. The ophthalmic lens according to claim 8, characterized in that Second additional focal power P A2 With the first additional focal power P A1 The same or different, and the second additional focal power P A2 Select from +1.00D to +8.00D.

11. The ophthalmic lens according to claim 10, characterized in that Second additional focal power P A2 Select from +1.20D to +7.00D.

12. The ophthalmic lens according to claim 11, characterized in that Second additional focal power P A2 Select from +1.50D to +6.00D.

13. The ophthalmic lens according to claim 12, wherein: Second additional focal power P A2 Select from +2.00 to +4.00D.

14. The ophthalmic lens according to claim 1 or 2, characterized in that: A third designated focal length P3 is provided between the first designated focal length P1 and the prescription focal length P0. The third designated focal length P3 is the prescription focal length P0 plus a third additional focal length P A3 , and the distance r3 from the third designated focal power P3 to the optical center of the lens is 1.05-1.25 mm, and the focal power between r1 to r3 and r3 to r0 changes progressively in a designated manner, The gradual change of focal length between r1 and r3 satisfies the following formula: P(r)=P0+f A1 (r-r1)+P A1 The gradual change of focal length between r3 and r0 satisfies the following formula: P(r)=P0+f A3 (r-r3)+P A3 Among them, f A3 is a linear polynomial, quadratic polynomial, or Nth-degree polynomial in r.

15. The ophthalmic lens according to claim 14, characterized in that The incident light beam parallel to the optical axis of the ophthalmic lens is irradiated to an area within 20 degrees around the center of the retinal macula after passing through the third specified focal power P3.

16. The ophthalmic lens according to claim 14, wherein: The third additional focal power P A3 Greater than 0 and less than the first additional focal power P A1 .

17. The ophthalmic lens according to claim 1 or 2, characterized in that: The focal power of the optical center of the lens is equal to the first specified focal power.

18. The ophthalmic lens according to claim 1 or 2, characterized in that: The ophthalmic lens is a contact lens, a scleral lens, or a corneal inlay.

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