CN115220244A - Ophthalmic lens with critical addition location - Google Patents

Abstract

The present disclosure relates to an ophthalmic lens with a key light adding position, in particular to an ophthalmic lens for preventing myopia or delaying myopia development, wherein a first appointed focal power P1 and a prescription focal power P0 are sequentially arranged in an optical area of the ophthalmic lens along the direction from the center to the edge of the optical area; wherein the first prescribed focal power P1 is the prescribed focal power P0 plus the first addition focal power P _A1 And the distance r1 from the optical center of the lens to the first specific power P1 is 0.75-0.95mm, the distance r0 from the optical center of the lens to the prescription power is 2.5-3.5mm, and the power between the first specific power and the prescription power is gradually changed in a specific manner. By performing the light addition processing at a specific position of the lens, a narrow light beam passing through the specific position passes through the center of the pupil and then irradiates an area ranging from 10 degrees to 20 degrees beside the center of the macula lutea. The myopia out-of-focus in the area has better myopia control effect.

Description

Ophthalmic Lenses with Key Addition Locations

technical field

The present disclosure relates to an ophthalmic lens, and more particularly, to an ophthalmic lens having a key add-on location for preventing the occurrence of myopia or delaying the progression of myopia.

Background technique

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, in which the ciliary muscle can adjust the focus by changing the curvature of the lens. For clear image perception, the optical system of the eye should produce an image that is focused on the retina. When, for various reasons, the on-axis image is focused in front of, or behind the fovea, causing blurred vision, an optical disorder commonly known as nearsightedness or farsightedness develops. The eye may also have other vision defects such as astigmatism or higher order optical aberrations such as spherical aberration, coma, and the like.

Among various visual defects, the incidence of myopia is increasing year by year, especially among adolescents. It is estimated that by 2050, the global myopia population will reach about 5 billion. Myopia has the potential to develop into high myopia, which is closely associated with the risk of developing various eye diseases such as retinal detachment, cataracts, macular hemorrhage and macular degeneration, glaucoma, etc. 0 to 12 years old is a sensitive period for visual development. At birth, the human eye is generally hyperopic, meaning that the axial length of the eyeball is too short relative to its optical power. The axial length of the eye increases with age, and its elongation process is controlled by a feedback mechanism commonly referred to as emmetropization. During emmetropia, the axis of the eye is controlled by the position of the focal point relative to the retina, but cannot be shortened. Therefore, it has been proposed that the progression of myopic refractive error can be controlled by positioning the focus in front of the retina.

Usually, the best focusing surface formed by light incident at different field angles is called the Petzval surface. When the Petzval surface is in front of the retina, it is called myopic defocusing, and vice versa, it is hyperopic defocusing. The Petzval surface produced by the conventional monofocal spherical lens is spherical, while the eyeball is generally ellipsoid, so the peripheral Petzval surface is located behind the retina, resulting in hyperopia and defocus, which promotes the progression of myopic refractive error. At present, the mainstream design concept of myopia prevention and control lenses is center-for-distance (CD, center-for-distance), that is, the central area of the lens has the prescribed power for distance vision correction, and the periphery is the area with positive additional power. It is used to form myopia and defocus in front of the retina, so as to achieve the effect of inhibiting or slowing down the growth of the eye axis.

For example, CN110068937A discloses an ophthalmic lens having an optically non-coaxial zone for myopia control, the lens comprising a central zone, at least one treatment zone and a transition zone therebetween, the central zone having a central zone for Negative power for myopia correction, while the treatment zone minimizes the generation of focus behind the retinal plane of the wearer's eye through positive add power.

CN207867163U discloses a myopia control lens with an aspheric surface to form peripheral defocus, the lens includes a central optical zone and a peripheral optical zone surrounding the central optical zone, the central optical zone is used to form a clear image on the retina, and The peripheral optical zone has an aspherical outer surface and causes passing light to be imaged at the location of the peripheral out-of-focus image zone in front of the retina of the eye.

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

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) adopted a bifocal lens (zero diopter zone in the center, +3D and zero diopter around the periphery) Alternating concentric annular diopter zones), by controlling the diameter of the central zero diopter zone, so that objects above a certain eccentricity are imaged only through the double diopter peripheral zone, thus finding that compared with the myopic defocus imposed at larger eccentricities, Competing myopic defocus signals applied close to the fovea had a stronger and more consistent effect on slowing axial growth of the eye.

However, the myopia prevention and control effect of the existing lenses is not satisfactory. Therefore, there is a need for new lens designs that have the effect of preventing the occurrence of myopia or delaying the progression of myopia.

SUMMARY OF THE INVENTION

The present invention provides an ophthalmic lens, wherein a first specified power P1 and a prescription power P0 are sequentially arranged along the center to the edge direction in the optical zone; wherein, the first specified power P1 is the prescription power P0 plus the first specified power P0 The additional power P _A1 , and the distance r1 of the first specified power P1 from the optical center of the lens is 0.75-0.95mm, the distance r0 of the prescription power P0 from the optical center of the lens is 2.5-3.5mm, and the focal point between r1 and r0 The degree changes incrementally in the specified manner.

In some embodiments, the incident light beam parallel to the optical axis of the ophthalmic lens passes through the first specified power P1 and irradiates an area within 15 degrees of the center of the retinal macular.

In some embodiments, the first add power P _A1 is selected from +1.00D to +6.00D, preferably +1.20D to +5.00D, more preferably +1.50D to +4.00D, most preferably +2.00 to +3.00D .

In some embodiments, the power of the lens is constant at the prescription power P0 in the region between r0 and the edge of the optic zone.

In some embodiments, a second specified power P2 is further provided between the center of the optical zone and the first specified power, and the second specified power P2 is the prescribed power P0 plus the second additional power P _A2 , and The distance r2 of the second specified power P2 from the optical center of the lens is 0.47-0.67 mm; the power between r2 and r1 changes gradually in a specified manner.

In some embodiments, the incident light beam parallel to the optical axis of the ophthalmic lens passes through the second specified power P2 and irradiates an area within 10 degrees of the center of the retinal macular.

In some embodiments, the second add power P _A2 is the same as or different from the first add power P _A1 and is selected from +1.00D to +8.00D, preferably +1.20D to +7.00D, more preferably +1.50D to +6.00D, most preferably +2.00 to +4.00D.

In some embodiments, a third specified power P3 is provided between the first specified power P1 and the prescribed power P0, and the third specified power P3 is the prescribed power P0 plus the third additional power P _A3 , and the distance r3 of the third specified power P3 from the optical center of the lens is 1.05-1.25 mm, and the powers between r1 to r3 and r3 to r0 are gradually changed in a specified manner.

In some embodiments, the incident light beam parallel to the optical axis of the ophthalmic lens passes through a third specified power P3 and irradiates an area within 20 degrees of the center of the retinal macular.

In some embodiments, the third add power P _A3 is greater than 0 and less than the first add power P _A1 .

In some embodiments, the power of the optical center of the lens is selected from P0 to P0+8.00D.

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

In some embodiments, the ophthalmic lens further includes one or more stabilizing features.

The technical solution provided by the present invention adopts the design of center-for-near (CN, center-for-near), sets the prescription power on the outer periphery of the optical zone of the lens, and also performs light addition processing at a specific position, which avoids the need for The situation in which the peripheral Petzval plane is located behind the retina, on the other hand, ensures that the area within 20 degrees of the center of the macula produces myopic defocus. Both mechanisms work together to provide the lenses of the present invention with unexpected myopia control effects.

Description of drawings

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

Fig. 2 shows the working principle diagram of the lens of the present invention when the first specified power P1 is set;

Fig. 3 shows the graph of the change of the power of the lens with the distance when the first specified power P1 is set;

Fig. 4 shows another variation graph of the power of the lens with the distance when the first specified power P1 is set;

Fig. 5 shows another variation graph of the power of the lens with the distance when the first specified power P1 is set;

Fig. 6 shows another variation graph of the power of the lens with distance when the first specified power P1, the second specified power P2 and the third specified power P3 are set;

FIG. 7 shows a graph of the peripheral defocus diopter after setting a specified power in an existing CD lens;

FIG. 8 shows a graph of the peripheral defocus diopter after setting the specified power in the ophthalmic lens provided by the present invention.

Detailed ways

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 one of ordinary skill in the art to which this application belongs.

Figure 1 shows a schematic diagram of the optical lens disclosed in CN207867163U as a representative example of a prior art design employing peripheral defocus. Wherein, the optical lens 1 includes a central optical zone 11 and a peripheral optical zone 12, and the negative power of the peripheral optical zone is lower than that of the central optical zone. Light passing through the central optic zone forms a focal point 211 on the retina, resulting in a sharp image, while light passing through the peripheral optic zone forms a focal point 212 in front of the retina.

FIG. 2 shows the working principle diagram of the lens of the present invention when the first specified power P1 is set. As shown in Figure 2, the optical zone of the lens is sequentially provided with a first specified power P1 and a prescribed power P0 along the direction from the center to the edge; wherein, the first specified power P1 is a "key addition position" of the lens , the power of this position is the specified power, and the power change form from the position to the prescribed power position is the specified form. In the context of the present invention, the prescribed power is 0 or a negative power that provides best corrected visual acuity for myopic patients. This power is specifically determined by a doctor or optometrist. In addition, in the optical zone of the lens of the present invention, the power is symmetrically distributed around the center of the optical zone, and the drawings only show the situation of one side in an exemplary manner.

Specifically, the first specified power P1 is the prescription power P0 plus the first additional power P _A1 . Among them, the first additional power P _A1 is selected from +1.00D to +6.00D, preferably +1.20D to +5.00D, more preferably +1.50D to +4.00D, most preferably +2.00 to +3.00D. For example, it may 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 of the first specified power P1 from the optical center of the lens is 0.75-0.95mm, preferably 0.80-0.90mm, and preferably 0.85mm, such as 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.

As shown in Fig. 2, after the incident light beam parallel to the optical axis of the lens passes through the first specified power, it irradiates a specified area next to the center of the macula of the retina. In the context of the present invention, the angle α at which it deviates from the optical axis is referred to as eccentricity, or the paracentre angle of the retinal macular. After the incident light beam parallel to the optical axis of the lens passes through the first specified power, it irradiates an area within a range of 15° (ie α=15°) next to the center of the macula of the retina. The myopic defocus in the range of 20 degrees around the center of the retinal macular has a more excellent myopia control effect, and the myopia defocus at the position of 15 degrees produces the strongest myopia control effect.

There is no particular limitation on the power change between the center of the optical zone and the first specified power P1. Fig. 3 shows a graph showing the change of the power of the lens with distance when the first specified power P1 is set, wherein the power change between the first specified power P1 and the center of the optical zone is the prescription power to the first specified power The natural continuation of the power change between degrees; Fig. 4 shows another graph of the change of the power of the lens with distance when setting the first specified power P1; Fig. 5 shows the setting of the first specified power P1 Another graph of the change in the power of the lens with distance.

As shown in FIGS. 3 to 5 , the distance r0 from the prescription power P0 to the optical center of the lens is 2.5-3.5mm, preferably, the distance r0 is 2.75mm, and the focal point between the first specified power P1 and the prescription power P0 The optical power is gradually changed in a specified manner, and this optical power gradual change satisfies the following formula:

P(r)=P0+f _A1 (r-r1)+P _A1

Among them, r is the distance from the optical center of the lens, f _A1 is the first-order polynomial, second-order polynomial or N-degree polynomial of r, r1 is the distance from the first specified power P1 to the optical center of the lens, P0 is the prescription power, P _A1 is the first additional power; P(r1)=P0+P _A1 is satisfied.

As an example, taking 0.85mm from the center of the contact lens as the key addition position (ie, r1=0.85mm), and P0=-3D, P _A1 =+2.5D, between the first specified power P1 and the prescription power P0 The power calculation method of can be any of the following:

1st degree curve

P(r)=-3-1.316(r-0.85)+2.5 (Formula I)

quadratic curve

P(r)=-3-0.365(r-0.85) ² -0.6205(r-0.85)+2.5 (Formula II)

or

P(r)=-3-0.692(r-0.85) ² +2.5 (Formula III)

3rd degree curve

P(r)=-3-0.364(r-0.85) ³ +2.5 (Formula IV)

or

P(r)=-3-0.378(r-0.85) ³ +0.025(r-0.85) ² +2.5 (Formula V)

In the embodiment of the present invention, in the region between the prescription power and the edge of the optical zone, the power of the lens is constant as the prescription power. The ophthalmic lenses of the present invention may be contact lenses, scleral lenses, or corneal inlays. Among all kinds of 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 zone of the ophthalmic lens depends on the height of the palpebral fissure and the diameter of the pupil of the wearer. Therefore, those skilled in the art can select an appropriate size of the optical zone as required.

As shown in FIGS. 3 to 5 , the power between the optical center of the lens and the first specified power P1 is not limited, and can be set according to the performance of the lens, wherein the power of the optical center of the lens can be from P0 to P0+8.00D Any value between the optical center of the lens and the first specified power can be changed in a gradual way, a stepped way or a constant value, preferably a gradual way (as shown in Figures 3 to 5), or a constant value Equal to the first specified power. Because sudden changes in optical power make processing difficult, sudden changes in surface morphology may result. Sudden changes in optical power or lens surface morphology, resulting in scattering or diffraction in the abrupt region, but scattering may cause diffuse light to strike the macula, producing halos, flares, and reduced contrast sensitivity.

In the embodiment of the present invention, there may be more than one "critical light-adding position" on the lens, and more light-adding positions can also be set on the lens, and the light-adding amount of the light-adding position can be set. The following three light-adding positions are used. Take the position as an example, that is, adding a second specified power and a third specified power to the lens.

As shown in FIG. 6 , a second specified power P2 may be provided between the center of the optical zone and the first specified power, and the second specified power P2 is the prescribed power P0 plus the second additional power P _A2 . Wherein, the second additional power P _A2 is the same as or different from the first additional power P _A1 , and is selected from +1.00D to +8.00D, preferably +1.20D to +7.00D, more preferably +1.50D to +6.00D, Most preferably +2.00 to +4.00D. For example, it may 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 of the second specified power P2 from the optical center of the lens is 0.47-0.67mm, preferably 0.50-0.64mm, and 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 passes through the second specified power P2 and then irradiates an area within 10 degrees next to the center of the macula of the retina. Similarly, there is no particular limitation on the power change between the center of the optical zone and the second specified power P2. In a preferred case, the power between the center of the optical zone and r2 is constant as the second specified power P2.

A third specified power P3 may also be provided between the first specified power P1 and the prescribed power P0, and the third specified power P3 is the prescribed power P0 plus the third additional power P _A3 . Wherein, the third additional power P _A3 is greater than 0 and smaller than the first additional power P _A1 . And the distance r3 of the third specified power P3 from the optical center of the lens is 1.05-1.25mm, preferably 1.10-1.20mm, and 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 is such that after passing through the third specified power P3, it irradiates an area within 20 degrees of the center of the macula of the retina.

The power between the second specified power P2 and the first specified power P1 changes gradually in a specified manner, and the gradual change of the power satisfies the following formula:

P(r)=P0+f _A2 (r-r2)+P _A2

Among them, r is the distance to the optical center of the lens, f _A2 is the first-order polynomial, second-order polynomial or N-degree polynomial of r, r2 is the distance from the second specified power P2 to the optical center of the lens, P0 is the prescription power, P _A2 is the second additional power.

As shown in FIG. 6 , the power between the first specified power P1 and the third specified power P3 changes gradually in a specified manner, and the gradual change of the power satisfies the following formula:

P(r)=P0+f _A1 (r-r1)+P _A1

where r is the distance from the optical center of the lens, f _A1 is the first-order polynomial, second-order polynomial, or Nth-degree polynomial of r, r1 is the distance from the first specified power to the optical center of the lens, P0 is the prescription power, and P _A1 is the The first additional power; and the power between the third specified power P3 and the prescribed power P0 is gradually changed in a specified manner, and the power satisfies the following formula:

P(r)=P0+f _A3 (r-r3)+P _A3

Among them, r is the distance to the optical center of the lens, f _A3 is the first-order polynomial, second-order polynomial or Nth-degree polynomial of r, r3 is the distance from the third specified power P3 to the optical center of the lens, P0 is the prescription power, P _A3 is the third additional power.

Therefore, in the embodiment of the present invention, by additionally setting the second specified power P2 and the third specified power P3 on the lens, the lens can generate myopia and defocus in a wider range beside the center of the retina, thereby providing stable myopia Control effect. It should also be emphasized that this embodiment only takes three light-adding positions as an example, but is not limited to the above three light-adding positions, and the lens can have different light-adding settings according to actual use and performance requirements.

The technical solution provided by the present invention is to add light at a specific position of the lens, that is, to set a specified power at a specific position, and after the narrow beam passing through the specific position passes through the center of the pupil, it will be irradiated at 10 degrees to 20 degrees next to the center of the retinal macular. area within the range. The myopia and defocus in this area has better control effect of myopia, so it should produce as much myopia and defocus as possible within 10 to 20 degrees, of which 15 degrees is the most important. In order to demonstrate the advantages of the lens of the present invention, the inventors used the following simulation method to compare the prior art lens with the lens of the present invention.

Simulation method

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)), in OpticStudio Zemax Liou&Brennan model eye is established in , and according to the optical power of P(r)=P0+SA*r^2, the corresponding optical surface is added to simulate the corresponding contact eye in front of the simulated eye.

Calculate the zernike function coefficient of different field of view in OpticStudio Zemax, Zernike vsField, obtain the parameters of z4, z11, z22, z6, z12, z24 and the diameter of the exit pupil, and substitute them into the following formulas to calculate different fields of view. defocus diopter.

result

The prior art lenses are usually designed for CD, such as the central setting of -3D prescription power, with SA=0.33D/mm, according to P(r)=P0+SA*r^2, add light 0.24D at 0.85mm, Add light 0.33*3^2=3D at 3mm. FIG. 7 is a graph showing the change of the conventional CD lens after setting the specified power. As shown in Figure 7, it can be seen from the calculation that only -0.24D myopia defocus is generated in the 15-degree area next to the center of the retinal macula, therefore, a better myopia control effect cannot be achieved.

In the ophthalmic lens in the embodiment of the present invention, the prescription power -3D is set around the optical zone of the lens, and the first additional power P _A1 is set at 0.85mm from the center of the ophthalmic lens to be 2.76D, so the first specified power P1 is obtained as -0.24D, then gradually add power to the center of the ophthalmic lens at the prescription power to the first specified power. FIG. 8 shows a graph of the peripheral defocus diopter after setting the specified power in the ophthalmic lens provided by the present invention. As shown in FIG. 8 , within a 15-degree area next to the center of the retinal macular, a myopia defocus of -3.06D is generated. Therefore, the ophthalmic lens provided by the embodiment of the present invention has a better control effect of myopia.

Example

The lenses of the present invention were tested for retardation of myopia progression in a pilot study consisting of 5 myopic patients. The average age of the patients was 11 years, and the contact lenses used had a base arc radius of 8.6 mm and a diameter of 14.5 mm, with an optic zone radius of 3.5 mm and a plus light +2.50D at 0.85 mm. At the beginning of the experiment, the average spherical power of the lenses used was -2.60D. The patient wears the lens of the present invention every day, checks every 3 months and replaces the new lens. After 12 months of wearing, the average spherical lens of the lens is -2.90D, and the progression of myopia is -0.30D. .

According to the records in 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 BLINKRandomized Clinical Trial. JAMA. 2020; 324(6): 571-580), Under the same monitoring conditions, in the control of myopia with different additions of CD lens design, the average myopia progression in the +2.50D group was -0.60D per year, the +1.5D group was on average -0.89D per year, and the average of the control group monofocal contact lenses was -0.89D per year. -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.

It will be understood by those skilled in the art that the invention described herein may be subject to changes and modifications in addition to those specifically described. The present invention is not limited to the specific constructions described and illustrated herein, but includes all such changes and modifications that fall within its spirit and scope. Those skilled in the art may make any combination of any two or more of the features, structures or parts presented in this specification, individually or collectively, without departing from the spirit and scope of the invention.

Claims (13)

1. an ophthalmic lens with a key light-adding position, characterized in that, the optical zone is sequentially provided with a first specified power P1 and a prescription power P0 along its center to the edge direction; Wherein, the first specified power P1 is the prescription power P0 plus the first additional power P _A1 , and the distance r1 between the first specified power P1 and the optical center of the lens is 0.75-0.95mm, The distance r0 of the prescription power P0 from the optical center of the lens is 2.5-3.5mm, The power between r1 and r0 changes progressively in a specified manner. 2 . The ophthalmic lens according to claim 1 , wherein the incident light beam parallel to the optical axis of the ophthalmic lens passes through the first specified power P1 and irradiates an area within 15 degrees of the center of the retinal macular. 3 . 3. The ophthalmic lens according to claim 1 or 2, wherein the first additional power P _A1 is selected from +1.00D to +6.00D, preferably +1.20D to +5.00D, more preferably +1.50D to +4.00D, most preferably +2.00 to +3.00D. 4. The ophthalmic lens according to any one of claims 1 to 3, wherein in the region between r0 and the edge of the optical zone, the power of the lens is constant at the prescription power P0. 5. The ophthalmic lens according to any one of claims 1 to 4, wherein a second specified power P2 is further provided between the center of the optical zone and the first specified power, and the second specified power P2 is The prescribed power P0 is added to the second additional power P _A2 , and the distance r2 of the second specified power P2 from the optical center of the lens is 0.47-0.67 mm; the power between r2 and r1 changes gradually in a specified manner. 6 . The ophthalmic lens according to claim 5 , wherein the incident light beam parallel to the optical axis of the ophthalmic lens passes through the second specified power P2 and irradiates an area within 10 degrees of the center of the retinal macular. 7 . 7. The ophthalmic lens according to claim 5, wherein the second add power P _A2 is the same as or different from the first add power P _A1 and is selected from +1.00D to +8.00D, preferably +1.20D to +7.00D, more preferably +1.50D to +6.00D, most preferably +2.00 to +4.00D. 8. The ophthalmic lens according to any one of claims 1 to 7, wherein a third specified power P3 is further provided between the first specified power P1 and the prescribed power P0, and the third specified power is P3 is the prescription power P0 plus the third additional power P _A3 , and the distance r3 of the third specified power P3 from the optical center of the lens is 1.05-1.25mm, and the power between r1 and r3 and between r3 and r0 is 1.05-1.25mm. The designation method changes incrementally. 9 . The ophthalmic lens according to claim 8 , wherein the incident light beam parallel to the optical axis of the ophthalmic lens passes through the third specified power P3 and irradiates an area within 20 degrees of the center of the retinal macular. 10 . 10 . The ophthalmic lens of claim 8 , wherein the third additional power P _A3 is greater than 0 and smaller than the first additional power P _A1 . 11 . 11. The ophthalmic lens of any preceding claim, wherein the optical center of the lens has a power selected from P0 to P0+8.00D. 12. The ophthalmic lens of any preceding claim, wherein the ophthalmic lens is a contact lens, a scleral lens, or a corneal inlay. 13. The ophthalmic lens of any preceding claim, further comprising one or more stabilizing features.

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