CN115220244A

CN115220244A - Ophthalmic lens with critical addition location

Info

Publication number: CN115220244A
Application number: CN202110432435.3A
Authority: CN
Inventors: 苏海·沙伊尔; 肖真; 蓝卫忠
Original assignee: Zhuhai Fitland Medical Technology Co ltd; Fitland Ltd
Current assignee: Zhuhai Fitland Medical Technology Co ltd; Fitland Ltd
Priority date: 2021-04-21
Filing date: 2021-04-21
Publication date: 2022-10-21

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 lens with critical addition location

Technical Field

The present disclosure relates to ophthalmic lenses, and more particularly, to ophthalmic lenses with critical addition locations for preventing the onset or retarding the progression of myopia.

Background

The human eye has a complex set of optical systems comprising: cornea, anterior chamber (aqueous humor), iris (pupil), vitreous, retina, etc. Human eyes can form an inverted image on retinas through refractive imaging of three interfaces of air-cornea, aqueous humor-crystalline lens and crystalline lens-vitreous body, wherein ciliary muscles play a role in focusing by changing the curvature of the crystalline lens. In order to create a sharp image perception, the optical system of the eye should produce an image focused on the retina. Optical disorders are commonly known when the on-axis image is focused in front of, or behind, the fovea of the retina causing blurred vision for a variety of reasons: myopia or hyperopia. The eye may also have other vision defects such as astigmatism or higher order optical aberrations such as spherical aberration, coma, etc.

Of the various visual defects, myopia has increased worldwide, particularly in adolescents, with an estimated global myopia population reaching about 50 billion by 2050. Myopia is likely to progress to high myopia, which is closely associated with the risk of developing various ophthalmic diseases, such as retinal detachment, cataracts, macular hemorrhage and macular degeneration, glaucoma, and the like. The 0-12 years old is the sensitive stage of visual development. At birth, the human eye is generally hyperopic, i.e. the axial length of the eyeball is too short in relation to its optical power. The axis of the eye grows with age, and its elongation process is controlled by a feedback mechanism commonly referred to as an emmetropization process. During emmetropization, the axis of the eye grows as controlled by the position of the focal point relative to the retina, but fails to grow shorter. Thus, it has been proposed that the progression of myopic refractive error can be controlled by positioning the focus in front of the retina.

In general, the best focus plane formed by the rays incident at different angles of view is called the Petzval plane. When the Petzval surface is in front of the retina, it is called myopic defocus, and vice versa, hyperopic defocus. The Petzval surface generated by the conventional monofocal lens is spherical, and the eyeball is generally ellipsoidal, so that the peripheral Petzval surface is positioned behind the retina to form hypermetropia defocusing and promote the progression of myopic ametropia. The mainstream design concept of the current myopia prevention and control lens is central-for-distance (CD), i.e. the central region of the lens has a prescribed power for distance vision correction, and the periphery is a region with positive add power for forming myopic defocus in front of the retina, thereby achieving the effect of inhibiting or slowing down the growth of the axis of the eye.

For example, CN110068937A discloses an ophthalmic lens having an optically non-coaxial zone for myopia control, the lens comprising a central zone having a negative power for myopic vision correction, at least one treatment zone and a transition zone therebetween, the treatment zone minimizing the creation of a focal point behind the retinal plane of the wearer's eye by means of a positive add power.

CN207867163U discloses a peripheral defocus myopia control lens formed aspherically, comprising a central optical zone for forming a sharp image on the retina and a peripheral optical zone surrounding the central optical zone, having an aspherical outer surface and imaging passing light rays at a peripheral defocus image zone location in front of the retina of the eyeball.

CN104136964B discloses a multifocal optical lens useful in the treatment of presbyopia or myopia progression, comprising a central optic zone and a peripheral optic zone producing different focal points, providing a central refractive power for distance vision and a peripheral refractive power for near vision, respectively.

L. smith III et al (centre-dependent effects on evaluating depth on accommodation in area of once monkey, vision Research,17 (3): 32-40, 2020) employ bifocal lenses (concentric annular zones of diopter centered at zero diopter and surrounded by alternating zones of +3D and zero diopter) to image objects above a certain Eccentricity only through the bifocal peripheral zone by controlling the diameter of the central zero diopter zone, thereby finding that a competing myopic defocus signal applied near the fovea of the center has a stronger and more consistent effect in slowing axial growth of the eye axis than a myopic defocus applied at greater Eccentricity.

However, the myopia prevention and control effect of the existing lens is not satisfactory. Thus, there is a need for new lens designs that have the effect of preventing the onset or slowing the progression of myopia.

Disclosure of Invention

The invention provides an ophthalmic lens, wherein a first appointed focal power P1 and a prescription focal power P0 are sequentially arranged in an optical area along the direction from the center to the edge of the optical area; wherein the first appointed focal power P1 is the focal power P0 plus the first addition focal power P _A1 And the distance r1 of the first specified focal power P1 from the optical center of the lens is 0.75-0.95mm, the distance r0 of the prescribed focal power P0 from the optical center of the lens is 2.5-3.5mm, and the focal powers between r1 and r0 are gradually changed in a specified manner.

In some embodiments, an incident beam of light parallel to the optical axis of the ophthalmic lens passes through a first prescribed power P1 and illuminates a region within 15 degrees beside the macula of the retina.

In some embodiments, the first add power P _A1 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 optic zone periphery.

In some embodiments, a second prescribed power P2 is also provided between the center of the optical zone and the first prescribed power, the second prescribed power P2 being the prescribed power P0 plus a second add power P _A2 And the distance r2 of the second designated focus P2 from the optical center of the lens is 0.47-0.67mm; the power between r2 and r1 varies progressively in a prescribed manner.

In some embodiments, an incident beam of light parallel to the optical axis of the ophthalmic lens passes through a second prescribed power P2 and illuminates a region within 10 degrees beside the macula of the retina.

In some embodiments, the second add power P _A2 And a first add power P _A1 Identical or different and 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 specific power P3 is further provided between the first specific power P1 and the prescribed power P0, the third specific power P3 being the prescribed power P0 plus a third addition power P _A3 And the third prescribed power P3 is a distance r3 from the optical center of the lens of 1.05-1.25mm, r1 to r3, and powers between r3 and r0 are progressively varied in a prescribed manner.

In some embodiments, an incident beam of light parallel to the optical axis of the ophthalmic lens passes through a third prescribed power P3 and illuminates a region 20 degrees lateral to the macula of the retina.

In some embodiments, the third add power P _A3 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 comprises one or more stabilization features.

The technical scheme provided by the invention adopts the design of central-for-near vision (CN), the prescribed focal power is arranged at the periphery of the optical area of the lens, and the light adding treatment is also carried out at a specific position, so that the situation that the peripheral Petzval surface is positioned behind the retina is avoided on one hand, and the myopia and the defocus of the area within 20 degrees beside the center of the macula lutea of the retina are ensured on the other hand. The two mechanisms work together to provide the lenses of the invention with a surprising myopia control effect.

Drawings

FIG. 1 is a schematic view of a prior art lens for preventing the onset and controlling the progression of myopia;

FIG. 2 shows a schematic diagram of the operation of the lens of the invention with a first given power P1;

FIG. 3 shows a graph of the power of the lens as a function of distance at a first given power P1;

FIG. 4 shows another plot of power of the lens as a function of distance at a first given power P1;

FIG. 5 shows yet another plot of power of the lens as a function of distance at a first given power P1;

FIG. 6 shows a further graph of the power of the lens as a function of distance for a first prescribed power P1, a second prescribed power P2 and a third prescribed power P3;

FIG. 7 shows a peripheral defocus plot of a prior art CD lens after setting a given power;

figure 8 shows a peripheral through-focus diopter plot after setting a specified power in an ophthalmic lens provided using the present invention.

Detailed Description

Exemplary embodiments of the present invention will be described below with reference to the accompanying drawings. Unless defined otherwise, 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.

Fig. 1 shows a schematic view of an optical lens disclosed in CN207867163U as a representative example of a prior art design assuming peripheral defocus. Wherein the optical lens 1 comprises a central optical zone 11 and a peripheral optical zone 12, the peripheral optical zone having a lower negative power than the central optical zone. Light rays passing through the central optical zone form a focal point 211 on the retina, thereby forming a sharp image, while light rays passing through the peripheral optical zone form a focal point 212 in front of the retina.

Figure 2 shows a schematic diagram of the operation of the lens of the invention when set to a first given power P1. As shown in fig. 2, a first designated focal power P1 and a prescribed focal power P0 are sequentially arranged in the optical zone of the lens along the direction from the center to the periphery; the first specific focal power P1 is a 'key addition position' of the lens, the focal power of the position is the specific focal power, and the focal power change form from the position to the prescription focal power position is a specific form. In the case of the present invention, the prescribed power is 0 or a negative power that provides the best corrected vision for myopes. The power is specifically determined by the doctor or optometrist. In addition, in the optical zone of the lenses of the invention, the power is distributed symmetrically about the center of the optical zone, and the figures show only one side by way of example.

Specifically, the first prescribed power P1 is the prescribed power P0 plus the first addition power P _A1 . Wherein the first addition power P _A1 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, and the like. And the first given power P1 is at a distance r1 from the optical center of the lens of 0.75-0.95mm, preferably 0.80-0.90mm, still preferably 0.85mm, e.g. 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, an incident beam parallel to the optical axis of the lens, after a first prescribed power, illuminates a prescribed area near the center of the macula lutea. In the context of the present invention, its angle α from the optical axis is referred to as the eccentricity, or the paramacular angle. An incident beam of light parallel to the optical axis of the lens, after a first prescribed power, strikes a region within 15 degrees (i.e., α =15 °) near the center of the macula of the retina. The myopia out-of-focus in the 20 degree range near the center of the macula lutea has more excellent myopia control effect, wherein the myopia out-of-focus produces the strongest myopia control effect at the 15 degree position.

There is no particular limitation on the power change between the center of the optical zone to the first prescribed power P1. FIG. 3 shows a graph of the power of the lens as a function of distance at a first specified power P1, wherein the power change from the first specified power P1 to the center of the optical zone is a natural continuation of the power change from the prescription power to the first specified power; FIG. 4 shows another graph of the power of the lens as a function of distance at a first given power P1; fig. 5 shows a further graph of the power of the lens as a function of distance when the first given power P1 is set.

As shown in fig. 3 to 5, the prescribed power P0 is at a distance r0 of 2.5-3.5mm from the optical center of the lens, preferably at a distance r0 of 2.75mm, and the power between the first prescribed power P1 and the prescribed power P0 is progressively changed in a prescribed manner, the power progression change satisfying the following formula:

P(r)＝P0+f _A1 (r-r1)+P _A1

where r is the distance to the optical center of the lens and f _A1 Is a first, second or nth order polynomial of r, r1 is the distance of the first prescribed power P1 to the optical center of the lens, P0 is the prescription power, P _A1 Is a first add power; satisfies the condition that P (r 1) = P0+ P _A1 。

As an example, with 0.85mm from the contact lens center as the key addition position (i.e., r1=0.85 mm), and P0= -3d, P _A1 = +2.5D, the power calculation between the first prescribed power P1 to the square power P0 may be any of the following:

1 time curve

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

Curve of degree 2

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)

3 degree curve

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

Or alternatively

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

In embodiments of the invention, the power of the lens is constant at the prescription power in the region between the prescription power and the optic zone periphery. The ophthalmic lens of the invention may be a contact lens, a scleral lens, or a corneal inlay. Among the various types of ophthalmic lenses, the optical zone diameter of the lens is generally 7.0 to 12.0mm. Those skilled in the art will appreciate that the size of the optic zone of an ophthalmic lens depends on the height of the palpebral fissure and the pupil diameter of the wearer, and thus, those skilled in the art can select an appropriate optic zone size as desired.

As shown in fig. 3 to 5, the power between the optical center of the lens and the first specific 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 any value between P0 and P0+8.00D, and the power between the optical center of the lens and the first specific power can be changed in a gradual change manner, a step manner or a constant value manner, preferably in a gradual change manner (as shown in fig. 3 to 5), or constantly equal to the first specific power. Because the abrupt change in optical power makes processing difficult, it may result in an abrupt change in surface morphology. Sudden changes in power or lens surface morphology produce scattering or diffraction in the abrupt regions, but scattering can cause diffuse light to strike the macular area, creating halos, flare, and reducing contrast sensitivity.

In the embodiment of the present invention, there may be more than one "key add position" on the lens, and more add positions may be set on the lens, and the add amount of the add position is set, and three add positions are taken as an example, that is, a second specified focal power and a third specified focal power are added on the lens.

As shown in FIG. 6, a second prescribed power P2 can also be provided between the center of the optical zone and the first prescribed power, the second prescribed power P2 being the prescribed power P0 plus a second add power P _A2 . Wherein the second addition power P _A2 And a first add power P _A1 Identical or different, 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, and the like. And the distance r2 of the second prescribed focus P2 from the optical center of the lens is 0.47-0.67mm, preferably 0.50-0.64mm, still preferably 0.57mm, e.g. 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. An incident light beam parallel to the optical axis of the ophthalmic lens irradiates a region within 10 degrees near the center of the macula lutea of the retina after passing through a second prescribed power P2. Similarly, there is no particular limitation on the power change between the center of the optical zone to the second prescribed focus P2. In the preferred aspectsIn this case, the power between the center of the optical zone and r2 is constant at a second prescribed power P2.

A third appointed focal power P3 can be arranged between the first appointed focal power P1 and the prescription focal power P0, and the third appointed focal power P3 is the addition of the prescription focal power P0 and the third addition focal power P _A3 . Wherein the third addition power P _A3 Greater than 0 and less than the first add power P _A1 . And the distance r3 of the third given power P3 from the optical center of the lens is 1.05-1.25mm, preferably 1.10-1.20mm, still preferably 1.15mm, e.g. 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. An incident beam of light parallel to the optical axis of the ophthalmic lens causes illumination of a region within 20 degrees lateral to the macula of the retina after a third prescribed power P3.

The focal power between the second specific focal power P2 and the first specific focal power P1 is gradually changed in a specific manner, and the gradual change of the focal power meets the following formula:

P(r)＝P0+f _A2 (r-r2)+P _A2

where r is the distance to the optical center of the lens and f _A2 A first, second or N-th order polynomial of r, r2 is the distance of the second prescribed power P2 to the optical center of the lens, P0 is the prescription power, P _A2 Is the second add power.

As shown in fig. 6, the power between the first prescribed power P1 and the third prescribed power P3 is gradually changed in a prescribed manner, and the power gradual change 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 and f _A1 A first, second or N-th order polynomial of r, r1 is the distance from the first prescribed power to the optical center of the lens, P0 is the prescription power, P _A1 Is a first add power; and the power between the third prescribed power P3 to the prescribed power P0 varies progressively in a prescribed manner, the power satisfying the following formula:

P(r)＝P0+f _A3 (r-r3)+P _A3

where r is the distance to the optical center of the lens and f _A3 Is a first, second or N-th order polynomial of r, r3 is the distance of the third prescribed power P3 to the optical center of the lens, P0 is the prescription power, P _A3 Is the third add power.

Therefore, in the embodiment of the invention, the second specific focal power P2 and the third specific focal power P3 are additionally arranged on the lens, so that the lens generates myopic defocus in a wider range beside the center of the macula lutea, and a stable myopia control effect is provided. It should be noted that, in the present embodiment, only three light-applying positions are taken as an example, but the present invention is not limited to the above three light-applying positions, and the lens may be set differently according to actual use and performance requirements.

According to the technical scheme provided by the invention, the light adding treatment is carried out at the specific position of the lens, namely, the specified focal power is set at the specific position, and the narrow light beam passing through the specific position passes through the center of the pupil and then irradiates the area within the range of 10-20 degrees beside the center of the macula lutea. Myopic defocus in this region has a better myopia control effect and so as much myopic defocus as possible should be produced at 10 to 20 degrees, with 15 degrees being the most important. To demonstrate the advantages of the lenses of the invention, the inventors compared prior art lenses and lenses of the invention using the following simulation method.

Simulation method

A Liou & Brennan model eye was created in an Optic studio Zemax as described by Liou et al (Hwey-Lan Liou and Noel A. Brennan, "adaptive acurate, fine model eye for optical modeling," J.Opt.Soc.Am.A. 14,1684-1695 (1997)), and the corresponding contact eye was simulated with the addition of the corresponding optical curve before the simulated eye according to the optical power of P (r) = P0+ SA r ^ 2.

Zernike function coefficients of different Field angles, zernike vs fields, are calculated in an OpticStaudio Zemax, parameters of z4, z11, z22, z6, z12 and z24 and exit pupil diameters are obtained and are substituted into the following formula, and defocusing diopters at different Field angles are calculated.

As a result, the

Prior art lenses are typically designed for CD, such as a central set-3D prescription power, with SA =0.33D/mm, in terms of P (r) = P0+ SA ^ r ^2, 0.24D at 0.85mm, 0.33 x 3^2=3D at 3 mm. Fig. 7 shows a graph of the change after setting a given power in a conventional CD lens. As shown in fig. 7, it can be found by calculation that only-0.24D myopic defocus is generated in the 15 degree area beside the center of the macula lutea, and therefore, a better myopia control effect cannot be achieved.

In an ophthalmic lens of an embodiment of the invention, the prescription power-3D is provided at the periphery of the optic zone of the lens and the first add power P is provided at a distance of 0.85mm from the center of the ophthalmic lens _A1 Is 2.76D, thus obtaining a first prescribed power P1 of-0.24D, and then gradually adding light to the center of the ophthalmic lens at the prescribed power to the first prescribed power. Figure 8 shows a peripheral through-focus diopter plot after a given power setting in an ophthalmic lens provided using the present invention. As shown in FIG. 8, a myopic defocus of-3.06D is generated in a 15 degree region near the macula lutea, and thus the ophthalmic lens provided by the embodiment of the present invention has a better myopia control effect.

Examples

The retarding effect of the lenses of the invention on the progression of myopia was tested in a pilot study group containing 5 myopes. The average age of the patient was 11 years, and a contact lens was used having a base curve radius of 8.6mm and a diameter of 14.5mm, with an optic zone radius of 3.5mm plus +2.50D at 0.85 mm. At the start of the experiment, the mean spherical power of the lenses used was-2.60D. The patient wears the lenses of the invention daily, every 3 months, with an examination and replacement of new lenses, and 12 months after wear, the lenses have a mean sphere of-2.90D and a progression of-0.30D of myopic power. .

According to The records of The literature (Wallian JJ et al. Effect of High added Power, medium added Power, or Single-Vision contacts Lenses on Myopia Progression in Children: the BLINK Randomized Clinical Trial. JAMA.2020;324 (6): 571-580), the same monitoring conditions, different Add powers of CD lens designs, in The control of Myopia, myopia progresses in +2.50D groups at an average of-0.60D per year, myopia progresses in +1.5D groups at an average of-0.89D per year, and monofocal Contact Lenses in control groups at an average of-1.05D per year. Therefore, the correction mode provided by the embodiment of the invention is superior to the existing CD lens correction mode.

Those skilled in the art will appreciate that the invention described herein is susceptible to variations and modifications other than those specifically described. The present invention is not limited to the particular constructions described and illustrated herein, but encompasses all such variations and modifications as fall within the spirit and scope thereof. Any two or more of the features, structures, or parts presented in this specification, individually or collectively, may be combined in any combination by those skilled in the art without departing from the spirit and scope of the present invention.

Claims

1. An ophthalmic lens with a key addition position is characterized in that a first appointed focal power P1 and a prescription focal power P0 are sequentially arranged in an optical area 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 first prescribed power P1 is at a distance r1 of 0.75-0.95mm from the optical center of the lens,

the distance r0 between the prescribed focal power P0 and the optical center of the lens is 2.5-3.5mm,

the power between r1 and r0 varies progressively in a prescribed manner.

2. An ophthalmic lens according to claim 1, characterized in that an incident light beam parallel to the optical axis of the ophthalmic lens illuminates a zone within 15 degrees beside the macula lutea of the retina after a first prescribed power P1.

3. An ophthalmic lens according to claim 1 or 2, characterized in that 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.

4. An ophthalmic lens according to any one of claims 1 to 3, characterized in that the power of the lens is constant at the prescription power P0 in the region between r0 and the periphery of the optical zone.

5. An ophthalmic lens according to any one of claims 1 to 4, wherein a second prescribed power P2 is provided between the center of the optical zone and the first prescribed power, the second prescribed power P2 being the prescribed power P0 plus a second add power P _A2 And the distance r2 of the second designated focus P2 from the optical center of the lens is 0.47-0.67mm; the power between r2 and r1 varies progressively in a prescribed manner.

6. An ophthalmic lens according to claim 5, characterized in that an incident light beam parallel to the optical axis of the ophthalmic lens illuminates a zone within 10 degrees beside the macular center after a second prescribed power P2.

7. An ophthalmic lens according to claim 5, characterized in that the second additional power P _A2 And a first add power P _A1 Identical or different and 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. An ophthalmic lens according to any one of claims 1 to 7, characterized in that a third specific power P3 is provided between the first specific power P1 and the prescribed power P0, the third specific power P3 being the prescribed power P0 plus a third addition power P _A3 And a third prescribed power P3 is a distance r3 from the optical center of the lens of 1.05-1.25mm, r1 to r3, and powers between r3 and r0 vary progressively in a prescribed manner.

9. An ophthalmic lens according to claim 8, characterized in that an incident light beam parallel to the optical axis of the ophthalmic lens illuminates a zone within 20 degrees of the paramacular center after passing through a third prescribed power P3.

10. An ophthalmic lens according to claim 8, characterized in that the third additional power P _A3 Greater than 0 and less than the first add power P _A1 。

11. An ophthalmic lens according to any one of the preceding claims, characterized in that the power of the optical center of the lens is selected from P0 to P0+8.00D.

12. An ophthalmic lens according to any one of the preceding claims, characterized in that the ophthalmic lens is a contact lens, a scleral lens, or a corneal inlay.

13. An ophthalmic lens according to any one of the preceding claims, characterized in that it further comprises one or more stabilization features.