Enhanced ophthalmic lens with singular aspheric axicon refractive optics

Abstract

The present invention relates to a novel ophthalmic lens designed to extend the depth of focus of a patient using the lens. The lens includes an optic having a front surface, a back surface, and an optical axis. At least one of the front surface and the back surface includes a first region extending from the optical axis to a first radial boundary and a second region extending from the first radial boundary to an edge of the optic. The first region includes a surface having singular aspheric conic lens features, and the second region includes a surface having even aspheric features. If the ophthalmic lens is intraocular, a haptic will be connected to the optic to secure the lens in place after insertion into the capsular bag of a human eye.

Description

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS

[0002] This application claims priority to U.S. Provisional Patent Application No. 63 / 385,797, filed on December 2, 2022. The entire disclosure of the prior application is considered part of the disclosure of the accompanying application and is incorporated herein by reference. Technical Field

[0003] The present disclosure relates generally to ophthalmic lenses and, more particularly, to ophthalmic lenses having optics comprised of two regions of extended depth of focus. Background Art

[0004] A common eye disease among older people is cataracts. Cataracts are cloudy areas in the lens of the eye that cause decreased vision. Cataracts usually develop slowly and can affect one or both eyes, often making it difficult to complete daily tasks such as driving, reading or recognizing faces. If left untreated, cataracts can lead to blindness. A common treatment is to remove the natural lens of the eye (called the crystalline lens) and replace it with an artificial lens called an intraocular lens (IOL). IOLs can be designed to provide good vision with a single focus or with multiple focuses. The former are called monofocal IOLs and usually use an aspheric surface. In contrast, the latter are called multifocal IOLs and use a diffractive surface.

[0005] Multifocal IOLs with multiple focal points are often preferred over monofocal IOLs because such lenses generally do not require glasses. However, multifocal lenses are more expensive than monofocal lenses due to their diffractive design, and patients using multifocal lenses are many times less satisfied with their visual experience than patients using monofocal lenses. Therefore, many IOL monofocal designs attempt to improve the monofocality of the lens by modifying its aspheric surface to increase the depth of focus at its single focus.

[0006] U.S. Publication 20200121448, entitled “Intraocular Lens with Extended Depth of Focus” by Myoung Taek Choi et al., discloses an IOL comprising an optic zone and a modulating surface profile formed in the optic zone, the modulating surface profile being configured to focus incident light at a plurality of focal points, wherein the modulating surface profile is combined with a substrate surface profile of the optic zone. The modulating surface may have a profile that is sinusoidal, triangular, or some form thereof, the purpose of which is to extend the depth of focus. Another example is U.S. Patent 11083566, entitled “Ophthalmic Lens with Extended Depth of Focus” by Xin Hong et al. Here, Hong discloses an ophthalmic lens comprising an optical device having a front surface, a rear surface, and an optical axis. At least one of the front surface and the rear surface comprises a first region extending from the optical axis to a first radial boundary and a second region extending from the first radial boundary to an edge of the optical device. The first region comprises an inner region and an outer region separated by a phase shift feature, the phase shift comprising ridges extending outward from the inner region and the outer region. The optical combination of the inner region of the first and second regions, the phase shifting features, and the outer region extends the depth of focus of the lens. Summary of the invention

[0007] Disclosed herein is an ophthalmic lens, typically an IOL, wherein in certain embodiments, the optic has a front surface, a back surface, and an optical axis. At least one of the front surface and the back surface includes a first region extending from the optical axis to a first radial boundary and a second region extending from the first radial boundary to an edge of the optic. The first region has a surface consisting of an even-order aspheric surface modified with an odd asphere axicon (OAA), while the second region is a normal conic surface or an even-order aspheric surface. By modifying the parameters of the OAA, an unlimited number of embodiments can be created, some of which are disclosed herein.

[0008] Neither this summary nor the following detailed description defines or restricts the present invention. The present invention is defined by the claims. BRIEF DESCRIPTION OF THE DRAWINGS

[0009] The present invention will be more fully understood through the detailed description and accompanying drawings. Other systems, methods, features and advantages of the present invention will become apparent to those skilled in the art upon review of the following drawings and detailed description. All such additional systems, methods, features and advantages are included within this description, are within the scope of the present invention, and are protected by the following claims, wherein:

[0010] Figure 1 shows a front view of one embodiment of an IOL with extended depth of focus according to an embodiment of the present disclosure;

[0011] Figure 2shows a surface depression of a first embodiment of the disclosed IOL;

[0012] Figure 3 The through-focus modulation transfer function (MTF) of the first embodiment at 50 cycles / mm and 100 cycles / mm (CPMM) at 3.0 mm aperture is shown;

[0013] Figure 4 The through-focus MTF of the first embodiment at 50 cycles / mm and 100 cycles / mm (CPMM) for a 5.0 mm aperture is shown;

[0014] Figure 5 Simulated through-focus retinal images of a monofocal IOL from afar to +3.0D at 0.5D intervals are shown;

[0015] Figure 6 shows simulated through-focus retinal images of the first embodiment from afar to +3.0D at intervals of 0.5D for a 3.0mm aperture;

[0016] Figure 7 shows simulated through-focus retinal images of the first embodiment of a 5.0 mm aperture from afar to +3.0D at intervals of 0.5D;

[0017] Figure 8 shows a surface concavity of a second embodiment of the disclosed IOL;

[0018] Fig. 9 The through-focus MTF of the second embodiment at 3.0 mm aperture at 50 cycles / mm and 100 cycles / mm (CPMM) is shown;

[0019] Fig.10 The through-focus MTF of the second embodiment at 50 cycles / mm and 100 cycles / mm (CPMM) for an aperture of 5.0 mm is shown;

[0020] Fig.11 shows simulated through-focus retinal images of the second embodiment from afar to +3.0D at intervals of 0.5D for a 3.0mm aperture;

[0021] Fig.12 shows surface concavity of a third embodiment of the disclosed IOL;

[0022] Fig.13 The through-focus MTF of the third embodiment at 50 cycles / mm and 100 cycles / mm (CPMM) at 3.0 mm aperture is shown;

[0023] Fig.14The through-focus MTF of the third embodiment at 50 cycles / mm and 100 cycles / mm (CPMM) at 5.0 mm aperture is shown;

[0024] Fig.15 shows simulated through-focus retinal images of the third embodiment from afar to +3.0D at an aperture of 3.0 mm at intervals of 0.5D;

[0025] Fig.16 shows surface concavity of a fourth embodiment of the disclosed IOL;

[0026] Fig.17 shows the through-focus MTF of the fourth embodiment at 3.0 mm aperture at 50 cycles / mm and 100 cycles / mm (CPMM);

[0027] Fig.18 The through-focus MTF of the fourth embodiment at 50 cycles / mm and 100 cycles / mm (CPMM) at an aperture of 5.0 mm is shown;

[0028] Fig.19 Simulated through-focus retinal images of the fourth embodiment are shown for a 3.0 mm aperture from afar to +3.0 D at intervals of 0.5 D. DETAILED DESCRIPTION

[0029] The exemplary embodiments relate to ophthalmic devices, such as spectacles, IOLs, and contact lenses. The following description is presented to enable one of ordinary skill in the art to make and use the invention, and is provided in the context of a patent application and its requirements. Various modifications to the exemplary embodiments and general principles and features described herein will be apparent. The exemplary embodiments are described primarily in terms of specific methods and systems provided in specific implementations. However, these methods and systems will operate effectively in other implementations. For example, the methods and systems are described primarily in terms of IOLs. However, the methods and systems may also be used with contact lenses and spectacles.

[0030] In the following description, details are set forth by way of examples to facilitate discussion of the disclosed subject matter. However, it will be apparent to one of ordinary skill in the art that the disclosed embodiments are exemplary rather than exhaustive of all possible embodiments.

[0031] The present invention relates to a monofocal ophthalmic lens, such as those found in spectacles, IOLs and contact lenses and Figure 1An IOL lens 10 is shown in FIG. The lens includes two regions: a first region 12 surrounding the optical axis and a second region 14 surrounding the first region and extending to an edge 16. The first region 12 and the second region 14, which have a radius R0, are both symmetrical about the optical axis of the lens. These regions can be found on the anterior or posterior surface of the lens 10. The first region 12 has a surface depression that applies a singular aspheric cone lens wavefront to the incident light, which will extend the depth of focus of the monofocal lens. The lens 10 can correct the wearer's presbyopia under bright vision conditions at all distances, and when under intermediate vision conditions, the lens 10 will function as a monofocal lens.

[0032] For some background, with a monofocal ophthalmic lens, the wavefront emerging from the lens is essentially a sphere that converges to a single focus. A uniform aspheric surface is typically applied to the lens to correct for spherical aberrations of the eye's cornea. However, when a carefully designed OAA surface is applied to either the front or back surface of the lens, a monofocal lens can add considerable depth of focus that can correct for the wearer's presbyopia. A wearer using such a lens will be able to see clearly over a range of distances, from far to intermediate or near, depending on the prescription.

[0033] The OAA-enhanced monofocal lens has a front surface and a back surface. One of the two surfaces is a normal standard conical surface, or even an aspheric surface. The other surface is a uniform aspheric surface modified with an OAA surface in its central area. The characteristics of this OAA surface can be defined by the following equation:

[0034]

[0035] in:

[0036] z(r) is the bow height of the OAA surface;

[0037] r is the radial coordinate of the lens aperture;

[0038] A n is the nth-order coefficient in the odd aspheric polynomial;

[0039] N is the highest order of the odd aspheric polynomial series, and n=1, 3, ..., N;

[0040] R0 is the aperture radius of the odd aspheric conic lens.

[0041] N.A. n (n=1, 3, ..., N), R0 is a specification parameter of a specific design. They are defined as a range of values ​​of feasible lens performance.

[0042] OAA is designed to achieve small aperture performance. Therefore, in order to enhance photopic performance, it should be less than 1.5 mm. The value of will determine the amount and size of enhancement. The performance of the present invention is illustrated below through four embodiments of the present invention.

[0043] The first embodiment is a first-order axicon with the following parameters:

[0044] N=1

[0045] R0=1.5mm

[0046] A1=-5.5000E-03

[0047] Figure 2 The surface depression of this embodiment is shown, where the equivalent focusing force of the axicon is neutralized to zero within the aperture of the first region. Figure 3 The through-focus MTF of this embodiment at a 3.0 mm aperture is shown for specific frequencies of 50 and 100 cycles per millimeter (CPMM). Figure 4 The through-focus MTF of this embodiment at 5.0 mm aperture is shown for specific frequencies of 50 cycles / mm and 100 cycles / mm (CPMM). Figure 3 and Figure 4 In the figure, the 50CPMM MTF is shown as a solid line, while the 100CPMM MTF is shown as a dashed line. The peak at 0.0D for the 3.0mm aperture lens is wider than that for the 5.0mm aperture lens, indicating better depth of focus performance. The through-focus MTF of the 5.0mm aperture lens is close to that of the monofocal lens.

[0048] Figure 6 and Figure 7 shows a simulation of a defocused retinal image of the first embodiment, and Figure 5 A simulation of a monofocal through-focus retinal image is shown for comparison with the first and subsequent embodiments. Figure 6 shows a simulation of a defocused retinal image with a 3.0 mm aperture, while Figure 7 Simulations of through-focus retinal images with a 5.0 mm aperture are shown. All simulations were performed at 0.5D intervals from afar (i.e., 0.0D) to +3.0D. As shown, Figure 6 The simulation in supports 3.0mm aperture lens Figure 3 Improved depth of focus performance shown. In addition, Figure 7 The simulation in supports 5.0mm aperture lens Figure 4 Monofocal-like depth of focus performance is shown. As will be seen in the remaining examples, the performance of the 5.0 mm aperture lens remains monofocal-like. Therefore, although the through-focus MTF of the 5.0 mm aperture lens will be described in the remaining examples, it will not be simulated.

[0049] The second embodiment is also a first-order axicon, but exhibits a longer depth of focus than the first embodiment. The second embodiment uses the following parameters:

[0050] N=1

[0051] R0=1.5mm

[0052] A1=-9.50E-003

[0053] Figure 8 The surface depression of this embodiment is shown, where the equivalent focusing force of the axicon is neutralized to zero within the aperture of the first region. Fig. 9 The through focus MTF of this embodiment at 3.0 mm aperture is shown for specific frequencies of 50 cycles / mm and 100 cycles / mm (CPMM). Fig.10 The through-focus MTF of this embodiment at 5.0 mm aperture is shown for specific frequencies of 50 cycles / mm and 100 cycles / mm (CPMM). Fig. 9 and Fig.10 In the figure, the 50CPMM MTF is shown as a solid line, while the 100CPMM MTF is shown as a dashed line. The peak at 0.0D for the 3.0mm aperture lens is wider than that for the 5.0mm aperture lens, indicating that the depth of focus performance of the 3.0mm aperture lens is better than that of the 5.0mm aperture lens. In addition, by Fig. 9 and Figure 3 By comparison, it can be seen that the focal depth of the second embodiment is improved over that of the first embodiment. The through-focus MTF of the 5.0 mm aperture lens is close to the through-focus MTF of the monofocal lens.

[0054] Fig.11 shows a simulation of a defocused retinal image of the second embodiment, and Figure 5 A simulation of a monofocal through-focus retinal image is shown for comparison. Fig.11 The simulation of the defocused retinal image of a 3.0 mm aperture lens at 0.5 D intervals from far focus (i.e. 0.0 D) to +3.0 D is shown. As shown in the figure, Fig.11 Simulation support in Fig. 9 Improved depth of focus performance of a 3.0 mm aperture lens is shown.

[0055] The third embodiment is a seventh-order axicon, which exhibits a longer depth of focus than the second embodiment. The third embodiment uses the following parameters:

[0056] N=7

[0057] R0=1.4mm

[0058] A1=-2.7004E-03

[0059] A3=2.1205E-02

[0060] A5=-4.6919E-03

[0061] A7=5.6212E-04

[0062] Fig.12 The surface depression of this embodiment is shown, where the equivalent focusing force of the axicon is neutralized to zero within the aperture of the first region. Fig.13 The through focus MTF of this embodiment at 3.0 mm aperture is shown for specific frequencies of 50 cycles / mm and 100 cycles / mm (CPMM). Fig.14 The through-focus MTF of this embodiment at 5.0 mm aperture is shown for specific frequencies of 50 cycles / mm and 100 cycles / mm (CPMM). Fig.13 and Fig.14 In the figure, the 50CPMM MTF is shown as a solid line, while the 100CPMM MTF is shown as a dashed line. The peak at 0.0D for the 3.0mm aperture lens is wider than that for the 5.0mm aperture lens, indicating that the depth of focus performance of the 3.0mm aperture lens is better than that of the 5.0mm aperture lens. In addition, by Fig.13 and Figure 3 and Fig. 9 By comparison, it can be seen that the focal depth of the third embodiment is improved over that of the first and second embodiments. The through-focus MTF of a 5.0 mm aperture lens is close to the through-focus MTF of a monofocal lens.

[0063] Fig.15 shows a simulation of a defocused retinal image of the third embodiment, and Figure 5 A simulation of a monofocal through-focus retinal image is shown for comparison. Fig.15 The simulation of the defocused retinal image of a 3.0 mm aperture lens at 0.5 D intervals from far focus (i.e. 0.0 D) to +3.0 D is shown. As shown in the figure, Fig.15 Simulation support in Fig.13 Improved depth of focus performance of a 3.0 mm aperture lens is shown.

[0064] The fourth embodiment is a third-order aconic lens that exhibits a longer depth of focus than the third embodiment. The fourth embodiment uses the following parameters:

[0065] N=3

[0066] R0=1.4mm

[0067] A1=0

[0068] A3=4.50E-03

[0069] Fig.16The surface depression of this embodiment is shown, where the equivalent focusing force of the axicon is neutralized to zero within the aperture of the first region. Fig.17 The through focus MTF of this embodiment at 3.0 mm aperture is shown for specific frequencies of 50 cycles / mm and 100 cycles / mm (CPMM). Fig.18 The through-focus MTF of this embodiment at 5.0 mm aperture is shown for specific frequencies of 50 cycles / mm and 100 cycles / mm (CPMM). Fig.17 and Fig.18 In the figure, the 50CPMM MTF is shown as a solid line, while the 100CPMM MTF is shown as a dashed line. The peak at 0.0D for the 3.0mm aperture lens is wider than that for the 5.0mm aperture lens, indicating that the depth of focus performance of the 3.0mm aperture lens is better than that of the 5.0mm aperture lens. Fig.17 and Figure 3 , Fig. 9 and Fig.13 By comparison, it can be seen that the depth of focus of the fourth embodiment is improved over that of the previous embodiments. The through-focus MTF of the 5.0 mm aperture lens is close to the through-focus MTF of the monofocal lens.

[0070] Fig.19 shows a simulation of a defocused retinal image of the fourth embodiment, and Figure 5 A simulation of a monofocal through-focus retinal image is shown for comparison. Fig.19 A simulation of a defocused retinal image from afar (i.e., 0.0D) to +3.0D with a 3.0mm aperture lens at 0.5D intervals is shown. As shown, Fig.19 Simulation support in Fig.17 Improved depth of focus performance of a 3.0 mm aperture lens is shown.

[0071] Exemplary embodiments of the present invention have been disclosed in an illustrative manner. Therefore, the terms used throughout the text should be understood in a non-restrictive manner. Although those skilled in the art may make minor modifications to the teachings herein, it should be understood that the scope guaranteed by this patent includes all embodiments that reasonably fall within the scope of the technological advancement contributed by this article, and the scope should not be limited unless otherwise specified by the attached claims and their equivalents.

Claims

1. An ophthalmic lens comprising: An optical device, comprising: front surface; rear surface; An edge of the periphery of the optical device; and Optical axis, Wherein, at least one of the front surface and the back surface includes a first region extending from the optical axis to a radial boundary and a second region extending from the radial boundary to the edge, the first region having a surface profile of a singular aspheric conic lens, and the second region having a surface profile of an even aspheric surface.

2. The ophthalmic lens according to claim 1, wherein: The radial boundary is less than 1.5 mm from the optical axis.

3. The ophthalmic lens according to claim 1, wherein: The bow height of the optical device is: is the bow height of the optical device; r is the distance from the optical axis; is the nth-order coefficient in the singular aspheric conic lens polynomial; N is the highest order of the polynomial series of the singular aspheric conic lens, and n= 1, 3, ..., N; is the aperture radius of the first region.

4. The ophthalmic lens according to claim 1, wherein: The bow height of the first region is a first-order, third-order or seventh-order singular aspheric conic lens.

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