Ophthalmic Devices, Systems and/or Methods for Management of Ocular Conditions and/or Reducing Night Vision Disturbances

An ophthalmic lens configured to correct and/or treat at least one condition of the eye (e.g., presbyopia, myopia, hyperopia, astigmatism, binocular vision disorders and/or visual fatigue syndrome) comprising: a central optical zone; a peripheral optical zone; a base power profile; and at least one feature selected to modify the base power profile and to form one or more off-axis focal points in front of, on, and/or behind a retinal image plane and reduce a focal point energy level at one or more image planes; wherein the at least one feature may be located on a front surface and/or a back surface of at least one of the central optical zone and the peripheral optical zone.

TECHNICAL FIELD

This disclosure relates to ophthalmic devices, systems and/or methods for correcting and/or treating refractive errors and/or conditions of the eye. More particularly, this disclosure is related to ophthalmic devices, systems, and/or methods for correcting and/or treating refractive errors and/or conditions of the eye and, in some embodiments, providing low light energy levels for, e.g., further reducing, mitigating or ameliorating night vision dysphotopsias or disturbances. In some embodiments, the ophthalmic lens designs may correct and treat the refractive errors and conditions of the eye by providing an extended depth of focus along the optical axis at least in part on and/or in front of the retina of the eye. In some embodiments, the ophthalmic devices, systems and/or methods may be directed to alleviating night vision disturbances including e.g., any combination of one or more of haloes, glare and/or starbursts and/or for improving vision deficiencies associated with myopia and/or presbyopia.

BACKGROUND

The discussion of the background in this disclosure is included to explain the context of the disclosed embodiments. This is not to be taken as an admission that the material referred to was published, known, or part of the common general knowledge at the priority date of the embodiments and claims presented in this disclosure.

Ophthalmic devices incorporating simultaneous vision and/or extended depth of field optics may be used for presbyopia correction, for treating refractive errors including myopia control, for alleviating binocular vision disorders and computer vision syndrome. However, there is a need for improved efficacy with use of such devices. Furthermore, although such ophthalmic devices may split light across multiple focal points, they may cause (or at least not alleviate or improve), visual disturbances such as ghosting as well as poor night vision from dysphotopsias or disturbances such as glare, haloes, and starburst to distant light sources.

Accordingly, there is a need to improve the performance of ophthalmic devices e.g., for applications utilizing simultaneous vision and/or extended depth of field optics. The present disclosure is directed to solving these and other problems disclosed herein. The present disclosure is also directed to pointing out one or more advantages to using exemplary ophthalmic devices, systems, and methods described herein.

SUMMARY

The present disclosure is directed to overcoming and/or ameliorating one or more of the problems described herein.

The present disclosure is directed, at least in part, to ophthalmic devices and/or methods for correcting, slowing, reducing, and/or controlling the progression of myopia.

The present disclosure is directed, at least in part, to ophthalmic devices and/or methods for correcting or substantially correcting presbyopia.

The present disclosure is directed, at least in part, to ophthalmic devices, systems and/or methods to correct and/or treat refractive errors and conditions of the eye including e.g., presbyopia, myopia, astigmatism, binocular vision disorders and/or visual fatigue syndrome and providing low light energy levels for e.g., to further reduce, mitigate or prevent one or more night vision disturbances.

In some embodiments, the method, device, system or feature to correct and/or treat refractive errors and conditions of the eye may incorporate simultaneous optics or extended depth of focus optics to result in a low (e.g., substantially low or moderately low) level of light intensity at the retinal image plane.

In some embodiments, the method, device, system or feature to slow the progression of myopia may incorporate simultaneous optics or extended depth of focus optics to result in a low level of light energy (e.g., low light ray intensity) at the retinal image plane.

In some embodiments, the ophthalmic lens designs may correct and/or treat refractive errors and conditions of the eye by extending the depth of focus along the optical axis at least in part on and/or in front of the retina of the eye during use, and/or further reduce, mitigate or prevent one or more night vision disturbances.

In some embodiments, the ophthalmic lens designs may correct the refractive error(s) of the eye of a user (including e.g., any combination of one or more of a distance refractive error and/or an astigmatic refractive error and/or intermediate and/or a near refractive errors) by extending the depth of focus along the optical axis at least in part on and/or in front of the retina of the eye and/or further reduce, mitigate and/or prevent one or more night vision disturbances.

In some embodiments, the ophthalmic devices, systems and/or methods to manage and/or control refractive errors and conditions of the eye such as presbyopia, myopia, astigmatism, binocular vision disorders and visual fatigue incorporate one or more features to provide low light energy levels and thereby reduce, or mitigate, and/or prevent one or more night vision disturbances including e.g., any combination of one or more of glare, haloes and/or starburst.

In some embodiments, the ophthalmic devices, systems and/or methods incorporating simultaneous and/or extended depth of field optics incorporate an ophthalmic devices, systems and/or methods incorporating simultaneous and/or extended depth of field optics a method, system, or feature to manage one or more night vision disturbances may accompany ophthalmic devices, systems and/or methods incorporating simultaneous and/or extended depth of field optics such that the ophthalmic device, system and/or method results in a low (e.g., substantially low or moderately low) level of light energy along the optical axis of the ophthalmic lens.

In some embodiments, the ophthalmic devices, systems and/or methods incorporating simultaneous and/or extended depth of field optics incorporate a method or system or a feature to manage one or more night vision disturbances such that the ophthalmic device, system, and/or method results in a through focus retinal image quality (RIQ) with one or more independent peaks (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, and/or 10 peaks) over a vergence range of about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D±3D, ±3.1 D±3.2 D, and/or ±3.25 D), and wherein the maximum RIQ value of the independent peaks is between about 0.11 (e.g., 0.09, 0.1, 0.11, 0.12, 0.13, 0.14 or 0.15) and about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

In some embodiments, the ophthalmic devices, systems and/or methods incorporating simultaneous and/or extended depth of field optics incorporate a method or system or a feature to manage one or more night vision disturbances such that the ophthalmic device, system, and/or method results in through focus retinal image quality (RIQ) with one or more independent peaks (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, and/or 10 peaks) over a vergence range of e.g., about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D), and/or wherein the maximum RIQ value of the independent peaks is between about 0.11 (e.g., 0.09, 0.1, 0.11, 0.12, 0.13, 0.14 or 0.15) and about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48), and/or wherein the RIQ area (e.g., the area under the through focus RIQ curve bounded by the peak RIQ value and the minimum RIQ value of e.g., 0.11) of the one or more independent peaks may be about 0.16 Units*Diopters (e.g., 0.13, 0.14, 0.15, 0.16, 0.17, 0.18 or 0.19) or less.

The present disclosure is directed, at least in part, to an ophthalmic device, system and/or method to manage one or more night vision disturbances wherein the ophthalmic lens may comprise an optical zone with a base power profile and wherein the optical zone may further comprise a central and a peripheral optical zone.

In some embodiments, the ophthalmic device, system, and/or method to manage one or more night vision disturbances may further comprise a cyclical power profile in the sagittal and/or tangential directions comprising one or more cycles across one or more of the central and/or peripheral optical zones, wherein a cycle of the cyclical power profile in the sagittal and tangential directions incorporates a “m” component that may be relatively more negative in power than the base power of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power of the ophthalmic lens.

In some embodiments, the ophthalmic device, system, and/or method to manage one or more night vision disturbances may comprise a cyclical power profile comprising one or more cycles across the central and/or peripheral zone of the ophthalmic lens; wherein the peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of a cycle of the cyclical power profile in a sagittal direction may be about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, about 5 D or less, about 4 D or less, about 3D or less and/or about 2D or less.

In some embodiments, the ophthalmic device, system, and/or method to manage one or more night vision disturbances may comprise a cyclical power profile comprising one or more cycles across the central and/or peripheral zone of the ophthalmic lens; wherein the peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of a cycle of the cyclical power profile in the tangential direction may be relatively large in order to distribute light energy across a very wide range of vergences (e.g., about 600 D, about 500 D, about 400 D, about 300 D, about 250 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, and/or about 30 D or less).

In some embodiments, the ophthalmic device, system, and/or method to manage one or more night vision disturbances may be a contact lens or an intraocular lens with a central optical zone of half-chord diameter of about 5 mm, about 4 mm, about 3 mm, about 2 mm, about 1.75 mm, about 1.5 mm, about 1.25 mm, about 1.0 mm, about 0.5 mm, about 0.25 mm, and/or about 0.1 mm or less or an absent central optical zone and the ophthalmic lens incorporates a cyclical power profile across the central and/or peripheral zone of the ophthalmic lens; wherein the peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of a cycle of the cyclical power profile in the sagittal direction may be about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, 5 D, 4 D, 3D, and/or 2D or less, and wherein the peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of a cycle of the cyclical power profile in the tangential direction may be about 600 D, about 500 D, about 400 D, about 300 D, about 250 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, and/or about 30 D or less, and the frequency of the cyclical power profile in the sagittal direction in at least a portion of the central and/or peripheral optical zone may be about 0.5, 1, 1.5, 2, 5, 10, 20, 50, 100 cycles/mm.

The present disclosure is directed, at least in part, to an ophthalmic lens, system, or method to manage one or more night vision disturbances wherein the ophthalmic lens with a prescribed focal power may comprise a central optical zone of half-chord diameter of about 5 mm, about 4 mm, about 3 mm, about 2 mm, about 1.75 mm, about 1.5 mm, about 1.25 mm, about 1.0 mm, about 0.5 mm, about 0.25 mm, and/or about 0.1 mm or less or an absent central optical zone; the ophthalmic lens may incorporate a cyclical power profile in the sagittal direction in the central and/or peripheral zone with a cycle incorporating a “m” and “p” component and the peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components being about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, about 5 D, about 4 D, about 3D, and/or about 2D or less in the sagittal direction, and a cyclical power profile in the tangential direction in the central and/or peripheral zone with a cycle incorporating a “m” and “p” component and the peak-to-valley power range between the absolute powers of the “m” and “p” components being about 600 D, about 500 D, about 400 D, about 300 D, about 250 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, and/or about 30 D or less in the tangential direction; the frequency of the cyclical power profile in a sagittal direction in at least a portion of the central and/or peripheral optical zone may be about 0.5, 1, 1.5, 2, 5, 10, 20, 50, 100 cycles/mm; and wherein the ophthalmic lens may form one or more off-axis focal points in front of, on, and/or behind the retinal image plane of the eye.

The present disclosure is directed, at least in part, to an ophthalmic lens or system or method to manage one or more night vision disturbances wherein the ophthalmic lens with a prescribed focal power may comprise a central optical zone of half-chord diameter of about 5 mm, about 4 mm, about 3 mm, about 2 mm, about 1.75 mm, about 1.5 mm, about 1.25 mm, about 1.0 mm, about 0.5 mm, about 0.25 mm, and/or about 0.1 mm or less or an absent central optical zone; the ophthalmic lens may incorporate a cyclical power profile in the sagittal direction in the central and/or peripheral zone; with a cycle incorporating a “m” and “p” component and the peak-to-valley power range between the absolute powers of the “m” and “p” components being about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, about 5 D, about 4 D, about 3D, and/or about 2D or less in the sagittal direction, and a cyclical power profile in the tangential direction in the central and/or peripheral zone; with a cycle incorporating a “m” and “p” component and the peak-to-valley power range between the absolute powers of the “m” and “p” components being about 600 D, about 500 D, about 400 D, about 300 D, about 250 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, about 30 D or less in the tangential direction, the frequency of the cyclical power profile in the sagittal direction may be about 0.5, 1, 1.5, 2, 5, 10, 20, 50, 100 cycles/mm and wherein the ophthalmic lens may form one or more off-axis focal points in front of, on, and/or behind the retinal image plane of the eye and wherein at least greater than about 50% of the total enclosed energy may be distributed beyond the 35 μm, 40 μm, 45 μm, 50 μm, 55 μm, 60 μm, 65 μm, 70 μm, 75 μm, 80 μm, and/or 95 μm half chord diameter of the retinal spot diagram, and may have an average slope of less than about 0.13 units/10 μm (e.g., about 0.11 units/10 μm, 0.12 units/10 μm, 0.125 units/10 μm, 0.13 units/10 μm, 0.14 units/10 μm, and/or 0.15 units/10 μm or less) over 35 μm, 40 μm, 45 μm, 50 μm, 55 μm, 60 μm, 65 μm, 70 μm, 75 μm, 80 μm, and/or 95 μm half chord diameter of the retinal spot diagram and/or an interval slope over any 20 μm (e.g., 17 μm, 18 μm, 19 μm, 20 μm, 21 μm, 22 μm, 23 μm, or 24 μm) half chord interval across the spot diagram of not greater than about 0.13 units/10 μm (e.g., not greater than about 0.11 units/10 μm, 0.12 units/10 μm, 0.13 units/10 μm, 0.14 units/10 μm, and/or 0.15 units/10 μm).

The present disclosure is directed, at least in part, to an ophthalmic lens or system or method to manage one or more night vision disturbances wherein the ophthalmic lens with a prescribed focal power may comprise a central optical zone of half-chord diameter of about 5 mm, about 4 mm, about 3 mm, about 2 mm, about 1.75 mm, about 1.5 mm, about 1.25 mm, about 1.0 mm, about 0.5 mm, about 0.25 mm, and/or about 0.1 mm or less or an absent central optical zone; the ophthalmic lens may incorporate a cyclical power profile in the sagittal direction in the central and/or peripheral zone; with a cycle incorporating a “m” and “p” component and the peak-to-valley power range between the absolute powers of the “m” and “p” components being about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, about 5 D, about 4 D, about 3D, and/or about 2D or less in the sagittal direction, and a cyclical power profile in the tangential direction in the central and/or peripheral zone; with a cycle incorporating a “m” and “p” component and the peak-to-valley power range between the absolute powers of the “m” and “p” components being about 600 D, about 500 D, about 400 D, about 300 D, about 250 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, and/or about 30 D or less in the tangential direction, the frequency of the cyclical power profile in a sagittal direction may be about 0.5, 1, 1.5, 2, 5, 10, 20, 50, 100 cycle/mm and wherein the through focus retinal image quality (RIQ) has one or more independent peaks over a vergence range of e.g., about ±3.0 D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D), and the maximum RIQ value of any one of one or more independent peaks may be between about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48) and about 0.11 (e.g., 0.09, 0.1, 0.11, 0.12, 0.13, 0.14 or 0.15) and wherein the RIQ area (e.g., the area under the through focus RIQ curve bounded by the peak RIQ value and the minimum RIQ value of e.g., 0.11) of the one or more independent peaks may be about 0.16 Units*Diopters (e.g., 0.13, 0.14, 0.15, 0.16, 0.17, 0.18 or 0.19) or less.

The present disclosure is directed, at least in part, to an ophthalmic lens or system or method to manage one or more night vision disturbances wherein the ophthalmic lens with a prescribed focal power may comprise a central optical zone of half-chord diameter of about 5 mm, about 4 mm, about 3 mm, about 2 mm, about 1.75 mm, about 1.5 mm, about 1.25 mm, about 1.0 mm, about 0.5 mm, about 0.25 mm, and/or about 0.1 mm or less or an absent central optical zone; the ophthalmic lens may incorporate a cyclical power profile in the sagittal direction in the central and/or peripheral zone; with a cycle incorporating a “m” and “p” component and the peak-to-valley power range between the absolute powers of the “m” and “p” components being about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, about 5 D, about 4 D, about 3D, and/or about 2D or less in the sagittal direction, and a cyclical power profile in the tangential direction in the central and/or peripheral zone; with a cycle incorporating a “m” and “p” component and the peak-to-valley power range between the absolute powers of the “m” and “p” components being about 600 D, about 500 D, about 400 D, about 300 D, about 250 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, and/or about 30 D or less in the tangential direction, the frequency of the cyclical power profile in the sagittal direction in at least a portion of the central and/or peripheral optical zone being about 0.5, 1, 1.5, 2, 5, 10, 20, 50, 100 cycles/mm and wherein the light from one or more off-axis focal points may be distributed across a substantially wide range of vergences along the optical axis and in front of and/or on and/or behind the retinal image plane of the eye.

The present disclosure is directed, at least in part, to an ophthalmic lens or system or method to manage one or more night vision disturbances wherein the ophthalmic lens with a prescribed focal power may comprise a central optical zone of half-chord diameter of about 5 mm, about 4 mm, about 3 mm, about 2 mm, about 1.75 mm, about 1.5 mm, about 1.25 mm, about 1.0 mm, about 0.5 mm, about 0.25 mm, and/or about 0.1 mm or less or an absent central optical zone; the ophthalmic lens may incorporate a cyclical power profile in the sagittal direction in the central and/or peripheral zone; with a cycle incorporating a “m” and “p” component and the peak-to-valley power range between the absolute powers of the “m” and “p” components being about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, about 5 D, about 4 D, about 3D, and/or about 2D or less in the sagittal direction, and a cyclical power profile in the tangential direction in the central and/or peripheral zone; with a cycle incorporating a “m” and “p” component and the peak-to-valley power range between the absolute powers of the “m” and “p” components being about 600 D, about 500 D, about 400 D, about 300 D, about 250 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, and/or about 30 D or less in the tangential direction, the frequency of the cyclical power profile in the sagittal direction in at least a portion of the central and/or peripheral optical zone being about 0.5, 1, 1.5, 2, 5, 10, 20, 50, 100 cycle/mm and wherein the light energy from one or more narrow optical zones may be distributed across a substantially wide range of vergences along the optical axis of the eye to about +/−100 D or less (sagittal direction) in order to reduce the image quality to within a desired range and more evenly spread the light energy across the retinal image plane and may result in a through focus retinal image quality (RIQ) with one or more independent peaks over a vergence range of e.g., about ±3.0 D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D), and wherein the maximum RIQ value of the independent peaks is between about 0.11 (e.g., 0.09, 0.1, 0.11, 0.12, 0.13, 0.14 or 0.15) and about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48) and wherein the RIQ area of the one or more independent areas may be about 0.16 Units*Diopters (e.g., 0.13, 0.14, 0.15, 0.16, 0.17, 0.18 or 0.19) or less.

In some embodiments, the light passing through the off-axis focal points formed by the at least one or more narrow optical zones may intersect the optical axis and may form at least one or more (including e.g., an infinite number) on-axis focal points along the optical axis that may be distributed across a very wide range of vergences along the optical axis of the eye, in front of, on, and/or behind the retinal image plane, and may have low light energy level of the images of objects formed on the retina, and/or may have a uniform or relatively uniform light ray intensity distribution across the retinal spot diagram wherein at least greater than about 50% of the total enclosed energy may be distributed beyond the 35 μm, 40 μm, 45 μm, 50 μm, 55 μm, 60 μm, 65 μm, 70 μm, 75 μm, 80 μm, and/or 95 μm half chord diameter of the retinal spot diagram and may have an average slope of less than about 0.13 units/10 μm (e.g., about 0.11 units/10 μm, 0.12 units/10 μm, 0.125 units/10 μm, 0.13 units/10 μm, 0.14 units/10 μm, and/or 0.15 units/10 μm or less) over 35 μm, 40 μm, 45 μm, 50 μm, 55 μm, 60 μm, 65 μm, 70 μm, 75 μm, 80 μm, and/or 95 μm half chord diameter of the retinal spot diagram and/or an interval slope over any 20 μm (e.g., 17 μm, 18 μm, 19 μm, 20 μm, 21 μm, 22 μm, 23 μm, or 24 μm) half chord interval across the spot diagram of not greater than about 0.13 units/10 μm (e.g., not greater than about 0.11 units/10 μm, 0.12 units/10 μm, 0.13 units/10 μm, 0.14 units/10·m, and/or 0.15 units/10 μm).

In some embodiments, the ophthalmic lenses may include optical designs comprising at least one or more narrow optical zones incorporating cyclical power profiles in both sagittal and tangential directions and forming at least one or more off-axis focal points and at least one or more (including e.g., an infinite number) on-axis focal points along the optical axis that may have low light energy and may provide, at least in part, an extended depth of focus within a useable vergence ranges encountered by the user of the ophthalmic lens.

Other features and advantages of the subject matter described herein will be apparent from the description and drawings, and from the claims

DETAILED DESCRIPTION

The terms “about” as used in this disclosure is to be understood to be interchangeable with the term approximate or approximately.

The term “comprise” and its derivatives (e.g., comprises, comprising) as used in this disclosure is to be taken to be inclusive of features to which it refers, and is not meant to exclude the presence of additional features unless otherwise stated or implied.

The term “myopia” or “myopic” as used in this disclosure is intended to refer to an eye that is already myopic, is pre myopic, or has a refractive condition that is progressing towards myopia.

The term “presbyopia” or “presbyopic” as used in this disclosure is intended to refer to an eye that is has a diminished ability to focus on intermediate and near objects.

The term “ophthalmic lens” or “ophthalmic device” as used in this disclosure is intended to include one or more of a contact lens, or an intraocular lens, or a spectacle lens.

The term “night vision disturbances” or “night vision dysphotopsias” refer to any combination of one or more symptoms of haloes, glare and star bursts for distant objects. Methods for assessing the existence and/or reduction of night vision disturbances are well known in that art. For example, one subjective assessment of “lack of night vision disturbances” may involve measurement of “starbursts” ranked on an analog scale of 1-10 where 1=absent and 10=excessive, or on a Likert scale of good (no starburst), average (some starburst) and poor (excessive). In some embodiments, a reduction in subjective assessment of 1 unit or more may be considered to be reduction and/or minimization of night vision disturbance.

The term “low light energy levels” or “low light level” of an ophthalmic lens as used in this disclosure is intended to refer to a reduction in the amount of light at a given vergence and may be measured by the retinal image quality (RIQ) at that given vergence. Values of RIQ that may qualify as low light energy levels or low light levels may be approximately 50% or less (e.g., 0.5 or less), or about 45% or less (e.g., 0.45 or less) as compared to the RIQ of the diffraction limited lens at that given vergence and the area under the maximum peak RIQ value may be less than about 0.16 unit*Diopter where the range of vergences may be +/−3.00 D. A peak RIQ area may be defined as the area enclosed by the through focus RIQ curve beneath an independent peak (maximum peak RIQ value of between about 0.11 to about 0.45) and wherein the RIQ curve falls below about 0.11 on at least the side of the RIQ peak with the lower vergence value.

The term “focal point energy level” or “focal point energy” as used in this disclosure refers to the RIQ value at the vergence of that focal point at the image plane.

The term “line curvature” as used in this disclosure refers to a geometrically three-dimensional surface, wherein along at least one direction of that surface, a “portion” of a two-dimensional line or of a “substantially” two-dimensional line may be observed. For example, a line curvature may be created by the revolution of a “portion” of a two-dimensional line or of a “substantially” two-dimensional line on an annular zone around the central axis of an ophthalmic lens, and wherein a revolution curvature may be observed along a secondary direction for example, circumferentially.

The term “model eye” as used in this disclosure is used to determine the through focus RIQ curve, retinal spot diagram and the enclosed energy diagram and refers to a Navarro-Escudero eye modified to mimic presbyopic eyes with no accommodation and the ray-tracing routines performed in a ray tracing program (e.g., ZEMAX, FOCUS software) with the aberration terms optimized to zero.

There is a need for ophthalmic lens designs incorporating multifocal and extended depth of focus optics to improve efficacy with vision correction and/or vision treatment. A limitation of ophthalmic lens designs incorporating multifocal and extended depth of focus optics for vision correction and/or vision treatment based on the simultaneous vision optics has been the interference of out-of-focus images with the in-focus images; this may result in visual disturbances such as ghosting and/or night vision disturbances including, e.g., any combination of glare, haloes, and starbursts. For example, with ophthalmic lenses designed to provide extended depth of focus for presbyopia management, attention may be primarily targeted to providing the highest RIQ over an extended range of vergences rather than management of visual compromises, including night vision disturbances. Likewise, in vision treatments directed to slowing myopia, attention is primarily targeted to providing a higher RIQ on and/or in front of the retina than behind the retina. Typically, night vision disturbances may arise when ophthalmic lens designs incorporating multifocal and/or extended depth of focus optics provide a light distribution across the retinal image plane that may not be optimized, for example, because the intensity of defocused on-axis light rays from other image planes arriving at the retinal plane may be too high and/or concentrated and/or intense and may interfere and/or compete with the in focus light rays at the retinal plane. In addition to interfering with efficacy, they may produce visual compromises such as for example, ghosting by interfering with the in focus light energy. Also, the excessively high and/or concentrated and/or intense defocused light energy at the retinal plane may result in night vision disturbances such as glare, haloes, and/or starbursts. Consequently, some embodiments may relate to ophthalmic lens designs incorporating multifocal and extended depth of focus optics for vision correction and/or vision treatment by controlling the image quality of on-axis focal points across the through focus vergences to reduce the interference of out-of-focus images on in-focus images at the retinal image plane, and to provide a relatively even distribution of the light energy intensity with less interference from out-of-focus light rays at the retinal image plane and thereby reducing and/or mitigating night vision disturbances such as glare, haloes and starbursts. Therefore, some embodiments disclosed herein may provide ophthalmic lens designs incorporating extended depth of focus technology for vision correction and/or vision treatment and to provide desirable/optimal levels of image qualities along the optical axis and desirable/optimal light energy distribution across the retinal image plane to provide low light energy levels and reduce, mitigate and or prevent or night vision disturbances such as glare, haloes and/or starbursts.

In some embodiments, the ophthalmic lens may include an optical design formed on a lens surface, for example a front surface and/or a back surface, that may be configured with an optical zone with a base power, the optical zone comprising a small central zone that may form, for example, a focal point along the optical axis, in front of, and/or on, and/or behind the retinal image plane and may be surrounded by an annular peripheral zone comprising at least one or more narrow and/or annular conjoined optical zones that may have a cyclical power profile in a sagittal and a tangential directions that may be configured to form at least one or more off-axis focal points, for example in front of the retinal image plane, and may also result in at least one or more on-axis focal points when light rays from the off-axis focal points intersect along the optical axis, for example, in front of, and/or on, and/or behind the retinal image plane, and/or in front of, and/or, on, and/or behind the on-axis focal point formed by the central optical zone. In some embodiments, narrow and/or annular optical zones located in the central and/or peripheral zone may also be configured to provide a light energy distribution along the optical axis and may be distributed over a wide range of vergences and be of a defined low intensity. In some embodiments, the low intensity light energy distributed along the optical axis may form a light intensity across the retinal image plane that may also be uniform, for example evenly distributed over the retinal spot diagram. In some embodiments, the central zone may also be configured to provide at least one or more focal point(s) along the optical axis that may also be of low intensity, for example by sizing the central zone at a dimension small enough to reduce the light intensity of the focal point within defined value ranges. In some embodiments, the light intensity and distribution along the optical axis formed by the central zone may also form a light intensity on the retina that may also be of low intensity and/or may be uniform, for example evenly distributed over the retinal spot diagram.

In some embodiments, the light energy distribution along the optical axis, for example on-axis focal points, formed by the central zone and/or the narrow and/or annular optical zones of the peripheral zone may combine to provide an extended depth of focus, that may be formed over a range of vergences useful for vision correction including correcting myopia, hyperopia, presbyopia, astigmatism and/or any combinations thereof or for binocular vision orders and visual fatigue syndromes. In some embodiments, the on-axis focal points formed by the central zone and/or the narrow and/or annular optical zones of the peripheral zone may combine to provide an extended depth of focus, that may be formed over a range of vergences along the optical axis useful for controlling the progression of myopia. In some embodiments, the distribution and/or the intensity of the on-axis focal points formed by the central zone and/or the narrow and/or annular optical zones of the peripheral zone may combine to provide a light intensity on the retina that may be of low intensity and/or of relatively uniform intensity over the retinal spot diagram that may slow, reduce or control the progression of myopia. In some embodiments, the distribution and/or the intensity of the on-axis focal points formed by the central zone and/or the narrow and/or annular optical zones of the peripheral zone may combine to provide a light energy on the retina that may be of low energy and/or of relatively uniform intensity over the retinal spot diagram that may reduce, mitigate or prevent night vision dysphotopsias such as glare, haloes, and/or starbursts.

FIG.1illustrates a cross-sectional and a plan view of an exemplary embodiment of an ophthalmic lens, for example a contact lens, that may provide an extended depth of focus useful for vision correction and/or vision treatment and that may also reduce, or mitigate, or prevent one or more night vision disturbances.

The ophthalmic lens with a base power profile100comprises a front surface101, a back surface102, a central zone103and peripheral zones104and105. The central zone103may have a diameter of about 1.0 mm and may be formed by a surface curvature106to form a power profile that when combined with the back surface curvature102, the lens thickness and refractive index may produce at least one focal point along the optical axis in front of the retina208. The peripheral zone104incorporates a plurality of narrow annular concentric optical zones104ato104rthat are about 200 μm wide, are located on the front surface101and may be formed by corresponding line curvatures101a-101rand the resulting surface of the peripheral optical zone may be configured as a smooth and/or continuous surface e.g., without surface discontinuities. In some embodiments, the surface of the peripheral optical zone incorporating the plurality of narrow optical zones may not be configured as smooth and/or continuous (e.g. they may include one or more surface discontinuities). To simplify the diagram, only the first 10 narrow optical zones104ato104jare shown in the plan view and the remaining narrow optical zones104kto104rare not drawn (appearing as a blank space107) in the outer portion of the peripheral zone104while the cross-sectional view includes only the first 5 line curvatures101ato101ethat may configure the first 5 narrow optical zones104ato104eon the front surface of the peripheral zone104. The net resultant power profile of the narrow annular zones104a-104rof the peripheral zone104may be relatively more positive in power than the central zone103. The plurality of narrow annular concentric optical zones104ato104rmay be conjoined with an adjacent narrow annular concentric optical zone and may be formed by at least one line curvature. Additionally, the narrow annular concentric zones may be configured so that the innermost and outermost portions of the at least one narrow optical zones may be geometrically normal to the surface and may provide a lateral separation of the focal points (e.g., the infinite number of focal points) formed by the annular narrow optical zones from the optical axis207. A conjoined zone may exist when the spacing between the two adjacent optical zones may be about 0 mm and the innermost and the outermost portion of the surface curvature of the narrow optical zones may transition to the base curve (e.g., the curvature of the first or the base optical zone) or base curve of the peripheral zone. In some embodiments, at least one of the plurality of narrow zones may be conjoined with a second narrow zone (e.g.104aand104b). In some other embodiments, the at least one of the plurality of narrow optical zones may be spaced apart and, for example, the power profiles may alternate wherein at least one or more of the plurality of narrow zones may have a first power profile and at least one or more of a plurality of narrow zones may have a different power profile.

FIGS.2A,2B and2Cillustrate different views of a schematic ray diagram for parallel light rays originating from a distant object and passing through the example ophthalmic lens ofFIG.1and the optics of a simplified eye model and forming on-axis and off-axis focal points at multiple image planes. The schematic ray diagram illustrated inFIG.2Aprovides an overview of the light rays propagating through the optical system as described. For purposes of clarity, representative light rays are only shown for a portion of the center zone203and for the upper portion of the lens and for only 2 (204a,204b) of the 18 narrow annular conjoined optical zones (previously referred to as104aand104binFIG.1) of the peripheral zone204. The view of the schematic ray diagram illustrated inFIG.2Bprovides zoomed in details of the distribution of representative light rays in front of the eye, within the eye and behind the retinal image plane208by the center zone and the centermost, innermost and outermost portions of the narrow optical zones204aand204b. The zoomed in view of the schematic ray diagram illustrated inFIG.2Cprovides further zoomed in details of focused and defocused representative light rays formed by the center zone203and the first narrow annular optical zone204aalong the optical axis across a depth of focus216over a vergence in front of the retina210to the retinal image plane214.

In some embodiments, the power profile of the central zone203may be relatively more positive than the power required to correct the distance refractive error of the eye of the user and accordingly, as illustrated inFIGS.2A and2B, the light rays203a,203bfrom the central zone203converge to form a focal point212aalong the optical axis at image plane212in front of the retinal image plane214. Importantly, the focal point212aformed by the center zone203may be a reduced energy focal point. Light rays subsequently diverge from the focal point212aand may reach the retinal image plane214forming a defocused image on the retinal image plane214over distance219(FIG.2C).

As seen inFIG.2A,2of the plurality of the narrow annular conjoined optical zones204ato204bin the peripheral zone204may be configured with a surface geometry and a power profile to laterally separate the focal points from the optical axis and form off-axis focal points205dand206dbehind the retinal image plane214. The front surface line curvatures201aand201bforming the narrow optical zones may be configured geometrically as normal to the surface and in some embodiments, the optical axes e.g., the centermost rays205aand206a(and205a′ and206a′ from the bottom portion on the ray diagram cross-section inFIG.2B) of the narrow optical zones204a-204b(FIG.2B) may intersect the optical axis207and form on-axis focal point211aat image plane in front of the reduced light energy coaxial focal point212afrom the center zone203(see, e.g.,FIG.2C).FIG.2Bshows the light rays from the innermost (205b,206b) and outermost (205c,206c) portions of the narrow optical zones204aand204bmay intersect the optical axis207across a wide range of vergences, for example the zone204adisperses the light energy over distance215(e.g., 15 D) between215′ and215″ and the second optical zone204bdisperses the light energy over distance217(e.g., 11 D) between217′ and217″, Dispersing the light energy over distance215and217may be substantially beyond an extended depth of focus216(e.g., about 2D to 3D) between image planes210and214required for useful vision correction and/or vision treatment and accordingly the light energy contributing to forming focal points along the optical axis over distance217and also the depth of focus216may be reduced to lower levels. Likewise, the retinal image quality (RIQ) along the optical axis may also be low but importantly may have sufficient image quality to provide an extended depth of focus useful for vision correction and/or vision treatment by reducing/minimizing interference of low energy in focus images by also lowering the energy level of out of focus images and overcoming one or more limitations of simultaneous vision lenses.FIG.2Cprovides a zoomed in view of the ray diagram from a representative sample of light rays from the center zone203and the first narrow optical zone204aof the peripheral zone204(FIG.2A) over the distance216between focal plane210and the retinal image plane214and may correspond to about the depth of focus provided by the example lens fromFIG.1(e.g., about 2D). The light rays from the small center zone203form a reduced energy focal point at212aand subsequently form a defocused image, also of reduced energy, on the retinal image plane214over about distance219. In addition, further low energy defocused images may be formed over the retinal image plane by defocused light rays from the narrow optical zones such as the centermost light rays (205a) from a reduced energy focal point211aand light rays from a portion of the zone204abetween the innermost (205b) and outermost (205c) light rays converging to focal point205dor diverging after intersecting the optical axis and these rays may be of sufficiently low intensity and sufficiently evenly distributed across the retinal image plane that the in focus retinal image used for far vision at night may have reduced night visual disturbances from e.g., glare, haloes and/or starbursts.

FIGS.3A and3Bare schematic plots of the on-axis power profile of the central zone103and a portion of the peripheral zone104of the ophthalmic lens described inFIG.1, modeled in optical design software (Zemax) in both the sagittal (FIG.3A) and tangential (FIG.3B) directions. The horizontal axis of the power plot is the normalized half chord diameter over a unit of +/−1 from the lens center and so 1 unit represents a 2.5 mm half chord diameter on the ophthalmic lens. The central zone103of the ophthalmic lens100forms a constant power profile301of about +2.25 D over the 1.0 mm diameter. In some embodiments, the central zone power301of the ophthalmic lens may be more positively powered than the refractive error of the eye (e.g., nominally set at +2.25 D for a +1.75 D spherical refractive error) and therefore may form a coaxial focal point212ain front of the retina, as detailed inFIG.2B. In some embodiments, the central zone power profile301may be configured to correct the far refractive error and in some embodiments the center zone power profile may be configured to focus at a vergence other than the far refractive error of the eye. The power profile of a portion, for example about 2 mm width (303) of the peripheral optical zone104comprising a plurality of narrow optical zones (e.g., 10 zones)104ato104jillustrated inFIG.1shows cyclical power profiles in both sagittal and tangential directions. In the sagittal direction, the narrow optical zones of the peripheral zone forms a single cycle of oscillation of power, for example at305between A and B, around the base power of the center zone power301. In some embodiments, the cyclical power profile of the narrow optical zone may oscillate around the base lens power of the peripheral zone. The power profile cycles, for example in the sagittal direction, may form a more positive (“p” e.g.,304) and a more negative (“m” e.g.,306) component relative to central zone power301that may arise from the geometrical normal to the surface configuration of the narrow optical zones. In some embodiments, a line curvature may be used to form the narrow optical zones wherein the power changes within a cycle in the sagittal direction may be linear between the p and m components and passing through the center zone power. In some embodiments, at least two or more-line curvatures may be used to form a narrow optical zone and therefore may be used to provide a different linear power profiles or any shape of power progression by using a greater number of line curvatures within a zone. In some embodiments, at least one line curvature may be used in conjunction with any other surface curvature e.g., at least one spherical or aspherical curvature to provide a curvilinear power profile or any shape of power progression. In some embodiments, any curvature may be used to provide a power profile with any shape and/or slope of progression within a cycle. The absolute power range between the “p” and “m” components in the single power profile cycle e.g., in the sagittal direction between C and D in the first cycle305(the peak to valley or P-V value) of the first and second (between E and F) narrow optical zones of the peripheral region104of example lens100fromFIG.1is about 15 D and about 11 D respectively and the P-V value decreases in value across the peripheral region e.g., between307-308and309-310. In some embodiments, the P-V values may be constant or may not be constant. In some embodiments, the P-V values may increase or decrease or remain constant for at least 2 of the cycles or may be randomly changing. The high-powered cyclical power profiles in the optical zones, for example in the sagittal direction (FIG.3A), may disperse the light energy across a wide range of vergences along the optical axis, for example over distance215and217for the first and second narrow optical zones204aand204bas illustrated inFIG.2Band thereby reducing the light energy of focal points formed along the optical axis. In some embodiments, the first cycle of the cyclical power profile in, for example the sagittal direction, originating from the first narrow optical zone of the peripheral zone adjacent to the center zone e.g. at305may begin with the power profile in the narrow optical zone increasing from A in relatively more positive power than the base center zone power to a maximum more positive power e.g., the ‘p’ or most positive powered component of the cycle and then the power profile may decrease in relatively more negative power than the ‘p’ component and the base center zone power to reach a maximum more negative power e.g., the ‘m’ or most negative powered component. A single cyclical power profile in the sagittal direction may be completed when the power returns to the base power of the center zone e.g., at B. In some embodiments, the first cycle may first reach or pass through the p component or may first reach the m component.

FIG.3Bshows the tangential power map for the example ophthalmic lens described inFIGS.1and2. The cycles of the cyclical power profiles formed by the narrow optical zones e.g.,305(FIG.3A) configured with conjoined line curvatures on the front surface shaped geometrically normal to the surface (plano-concave lens cross section) may form high minus off-axis power values e.g., of −55 D at312inside the single optical zone (e.g. the power at311is formed over a smaller dimension than a single cycle305). The boundaries between the conjoined annular zones on the object side of the lens front surface may form surface contours e.g. a surface contour formed by an outer portion of the first narrow optical zone104aand an inner portion of the second narrow optical zone104b(FIG.1A) at about their boundary, and create a boundary power that may also form high positive off-axis power values e.g., +46 D at313by the narrow optical zones104aand104b. In some embodiments, the high cyclical power values in the sagittal (FIG.3A) and tangential (FIG.3B) direction may contribute to the dispersion of light energy over a very wide range of vergences along the optical axis as illustrated and described inFIG.2B.

The through focus image quality along the optical axis of the ophthalmic lens may be measured by one or more metrics such as the visual strehl ratio and may be determined as the ratio of the integration of the MTF values across the desired spatial frequencies e.g., 0-30 cycles/degree of the image at the vergences along the optical axis divided by the integration of the MTF values across the desired spatial frequencies e.g. 0-30 cycles/degree of an image formed by the equal diffraction limited lens and ranked as 1-0 wherein 1=perfect image quality and 0=poor image quality. The image quality metric may encompass both the intensity of light rays focused at the image plane as well as the intensity of any defocused light rays converging or diverging toward the image plane, and thus the image quality is a sum of higher intensity light rays formed by on-axis optical zones at the image plane as well as interference from any light energy emanating from any other on-axis and off-axis optical zones.

FIG.4is a plot of the through focus retinal image quality (RIQ) curve, in the form of the visual strehl ratio, over −2 D to +3 D vergences for the example lens described inFIG.1over a 5 mm pupil for a 589 nm wavelength. As illustrated, the through focus RIQ for the ophthalmic lens ofFIG.1demonstrates an independent peak (denoted “primary peak” for the purpose of clarity)401that is approximately symmetrical around “0” vergence with a maximum RIQ value of about 0.4 and another independent peak (denoted “secondary peak” in specification and figures)403at about +1.5 D vergence with a maximum RIQ value of about 0.14. Additionally, the image quality may be further defined by calculating the area under the curve402at the primary peak401, the primary Peak RIQ area, and the secondary peak403, the secondary peak RIQ area404. A maximum peak RIQ value may be defined as the highest value of the RIQ for the peak on the through focus RIQ curve. The peak RIQ area may be calculated as the area under the through focus RIQ curve bounded by the maximum RIQ value and a minimum line corresponding to an RIQ value of 0.11. The through focus RIQ curve shown inFIG.4for example lens ofFIG.1may have a secondary peak RIQ value403above 0.11 that is independent because the RIQ values405immediately preceding the peak RIQ value403fall below 0.11 for a range of vergences of about 0.5 D at405(e.g., on side of the peak403with the lower vergence) and then rise above the 0.11 line to form the secondary peak RIQ value at403. In contrast, the RIQ value at −1.5 D vergence (406) may not be considered a secondary peak RIQ value because the RIQ value remains below about 0.11 even though the values over region407(e.g., on side of the ‘peak’ at406with the lower vergence) remain below 0.11. In some embodiments, the through focus RIQ curve for a lens may have one or more peaks

The distribution of the light energy across an image plane at a single vergence, e.g. at the retinal image plane, may be modeled qualitatively as a distribution of light rays across the retinal spot diagram in optical ray tracing software (e.g., Zemax) and may also be quantified by one or more metrics such as the total enclosed energy (e.g., the geometric encircled energy graph computed using ray-image surface intercepts and calculating the amount of the incident light energy over half chord distance in the optical system).FIG.5Ashows the distribution of light rays (dots) over the retinal spot diagram as modeled in optical design software (e.g., Zemax) for the ophthalmic lens embodiment ofFIG.1, andFIG.5Bis a plot of the cumulative fraction of total enclosed energy (CFTEE) over the half chord of the retinal spot diagram shown inFIG.5A. The vergence, and therefore image plane, at which the spot diagram and CFTEE may be computed for the example lens ofFIG.1may depend on the prescribed power of the center zone and may be prescribed relatively more positive in power than the distance spherical equivalent refractive error, SER, (center zone focal point212a,FIG.2B) e.g, about +0.5 D more positive than the SER, to provide the depth of focus (e.g.216,FIG.2Babout fully anterior to the retinal image plane (214as detailed inFIG.2B). Therefore, as prescribed, the retinal image plane of the example lens ofFIG.1may correspond to a vergence of about −0.5 D on the through focus RIQ curve ofFIG.4and the retinal spot diagram and CFTEE shown inFIG.5A,5Bmay be computed at the retinal image plane at a vergence of about −0.5 D. Lens ID 6 is a bifocal contact lens design and the center zone may be prescribed as about the same as the SER and so the retinal image plane corresponds to about 0 vergence (FIG.6R,6T,6U). As seen qualitatively from the lower (400 μm grid) scaled and higher (80 μm grid) scaled spot diagrams ofFIG.5A, the light rays formed at the retinal image plane (about −0.5 D vergence) may be seen as evenly distributed (e.g., with no regions of tightly packed or concentrated light rays outside of the small centroid). Likewise, the total enclosed energy plot inFIG.5Bshows the average slope502of the CFTEE progressing smoothly, without any rapid change in slope over any half chord intervals across the spot diagram with about 50% of the total enclosed energy accumulating before and after 40 μm from the centroid with an average slope of 0.12 units/10 μm. A less steep slope may indicate the absence of regions of concentrated light rays in the spot and regions of concentrated light rays may result in more relatively greater light energy that may increase the visibility of night visual disturbances such as glare, haloes and/or starbursts. Therefore, a useful metric of the evenness and uniformity of the distribution of light energy across the retinal image plane may be represented by the average slope of the CFTEE over a selected half chord from the centroid and/or any portion i.e. interval (the interval slope), along the half chord diameter of the spot diagram, for example, over any 20 μm or 30 μm or 40 μm or 50 μm or more of the half chord diameter from the centroid501, over which about 30% or about 50% or about 75% of the CFTEE of the spot diagram may be spread.

The example lens ofFIG.1, may have a substantially smooth slope of about 0.12 enclosed energy units/10 μm across either a 40 μm half chord, or 50 μm half chord or 60 μm half chord of the spot diagram and/or about 50% of the total enclosed energy falling beyond about the first 40 μm half chord of the spot diagram, and the interval slope (over any 20 μm interval) was not greater than about 0.13 units per 10 μm confirming the qualitative observation fromFIG.5Athat the light rays distributed across the retinal image plane may be substantially evenly distributed.

Further clinical observations with the ophthalmic lens embodiment ofFIG.1in an eye with advanced presbyopia found good visual acuity and minimal ghosting over an extended range from far to near distances and indicates that the retinal image quality may be sufficient for good and/or acceptable vision. In addition, it was observed that the ophthalmic lens ofFIG.1may also reduce, mitigate, or prevent one or more night vision disturbances that may accompany use of ophthalmic devices, systems and/or methods that incorporate simultaneous multifocal optics and/or an extended depth of focus. Clinical observations with the example ophthalmic lens embodiment ofFIG.1in eyes corrected for the distance refractive error, as may occur, for example, in a non presbyopic accommodating eye, has also determined the retinal image quality provided may be sufficient to provide good distance vision (e.g., distance and near visual acuity and minimal ghosting) and may allow the extended depth of focus falling in front of the retina to be used for vision treatments, for example, of myopia progression and/or binocular vision disorders and/or visual fatigue syndromes e.g., computer vision syndrome. In addition, it was observed that the ophthalmic lens ofFIG.1may also reduce, mitigate or prevent one or more night vision disturbances such as glare, haloes and/or starbursts that accompany the use of other ophthalmic devices, systems and/or methods that incorporate simultaneous multifocal optics and/or extended depth of focus for these other applications.

In some embodiments, the central zone and the plurality of narrow optical zones in the peripheral zone in combination with the front surface curvature, lens thickness, back surface curvature and the refractive index may be configured to form a power profile across the central and peripheral zones such that the lens may form on-axis focal points and off-axis focal points over a substantially wide range of vergences to provide an appropriate range of on-axis image qualities and/or light energy distributions along the optical axis and across the retinal image plane that may correct/treat the refractive condition of the eye by extending the depth of focus along the optical axis at least in part on and/or in front of the retina of the eye as well as to reduce, mitigate or prevent one or more night vision disturbances that accompany the use of such ophthalmic devices. In some embodiments, light rays from the central zone form a focal point that may have a higher light energy relative to focal points formed by light rays from the plurality of narrow annular optical zones of the peripheral zone. In some embodiments, the higher light intensity rays may not be positioned at about the midpoint of the most anterior and most posterior (e.g., retinal) image planes (e.g., at another position other than the mid-point of the depth of focus). In some embodiments, the higher light intensity rays may be positioned at about the midpoint of the most anterior and most posterior (e.g. retinal) image planes (e.g., at the mid-point of the depth of focus). In some embodiments, the light distribution across the image planes formed along the depth of focus may be substantially evenly distributed. In some embodiments, light rays from the plurality of narrow annular zones may have a lower light intensity that may have a reduced or lower interference on the near, intermediate, and/or distant image planes used for vision correction and/or vision treatment and may result in improved vision. In some embodiments, the interference from light rays distributed from the plurality of narrow optical zones across the anterior most image plane from retina may be less than the interference across the posterior most (e.g., retinal) image plane. In some embodiments, the light energy distributed at image planes along the optical axis and across the corresponding image planes may reduce, or mitigate, or prevent one or more night vision disturbances. In some embodiments, the center zone diameter and/or the power profile may be used to provide a preferred condition to minimize light interference on in-focus images by out-of-focus images and/or to reduce, or mitigate, or prevent one or more night vision disturbances (e.g. on-axis and/or off-axis focal points and image plane locations, light energy levels, image qualities, total enclosed energy distributions, and/or depth of focus). In some embodiments, the number of narrow optical zones and/or width and/or sagittal power profile and/or tangential power profile and/or m and/or p component values and/or P-V value and/or curvature and/or lateral separation and/or spacing and/or surface location of the optical zones may be used to minimize light interference of in focus images by out of focus images and/or to provide an extended depth of focus and/or to reduce, or mitigate, or prevent one or more night vision disturbances such as glare, haloes and/or starbursts.

FIG.6Asummarizes selected lens geometrical parameters, optical modeling outputs and clinical categorization for a series of lens designs. The clinical observations are categorized as good (providing good vision and relatively low night visual disturbances), or average (providing relatively poorer vision and relatively more visible night visual disturbances (e.g., similar to that observed with commercial multifocal soft contact lenses).

As used inFIG.6A, the following abbreviations and descriptors should be understood as follows:PZ refers to the ophthalmic lens surface incorporating the peripheral optical zone.CZ size refers to the central optical zone diameter.Zones per mm refers to the number of narrow optical zones located in the peripheral optical zone for every millimeter of the peripheral optical zone.Zone width refers to the width of the narrow annular zones in the peripheral optical zone.SER refers to the spherical equivalent refractive error for a user of the ophthalmic lens.Central zone power refers to the base power of the central optical zone.Zone off axis power refers to the diopter power of a middle portion of the first narrow optical zone of the cyclical power profile in the tangential direction.Boundary power refers to the diopter power in the tangential direction at the boundary between the first and second narrow optical zones resulting from the surface contour formed by an outer portion of the first narrow optical zone, the transition between the first and second narrow optical zones and an inner portion of the second narrow optical zone.DOF refers to the vergence range in diopters where a useful vision correction may be obtained for advanced presbyopia as determined from clinical observations.Night vision ratings at DOF refers to ratings of night vision disturbances when the base power profile of the central optical zone is prescribed to position the DOF anterior to the retinal image plane starting from the retinal image plane (i.e., more positively powered than the central optical zone base power).Night vision ratings at CZ focal point refers to ratings of night vision disturbances when the base power profile of the central optical zone is prescribed to correct the SER and thereby positioning a portion of the DOF both anterior and posterior to the retinal image plane.

FIGS.6B,6C,6D,6E,6F,6G,6H,6I,6J,6K,6L,6M,6N,60,6P,6Q,6R,6S,6T, and6Uprovide optical modeling results for the example lens designs ID 2 to ID 6 including, i) through focus RIQ distributions, ii) cyclical power profile (sagittal and tangential directions), iii) retinal spot diagrams at low (e.g. 200 μm×200 μm or 400 μm×400 μm grids) and high scales illustrating spatial distribution of light rays at the retinal image plane and iv) a plot of the CFTEE over the retinal image plane. Similar optical modeling details for the lens labelled Lens ID 1 have been previously presented inFIGS.3-5, as the ophthalmic lens ofFIGS.1-5corresponds to Lens ID 1.

FIG.6AandFIG.6B-6Eprovide details of an exemplary embodiment (Lens ID 2) of an ophthalmic lens that provides an extended depth of focus for vision correction e.g., presbyopia and/or vision treatment e.g., myopia control and further improves night vision by reducing/minimizing one or more visual disturbances such as glare, haloes and/or starbursts. Similar to Lens ID 1, the ophthalmic lens of Lens ID 2 comprises a central zone power profile that is relatively more positively powered than the distance refractive error (the vergence at about −1 D corresponds to the retinal image plane), a peripheral zone with a plurality of conjoined annular zones with line curvatures; a cyclical power profile in the sagittal and tangential direction in the peripheral zone with the cycles incorporating a “m” and “p” component, wherein the cyclical power profile may be designed/modulated (e.g., by altering “m” and “p” components values and sequence, and/or power progression slopes and/or power progression shapes over a power cycle and/or between “m” and “p” components (e.g., linear, curvilinear or other shape), and/or off axis powers and/or boundary powers) to distribute the light energy across a substantially wide range of vergences along the optical axis to result in a retinal image quality within a desired limit of ranges and furthermore, to evenly distribute the light energy across the retinal image plane; and wherein the ophthalmic lens provides an extended depth of focus for vision correction and/or vision treatment and may further substantially improve night vision by reducing one or more visual disturbances. Compared to Lens ID 1, Lens ID 2 has a smaller central zone of about 0.25 mm diameter, a peripheral optical zone comprising 3.3 annular zones/mm and located on the back surface of the ophthalmic lens (FIG.6A). Although the central zone power of both lens Lens ID 1 and ID 2 may be the same e.g., about +0.5 D to +1 D more positively powered than the distance refractive error (the vergence at about −0.5 D to −1 D therefore corresponds to the retinal image plane), the different configuration of Lens ID 2 (diameter of the central zone, width of the annular zone in the peripheral optical zone, the location of the zones on the back surface) may result in a cyclical power profile in the sagittal and tangential directions that may be different between the lenses with varying “m” and “p” components (FIG.6C) andFIG.3). Lens ID 2 may a have a primary independent RIQ peak603and two secondary RIQ peaks601and607that may be independent because the portion of the RIQ curve immediately preceding the RIQ peak values606and609(e.g., on at least the side of the RIQ peak with the lower vergence) fall below the minimal RIQ value 0.11 (e.g., on at least one side of the RIQ peak with the lower vergence). The maximum RIQ value603for the primary RIQ peak at about +1.2 D vergence (located at an image plane in front of the retinal image plane) may be lower for Lens ID 2 than Lens ID 1 (about 0.15 versus about 0.4; compareFIG.6BandFIG.4) but the maximum RIQ value of any secondary independent peaks601,607(FIG.6B) and401(FIG.4) formed for Lens ID 2 and ID 1 may be about the same. The RIQ areas (604,602and402,404) corresponding to the respective RIQ peak values for Lens ID 2 and Lens ID 1, respectively were calculated at about 0.01, 0.01 and 0.01 units*D for Lens ID 2 and 0.14 and 0.07 units*D for Lens ID 1 (FIG.6A). Both lenses (ID 1 and 2) provide good vision with a range of depth of focus of about 2 D indicating that a RIQ value for a primary and secondary RIQ peaks in the range of about 0.11 to about 0.45 and RIQ areas in the range of about the levels calculated for ID Lens 1 and 2 may be adequate for user satisfaction and furthermore, the low light energy may minimize night visual disturbances compared to simultaneous vision lenses.FIG.5AandFIG.6Dillustrating retinal spot diagrams for Lens ID 1 and Lens ID 2 indicate the distribution of light rays for both lenses to be substantially similar across the retinal spot diagram and this may be confirmed quantitatively by the CFTEE plots (FIG.5BandFIG.6E) where the average slopes502,602B were about 0.12 units/10 μm and 0.08 units/10 μm for Lens ID 1 and Lens ID 2 respectively. The interval slopes503,602C for Lens ID 1 and Lens ID 2 were about 0.12 units/10 μm and 0.08 units/10 μm, indicating that the slopes were smooth and constant and where 50% of the CFTEE fell beyond about 40 μm from the centroid for both lens types (FIG.6A).

FIG.6AandFIGS.6F-6Iprovide details of another exemplary embodiment (Lens ID 3) of an ophthalmic lens that may provide similar extended depth of focus as Lens ID 1 for vision correction and/or vision treatment but may not substantially minimize the one or more night vision disturbances. Similar to Lens ID 1, the ophthalmic lens of Lens ID 3 comprises a central zone power profile that is relatively more positively powered (e.g. +1 D) than the distance spherical equivalent distance refractive error (the vergence at −1 D corresponds to the retinal image plane), a peripheral zone with a plurality of annular conjoined zones of a frequency of 1 zone/mm and formed with curves; a cyclical power profile in the sagittal and tangential directions in the peripheral zone with the cycles incorporating a “m” and “p” component, wherein the cyclical power profile in at least a sagittal direction may be designed/modulated (e.g., by altering “m” and “p” components values and sequence, and/or power progression slopes and/or power progression shapes over a power cycle and/or between “m” and “p” components (e.g., linear, curvilinear or other shape), and/or off axis powers and/or boundary powers) to provide an extended depth of focus for vision correction and/or vision treatment. However, unlike Lens ID 1, Lens ID 3 may not distribute (or at least not distribute as effectively) the light energy along the optical axis and/or across the retinal image plane within value range limits to reduce/minimize night vision disturbances from glare, haloes and/or starbursts. Compared to Lens ID 1, Lens ID 3 may have a larger central zone of 3.0 mm diameter and a peripheral optical zone comprising 1.0 annular zones per mm of the lens and the design e.g. surface curvature configuration located on the front surface of the ophthalmic lens (FIG.6A). Although the central zone power and the resulting extended depth of focus may be about the same, the different configuration (e.g., diameter of the central zone, width of the annular zone in the peripheral optical zone, the surface curvature and/or the location of the zones on the front surface) may result in a power profile, including a cyclical power profile in the sagittal and tangential directions that may be different between the lenses with, for example, varying “m” and “p” components and/or off axis powers and/or boundary powers (FIG.6HandFIG.3). Although the depth of focus for both lens examples may be about 2 D (FIG.6A), the through focus RIQ curve for Lens ID 3 (FIG.6F) may be substantially different to the through focus RIQ curve for Lens ID 1 (FIG.4). Lens ID 3 forms single peak RIQ611with a maximum peak RIQ value for the primary peak at about “0” vergence (an image plane about +1 D in front of the retinal image plane) may be higher for Lens ID 3 than Lens ID 1 (about 0.52—FIG.6F) versus about 0.4,FIG.4) and the through focus RIQ curve for Lens ID 3 may remain high over a broader range of vergences over about 2 D depth of focus as seen at613to614(FIG.6F) to provide a useful vision correction over the depth of focus. In contrast, as previously described inFIG.4, Lens ID 1 may form 2 peaks including a primary peak401with a maximum peak value of about 0.4 at “0” vergence, the spread of the primary peak being narrow over a smaller range of vergences from a −0.6 D to +0.5 D and a secondary independent peak403with a maximum peak RIQ value of about 0.14 and spread over a vergence from +1.25 D to +1.7 D. Clinical observations (FIG.6A) indicate that both Lens ID 1 and ID 3 provide good vision for a range (depth of focus) of about 2 D and this may be consistent with the finding that the RIQ values at about the ends of the depth of focus e.g. between about A and A′ on the curve may be about similar for the lens types. As previously noted with Lens ID 2, despite the low maximum peak RIQ values, good vision correction may be achieved along the extended depth of focus range. However, unlike Lens ID 1 and ID 2, Lens ID 3 does not appear to minimize night vision disturbances with performance possibly similar to night vision disturbances observed with regular simultaneous vision multifocals (FIG.6A). The area under the curve for the primary RIQ peak611(the Peak RIQ Area612) of Lens ID 3 (FIG.6F) was about 0.46 units×D and substantially greater than the area under the curve402for primary RIQ peak401of Lens ID 1 at about 0.14 units×D. The relatively higher image quality of Lens ID 3 distributed over a broader range of vergences may provide a more intense and concentrated light energy at the retinal image plane and may result in substantially greater night visual disturbances than Lens ID 1.FIG.5AandFIG.6Hillustrating plots of the retinal spot diagrams for Lens ID 1 and Lens ID 3 indicate the distribution of light rays for both lenses and highlight the relatively less spatially uniform distribution of light rays across the retinal spot diagram for Lens ID 3 and confirmed quantitatively in the CFTEE plots (FIG.5BandFIG.6I) where the average slope of the CFTEE over the 50 μm half chord602C for Lens ID 1 was 0.12 units/10 μm (FIG.6A) and the interval slope601C over the half chord between the centroid and 20 μm was significantly steeper for Lens ID 3 than Lens ID 1,503, (0.15 units/10 μm vs 0.12 units/10 μm). Significantly, within the first 20 μm half chord of the retinal image spot diagram, the fraction of the total enclosed energy accumulated was greater at 35% for Lens ID 3 (FIG.6I) versus 20% for Lens ID 1 (FIG.5B).

FIGS.6J-6M and6N-6Qprovide details of two other exemplary embodiments of ophthalmic lenses (Lens ID 4 and Lens ID 5, Table inFIG.6A) where lens ID 4 may comprise a substantially smaller central zone of 0.25 mm diameter with a power profile that is relatively more positively powered (e.g. about +1 D) than the distance spherical equivalent refractive error (the vergence at about −1 D corresponds to the retinal image plane) of a user, a peripheral zone with a plurality of conjoined annular zones with line curvatures and about 3.3 annular zones/mm, a cyclical power profile in the sagittal and tangential directions in the peripheral zone with the cycles incorporating a “m” and “p” component wherein the cyclical power profile at least in a sagittal direction may be designed/modulated (e.g., by altering “m” and “p” components values and sequence, and/or power progression slopes and/or power progression shapes over a power cycle and/or between “m” and “p” components (e.g., linear, curvilinear or other shape), and/or off axis powers and/or boundary powers) to distribute the light energy across a substantially wide range of vergences along the optical axis to result in a retinal image quality of a desired range and furthermore, to evenly distribute the light energy across the retinal image plane; and wherein the ophthalmic lens provides an extended depth of focus for vision correction and/or vision treatment. The peripheral optical zones of Lens ID 2 may be formed on the back surface whereas those of Lens ID 4 may be formed on the front surface (FIG.6A). Although the central zone power profile may be about the same, the different configuration (e.g. line curvature on front versus back surfaces) may result in a cyclical power profile in the sagittal and tangential directions that is different between the lenses with, for example, varying “m” and “p” components, off axis powers and/or boundary powers (FIG.6CandFIG.6K) and the resultant clinically observed depth of focus different between the embodiments, with over about 2 D versus 1 D for Lens ID 2 and Lens ID 4 respectively (FIG.6A). The through focus RIQ curves of lenses ID 2 and ID 4 (FIG.6BandFIG.6J), respectively) show very low RIQ values of about 0.15 or less across all vergences. In the embodiment Lens ID 2, three independent (RIQ values in regions606,609on lower vergence side of the RIQ peak less than 0.11) peak RIQ values601,603and607(FIG.6B; regions606,609) may be formed with maximum peak RIQ values above about 0.11 and, as reported inFIG.6A, Lens ID 2 provides good vision over the depth of focus e.g. for advanced presbyopia. In contrast, the through focus RIQ curve for Lens ID 4 (FIG.6J) illustrates a single primary peak621with maximum RIQ of about 0.12 at about −0.2 D vergence (at an image plane about +1 D more anterior to the retinal image plane); at the remaining vergences, the maximum RIQ is below about 0.11 and due to the RIQ being very low and as noted inFIG.6A, clinically the lens was unable to provide good vision along an extended range as with Lens ID 2.

As summarized inFIG.6A, ID Lenses 1 to 3 may provide good vision correction over a depth of focus of about 2 D and the lenses may provide peak RIQ values for the through focus curve over the range of vergences illustrated of at least about 0.11 or greater (FIGS.4,6B,6F). In comparison, the RIQ values for ID Lens 4 were almost entirely below about 0.11 across the range of vergences illustrated and thus may not have been sufficient image quality to provide good vision and therefore, it may appear that a maximum peak RIQ value substantially lower than expected of at least about only 0.11 may be required to provide good vision correction. However, only Lens ID 1 and 2 but not Lens ID 3, may minimize night vision disturbances as the RIQ values at one or more peaks along the through focus RIQ curve may be relatively low, at about 0.45 or lower, and the corresponding peak RIQ areas for one or more maximum RIQ peaks may also be balanced at about 0.14 units×Diopters (FIG.6A). These peak RIQ areas for Lens ID Lens 1 and 2 were substantially lower than the peak RIQ area612for Lens ID 3 of 0.46 units×Diopters and these differences may also be reflected in the light energy distribution across the retinal image plane (e.g. CFTEE) where, compared to Lens ID 3, Lens ID 1 and 2 produced a more spatially uniform light energy distribution with an interval slope of the CFTEE over 20 μm (503and601C,FIGS.5B and6I, respectively) of no greater than about 0.13 units/10 μm (FIG.6A) compared to Lens ID 3 at about 0.15 units/10 μm indicating a significant concentration of energy over a portion of the spot diagram even though Lens ID 1 and 3 had 50% of the CFTEE distributed over the 40 μm half chord of the retinal spot diagram. Based on these values, it may be expected that Lens ID 4 may also minimize night vision disturbances compared to typical simultaneous vision multifocals based on the relatively low peak RIQ values621(about 0.12,FIG.6J) and corresponding RIQ area622(about 0.01 units×Diopters,FIGS.6J,6AJ), relatively uniform distribution of light rays modeled across the retinal spot diagram (FIG.6K) and confirmed quantitatively by the CFTEE plots inFIG.6Mwhere about 50% of the total enclosed energy fell beyond 60 μm from the centroid of the retinal spot diagram and the average slope601D of the CFTEE curve was not steep at about 0.08 units/10 μm over the 50 μm interval (FIG.6M). However, night vision disturbances with Lens ID 4 was observed to be similar to other simultaneous multifocals (FIG.6A) because of the overall very low RIQ values, for example below 0.11, across most of the depth of focus through focus RIQ curve provided a lens with overall lower/poor image quality generally including that may also contribute to night vision disturbances.

FIG.6AandFIG.6N-6Qprovide details of another exemplary embodiment (Lens ID 5) with a peripheral zone configured substantially similarly to Lens ID 1 to provide an extended depth of focus range for vision correction and/or vision treatment. Similar to Lens ID 1, the ophthalmic lens of Lens ID 5 comprises a central zone power profile that is relatively more positively powered (e.g., about +1 D) than the distance spherical equivalent refractive error (the vergence at about −1 D corresponds to the retinal image plane), a peripheral zone with a plurality of conjoined annular zones with line curvatures and formed on the front surface of the ophthalmic lens; a cyclical power profile in the sagittal and tangential directions (FIG.6O) in the peripheral zone with cycles incorporating a “m” and “p” component, wherein the cyclical power profile at least in a sagittal direction may be designed/modulated (e.g., by altering “m” and “p” components values and sequence, and/or power progression slopes and/or power progression shapes over a power cycle and/or between “m” and “p” components (e.g., linear, curvilinear or other shape), and/or off axis powers and/or boundary powers) to distribute the light energy across a substantially wide range of vergences along the optical axis to result in a retinal image quality within a desired limit ranges and furthermore, to evenly distribute the light energy across the retinal image plane; and wherein the ophthalmic lens provides an extended depth of focus for vision correction and/or vision treatment and may further substantially improve night vision by reducing one or more visual disturbances. Lens ID 5 has a substantially larger central zone of 3.0 mm diameter than Lens ID 1 (1.0 mm) but both lens types comprise a peripheral zone comprising narrow annular zones of similar width (0.2 mm or 5 cycles/mm) and consequently, Lens ID 5 may have fewer annular zones in the peripheral optical zone from its smaller width (FIG.6A). Although the distance refractive error power and the narrow annular zones widths may be about the same, the cyclical power profiles in the sagittal and tangential directions formed in the peripheral optical zone and the extended depth of focus may be substantially different between the lenses because other geometrical configurations e.g., central optical zone diameters, the plurality of annular zones in the peripheral optical zone and the distance of the first of the annular zones from the optical axis may result in the different light energy distribution along the optical axis and along the retinal spot diagram between the two lens types. The through focus RIQ curve of lens ID 5 (FIG.6N) shows an independent peak (denoted “primary RIQ peak”631for the purpose of clarity) at about +0.1 D vergence (e.g., an image plane more anterior to the retinal image plane by about +1 D) with a maximum peak RIQ value of 0.52 and is higher than the peak RIQ value401of Lens ID 1 (about 0.4,FIG.4). Both lens types may form other independent peaks (denoted “secondary” peaks) at 633, 635 Lens ID 5,FIG.6N and403Lens ID 1,FIG.4because of RIQ values in regions636,638(FIG.6N),405(FIG.4) are about <0.11) with maximum peak RIQ values for these secondary peaks at about similar values (about 0.13). Additionally, the area under the curve or peak RIQ area632for Lens ID 5 is about 0.24 units×Diopters and substantially larger than the peak RIQ area411for Lens ID 1 (0.14 units×Diopters). Therefore, the light energy formed at the retinal image plane by Lens ID 5 may be significantly higher than Lens ID 2. As observed clinically, both lenses may provide good vision along the depth of focus of about 2 D demonstrating a relatively low level of RIQ of about 0.11 or above may be sufficient for user satisfaction. However, despite the similarities in the through focus RIQ curves for the majority of the vergences, clinical observations indicated that Lens ID 5 may not reduce/minimize night vision disturbances compared to commercially available multifocals because the RIQ areas632and402of the lens types (FIG.6NandFIG.4for Lens ID 5 and ID 1, respectively) may be substantially different because the larger central zone of Lens ID 5 may substantially increase the light energy falling across the retinal image plane as compared to Lens ID 1.FIG.5AandFIG.6Dillustrating plots of the retinal spot diagrams for Lens ID 1 and Lens ID 5 may indicate the distribution of light rays on the retinal image plane for both lenses and the relatively less spatially uniform distribution of light rays with increased concentration of light rays around the centroid for Lens ID 5 (diameter of A=40 μm,FIG.6P) than Lens ID 1 (diameter A=10 μm,FIG.5A). The CFTEE plots (FIGS.5B and6Qfor Lens ID 1 and 5, respectively) also show the total enclosed energy formed calculated over the retinal spot diagram by Lens ID 5 was substantially more concentrated with nearly 50% of the total enclosed energy falling within about 20 μm of the centroid (interval slope601E of about 0.25 units/10 μm over the 20 μm half chord diameter) compared to about 60 μm for Lens ID 1 and the interval slope503over 20 μm, of Lens ID 1 was less steep at about 0.12 units/10 μm (FIG.6A). This difference in light energy distribution across the retinal image plane may, at least in part, contribute to the differences in night vision performances.

FIG.6AandFIG.6R-6Uprovide design and optical modeling results of an ophthalmic lens (Lens ID 6) e.g., a soft contact lens incorporating a simultaneous vision optical design used for vision correction e.g., presbyopia and/or vision treatment e.g., myopia control. The contact lens is an annular concentric optical design comprising a 3 mm center zone with a base power profile powered to correct the distance refractive error, a peripheral zone with four 1 mm wide annular zones with zones 1 and 3 providing more positive power than the center zone by +2D in the sagittal direction and zones 2 and 4 providing a power equal to the center zone base power (FIG.6S). The center zone and the peripheral zones may be coaxial and form 2 focal points on the optical axis that may be non-cyclical (e.g., the power profile does not oscillate around the base power). The more positively powered annular zones of Lens ID 6 provide a vision correction of a close-up refractive error in presbyopia e.g., high addition presbyopia and/or a vision treatment defocus in an image plane anterior to the retinal plane in an accommodating progressing myope to control myopia progression. The through focus RIQ curve for the bifocal contact lens, Lens ID 6, plotted inFIG.6Rshows an independent peak (denoted “primary” RIQ peak)643at about +2.5 D vergence with a maximum RIQ peak value of 0.51 and RIQ area645of 0.46 units×D. An independent peak641(RIQ values at644below 0.11) (denoted “secondary” RIQ peak) at about +0.2 D vergence (located at the retinal image plane during distance vision) has a maximum RIQ peak value of 0.35 and RIQ area642of 0.19 units×D. The distribution of light rays across the retinal spot diagram modeled for Lens ID 6 inFIG.6Tindicates light rays are markedly concentrated to smaller regions across the retinal image plane. Likewise, the CFTEE curve for Lens ID 6 plotted inFIG.6Uquantifies the non-uniform distribution of light energy over the image plane, for example, about 35% of the light energy falling over the first 3 μm half chord from the centroid (601F) and then almost no additional energy accumulating between the 5 μm to 40 μm half chord interval602F (e.g., zero slope) and the remaining 65% of the light energy concentrated over the 40 μm to 70 μm half chord interval (relatively steep interval slope603F over 20 μm between 40 μm and 60 μm of about 0.28 units/10 μm).

As categorized inFIG.6A, Lens ID 6 may provide compromised vision typical of simultaneous vision optical designs as the defocused images on the optical axis substantially (e.g., due to the peak RIQ value and peak RIQ areas) interfere with in focused images at the retinal image plane. Night vision was also observed clinically as average because the light rays may not be uniformly distributed across the retinal image plane (FIG.6T), for example light energy concentrated in narrow regions (FIG.6U) resulting in substantial disturbances to night vision by one or more visual disturbances such as glare, haloes and starbursts. The modeling results with Lens ID 6 inFIGS.6R-6Uindicate retinal image quality outside of a desired range e.g. RIQ peak values and peak areas outside the range of about 0.11 to about 0.45 and >0.16 units×D, respectively and may be too high for user satisfaction, and an interval slope601G (FIG.6U) of the CFTEE curve greater than about 0.13 units/10 μm over a 20 μm half-chord diameter that may promote night visual disturbances such as glare, haloes and/or starbursts compared to simultaneous vision lenses.

Therefore, from the various ophthalmic lenses (FIGS.3,4,5,6A-6U) designed with a range of geometrical parameters resulting in a range of optical properties and varying clinical observations, a series of criteria may be defined to design ophthalmic lenses with an extended depth of focus for vision correction and/or vision treatment as well as an improved night vision performance by reducing, mitigating and/or preventing one or more visual disturbances (e.g., by providing lower light energies).

An improved ophthalmic lens with an extended depth of focus for vision correction and/or vision treatment as well as an improved night vision performance by reducing, mitigating and/or preventing one or more visual disturbances may have one or more RIQ values at one or more peaks along the through focus curve be within an acceptable range e.g., an ‘acceptable’ peak RIQ value range is where the maximum peak RIQ value of one or more independent peaks is between about 0.11 and about 0.45. The peak RIQ values and peak RIQ areas outside the defined acceptable value ranges may be determined as ‘substantially unacceptable’ or “slightly unacceptable” as they may be too weak (if <about 0.11 maximum RIQ value) to provide good vision correction or too strong (if >about 0.45 maximum RIQ value) to provide a relatively uniform distribution of relatively low light energy across the retinal spot diagram, for example where the average slope of the CFTEE plot over the 50 μm half chord of the retinal spot diagram may be less than about 0.13 units/10 μm and/or where an interval slope over a 20 μm half chord is not greater than about 0.13 units/10 μm.

FIGS.7A-7Fprovide schematic illustrations of different configurations of cyclical power profiles in the sagittal direction that may be produced by a plurality of optical zones incorporated into one or more of central and/or peripheral optical zones of ophthalmic lenses to provide extended depth of focus for vison correction and/or vision treatment and also reduce, mitigate and or prevent night vision disturbances such as glare, haloes and starbursts. The embodiments of7A-7F may be configured to provide a light energy distribution across a wide range of vergences and to provide independent peak RIQ values and peak RIQ areas generated at vergences along the through focus RIQ curve and/or a light energy distribution over the retinal image plane to within the desirable limits disclosed herein. The pattern of the cyclical power profile pattern may be changed in several parameters, for example in the sagittal direction and as labelled inFIGS.7A-7Fincluding peak to valley (P-V) values of a cycle of the cyclical power profile may be the same or different e.g.,701(FIG.7A),702,703(FIG.7F), the value of the p and m components e.g., at704and705(FIG.7A),706and707(FIG.7B),708and709(FIG.7F) and/or the order p and m components e.g., the m component first at710(FIG.7D),711(FIG.7E) or the p component first e.g., at707(FIG.7B), the width of a single cycle e.g. a wider cycle at713(FIG.7C) than the cycle at714(FIG.7E) and/or an unbalanced cycle where a first portion of the cycle (above the base power line) may be wider than another portion of the cycle (below the base power line) e.g., at715(FIG.7B) of the cyclical power profile, the slope of the power progression within a cycle may be steeply sloped e.g., at716(FIG.7A) and steeper than a more sloped portion of a power profile cycle e.g., at717(FIG.7F), may be constant in power (e.g., is not sloped over a portion of the power profile cycle) e.g., at718(FIG.7D), or where the m component may not equal the p component e.g., p<m at719(FIG.7F) or the where the power progression may change and/or transition within a cycle e.g., the transition at the peak or trough of a p and/or m component may be sharp e.g., at720(FIG.7F), gradual at721(FIG.7C) or slow (e.g., plateaus) at722(FIG.7B) or where the power profile may progress over a portion of a zone e.g. at the base power where the cycle may not slow e.g., at723(FIG.7F) or plateaus e.g., at724(FIG.7D).

In some embodiments, the annular optical zones may comprise at least one cycle and the cycles may be located, at least in part, in the peripheral zone. In some embodiments, the frequency of power profile oscillations across the optical zone may be constant or may vary across the optical zones and may have a frequency defined as cycles/mm, for example, 0.5 cycles/mm, 1 cycles/mm or 1.5 cycles/mm or 2 cycles/mm or 5 cycles/mm or 10 cycles/mm or 20 cycles/mm or 50 cycles/mm or 100 cycles/mm or higher frequency. In some embodiments, the Peak to Valley (P-V) value of the cycles in a sagittal and/or tangential direction within an optical zone may be defined as the absolute power range between the ‘m’ and ‘p’ components. In some embodiments, the P-V value may be constant across the peripheral zone or may not be constant across the peripheral zone, for example, the P-V value may increase from the first optical zone to the last optical zone across the e.g., peripheral zone or may decrease from the first to the last optical zone across the e.g. peripheral zone or may not change in any pattern or may be random. In some embodiments, the P-V value in a sagittal and/or tangential direction may be very low e.g., be about 1 D or may be very high e.g., be about 600 D and/or anywhere in between. In some embodiments, the value and/or ratio of the m and p components in the sagittal and/or tangential direction may be constant over the optical zones or may decrease or increase toward the periphery or may be equal or may be unequal or may have combinations thereof. In some embodiments, the root mean square (RMS) value around base power in the sagittal direction may be constant or may vary, for example, RMS=1.0 or RMS<1.0 or RMS, >1.0.

In some embodiments, the m and p components may be optimized for depth of focus and light energy distribution along the optical axis and/or across the retinal image plane by defining the values of the m and/or p components and the slope of the power profiles and/or the shape of the power profiles within a narrow optical zone and/or of an oscillation cycle. For example, an optical zone in the peripheral zone may have a diameter of 2.0 mm and may have a relatively low frequency of 0.5 cycles/mm and defining the m and p components e.g. in a sagittal direction at −5.0 D and +5.0 D, respectively, with a P-V value of 10.0 D therefore the slope of the power change across the cyclical power cycle and between the m and p components may be slow and may form a plurality of light rays over the cycle of higher light energy compared to a higher frequency cycle formed by a narrower optical zone of similar power parameters. In some embodiments, the power profile e.g. at least in a tangential direction, may be provided that further controls the light energy dispersion over a wide range of vergences along the optical axis to form reduced energy focal points in a distribution beneficial for vision correction and/or vision treatment including, for example, by altering “m” and “p” components values and sequence, and/or power progression slopes and/or power progression shapes over a power cycle and/or between “m” and “p” components (e.g., linear, curvilinear or other shape), and/or off axis powers and/or boundary powers.

In some embodiments, independent maximum peak RIQ values and independent Peak RIQ Areas generated at vergences along the through focus RIQ curve may be controlled within the desirable limits using optical principles other than by modifying cyclical power profiles or by using other optical principles in combination with cyclical power profiles in one or more regions across the ophthalmic lens. In some embodiments, the surface geometry or lens matrix may incorporate features that impart lower or higher order aberrations, refraction, diffraction, phase or non-refractive optical principles or any combinations of refractive and/or non-refractive optical principles thereof to modify the independent peak RIQ values and independent peak RIQ areas generated at vergences along the through focus RIQ curve may be controlled within the desirable limits. For example, the lens ID 5 described inFIGS.6A and6N-6Qmay be redesigned to improve night vision performance by providing a relatively lower light intensity, more evenly distributed across the retinal spot diagram by reducing the maximum peak RIQ value of the independent peak from 0.52 to about 0.45 or lower and to reduce the peak RIQ area to about 0.16 units×Diopters or lower by incorporating, for example, an additional higher order aberration in a portion of the surface geometry on the front and/or back surface of the example lens ID 5. In some embodiments, a non-refractive optical principle such as light scattering features or light amplitude modulating masks may be incorporated over a portion of the center optical zone on one or both surfaces or within at least one or more layers between the lens surfaces in the matrix of the ophthalmic lens.

In some embodiments, the ophthalmic lens may be configured with a central zone located at the center, e.g., the geometrical center or the optical center, of the lens and may be free of narrow optical zones and/or regions of cyclical power profiles. In some embodiments, a portion of the center zone may include, at least in part, narrow optical zones and/or one or more regions of cyclical power profiles that may be used to control the light energy distribution along the optical axis and/or across the retinal image plane within desirable value range limits as disclosed herein. In some embodiments, the center zone may not be located in the center of the lens e.g., the center zone may not be a first optical zone and may be located in a peripheral region and may be positioned inside and/or outside at least a portion of a peripheral zone. In some embodiments, the center zone may be absent e.g. does not exist and its dimension is less than 0.2 mm or less than about 0.1 mm in diameter. In some embodiments, the size of the central zone may alter the light energy intensity along the optical axis and/or the light energy distribution across the retinal image plane to within desirable value range limits as disclosed herein. For example, as the size of the central zone decreases, the peak light energy (e.g., the image quality) may also be reduced. In some soft contact lens or scleral contact lens or intraocular lens embodiments, the dimensions and/or power profiles of the center and peripheral zones including the diameters, widths, curvatures and cyclical power profiles in the sagittal and tangential directions may be configured proportionally to the dimensions and optics of the particular ophthalmic lens device to provide the required power profiles and light energy distribution along the optical axis and across the retinal image plane as disclosed herein. For example, the central zone diameter may be configured proportionally to the overall diameter of the particular ophthalmic lens and also by the position of the lens relative to the anterior surface of the eye. In general, ophthalmic lenses positioned on or in the eye such as a soft contact lens, or hybrid contact lenses or a rigid gas permeable lens or an intraocular lens may have a center zone that may be less than about 9.0 mm and preferably less than 6.0 mm and preferably less than 4.0 mm and more preferably less than 3.0 mm and even more preferably 2.0 mm or less and ideally the central zone may be very small and be 1.0 mm or less. In some embodiments, for example soft contact lenses, or hybrid contact lenses or RGPs or intraocular lenses, the center zone may be about 0.1 mm to 3.0 mm in diameter. In some embodiments, for example a scleral soft contact lenses where lens diameters may be up to 18 or 20 mm, the center zone may be 12 mm or less than 6.0 mm or less than 4.0 mm or less than 3 mm or 2 mm or less. In some embodiments, the central zone may be very small and be 1.0 mm or less. about 0.1 mm to 3.0 mm in diameter. In some embodiments, for example a spectacle lens, the overall lens diameter may be large and up to 40 mm or 50 mm or 70 mm and more and is also fitted in front of the anterior eye surface by a vertex distance of about 10 mm to 18 mm to the spectacle lens and so the central zone may be about 10.0 mm down to about 0.1 mm half chord diameter. In some embodiments, the central zone may have a power profile that may focus light on-axis on and/or in front of and/or behind the retinal image plane. In some embodiments, the center zone may have a power profile that may correct a far distance refractive error and in some other embodiments the central zone may have a power profile that may not have a power profile to correct a far distance refractive error. As disclosed herein the range limits of RIQ peak value and area metrics and CFTEE distributions and slopes of the CFTEE curves may be referenced to a vergence that corresponds to the retinal image plane. In some embodiments, the referenced vergence may correspond to an image plane used for distance or an intermediate or a close-up vision correction in either an accommodating eye or a presbyopic eye with a more limited accommodative range e.g. a low addition, a medium addition or a high addition correction.

In some embodiments, the annular peripheral zone surrounding the center zone may comprise at least one or more narrow annular concentric optical zones. In some embodiments, the narrow optical zones may be formed by lines or curvatures or any geometrical surface shape or any combinations thereof. In some embodiments, the peripheral optical zones e.g., the zones producing the cycles of the cyclical power profiles may be of any size. For example, they may be narrow, for example, 2.0 mm or less, or 1.0 mm or less or very narrow e.g., 0.7 mm or less or 0.5 mm or less or 0.3 mm or less or 0.2 mm or less or 0.1 mm or narrower. In some embodiments, at least a portion of the peripheral zone may incorporate a plurality of narrow optical zones and may have a frequency defined as zones per mm, for example, 1 zone per mm or 1.5 zones per mm or 2 zones per mm or 5 zones per mm or 10 zones per mm or 20 zones per mm or 50 zones per mm or 100 zones per mm or higher frequency.

In some embodiments, the narrow optical zones may be of about equal width or area or may be unequal in width or area or any combinations thereof in order that the light energy may be widely distributed along the optical axis and be of low light intensity and of a light distribution over the retinal image that is of low and even distribution.

In some embodiments, the narrow peripheral optical zones may be, at least in part, annular and concentric and rotationally symmetric, however, in some other embodiments, the zones may also be, at least in part, non-annular, non-concentric and rotationally asymmetric, for example, the zones may form segments or sectors patches or facets and may be of any geometrical shape and/or arranged in any pattern or may be random.

In some embodiments, the zones may be conjoined or may not be conjoined or may be separated by a transition or a blend that may or may not alter the power profile of the narrow peripheral optical zones.

In some embodiments, the zones may form a smooth and continuous surface profile and the tangent angles either side of the zones may be equal or may vary.

In some embodiments, the surface geometry may incorporate features that impart lower or higher order aberrations, refraction, diffraction, phase or non-refractive optical principles or any combinations of refractive and/or non-refractive optical principles thereof.

In some embodiments, for example some of the ophthalmic lenses described inFIG.6Aproviding an extended depth of focus useful for vision correction and/or vision treatment and/or providing an acceptable amount of light energy along the optical axis and across the retinal image that may minimize night vision disturbances, may incorporate a plurality of narrow optical zones located in the peripheral region of the ophthalmic lenses that may provide a power profile in at least a tangential direction in the optical zones, for example an off-axis power, that even in combination with the eyeball's optical power of about 45 D to about 55 D, may be high, for example may range from moderately high to very high and may be in the range from about +/−5 D or more or about +/−10 D or more or about or +/−40 D or more or about +/−70 D or more or about +/−100 D or more or about +/−150 D or even higher and may form off-axis focal points inside the eyeball e.g., behind the most anterior surface of the eye and/or on or in front of the retina and/or relatively short distance behind the retina. However, in some embodiments the surface geometry of the plurality of narrow optical zones located in the peripheral region of the ophthalmic lens may be configured so the resultant power profiles, in combination with the eyeball's optical power (e.g., about 45 D to about 55 D), may be low or very low or may be about zero power, for example the net off-axis focal power may be about +/−5 D or less or about +/−3 D or less or about +/−1 D or less or about +/−0.5 D or less and therefore may form off-axis focal points that fall outside the eyeball, for example in the object space in front of the anterior surface of the eyeball as a virtual image and/or on or behind the retinal image plane as a real image.

FIGS.8,9and10illustrate a cross sectional view of the schematic ray diagrams of select light rays from a far distance object traced through an exemplary ophthalmic lens and anterior eye optical system incorporating an exemplary optical design in accordance with some embodiments described herein incorporating a plurality of narrow optical zones in the peripheral region that may provide, in combination with the optical power of the eyeball, a very low or zero resultant power profile that may form off-axis focal points in the object space in front of the eye (FIG.8), or may not form off axis focal points (FIG.9) and/or may form off-axis focal points behind the eyeball (FIG.10).

The ophthalmic lens illustrated inFIG.8is a contact lens801and is positioned on the simplified schematic eye802and may have an anterior surface e.g., cornea803and a posterior surface e.g., retina804and may have an optical axis805. For simplicity of illustration, other optical components and structures of the eyeball such as the corneal curvature, crystalline lens and the anterior and posterior chambers may not be illustrated. The ophthalmic lens (e.g., contact lens)801has a front surface806and a back surface807and a center zone808and a peripheral region809that may incorporate a plurality of narrow annular, conjoined optical zones (for illustrative purposes only one of the annular optical zones810on the front surface806is drawn in cross section). The narrow optical zone810may be configured with a line curvature and may form a cyclical power profile that may provide an off-axis power profile of about −54 D in the object space but when combined with the optical power of the eyeball802of +50 D may result in a small net resultant power profile of about −4 D. Consequently, parallel light rays811originating from a distant object may form a virtual image812well in front of the anterior surface of the eyeball802and contact lens801. The light rays813diverge from the focal point812formed by the contact lens-eyeball optical system towards the retinal image plane804and intersect at the optical axis805and form on-axis focal points814and815of reduced energy level and the distance between the 2 focal points816may indicate the length over which the light energy is dispersed along the optical axis. The collection of on-axis focal points formed along the optical axis from light rays from the off-axis virtual image from the very low power profile of the resulting optical system of the eyeball802and the plurality of narrow optical zones e.g.,810in the peripheral region809may form at least one or more peak RIQ values and peak RIQ areas on the through focus RIQ curve and a light energy distribution across the retinal image plane within the predetermined acceptable limits that may provide an extended depth of focus useful for vision correction and/or vision treatment and/or also mitigate, reduce and/or prevent night visual disturbances such as glare, haloes and/or starbursts.

The ophthalmic lens illustrated inFIG.9is a contact lens901and is positioned on the simplified schematic eye902and may have an anterior surface e.g., cornea903and a posterior surface e.g., retina904and may have an optical axis905. For simplicity of illustration, other optical components, and structures of the eyeball such as the corneal curvature, crystalline lens and the anterior and posterior chambers may not be illustrated. The contact lens901has a front surface906and a back surface907and a center zone908and a peripheral region909that may incorporate a plurality of narrow annular, conjoined optical zones (for illustrative purposes only one of the annular optical zones910on the front surface906is drawn in cross section). The narrow optical zone910may be configured with a line curvature and may form a cyclical power profile that may provide an off-axis power profile of about −50 D in the object space but when combined with the optical power of the eyeball902of +50 D may result in a net resultant power profile of about 0 D. Consequently, parallel light rays911originating from a distant object may remain parallel and may not form an off-axis focal point either in front of or behind the anterior surface of the eyeball902and contact lens901or on the retinal image plane904. The parallel light rays911continue their parallel path through the contact lens—eyeball optical system and intersect the optical axis905to form on-axis focal points914and915either side of the retinal image plane904and the distance between the 2 on axis focal points916may indicate the extent of light energy dispersion along the optical axis. The collection of reduced energy focal points dispersed widely along the optical axis by the parallel light from the about zero power profile resulting from the plurality of narrow optical zones e.g.,910in the peripheral region909, and the optical system of the eyeball902, may, without forming off axis focal points, provide at least one or more peak RIQ values and RIQ areas on the through focus RIQ curve and a light energy distribution across the retinal image plane, within the predetermined acceptable limits that may provide an extended depth of focus useful for vision correction and/or vision treatment and/or also mitigate, reduce and/or prevent night visual disturbances such as glare, haloes and/or starbursts.

The ophthalmic lens illustrated inFIG.10is a contact lens1001and is positioned on the simplified schematic eye1002and may have an anterior surface e.g., cornea1003and a posterior surface e.g., retina1004and may have an optical axis1005. For simplicity of illustration, other optical components, and structures of the eyeball such as the corneal curvature, crystalline lens and the anterior and posterior chambers may not be illustrated. The contact lens1001has a front surface1006and a back surface1007and a center zone1008and a peripheral region1009that may incorporate a plurality of narrow annular, conjoined optical zones (for illustrative purposes only one of the annular optical zones1010on the front surface1006is drawn in cross section). The narrow optical zone1010may be configured with a line curvature and may form a cyclical power profile that may provide an off-axis power profile of about −45 D in the object space but when combined with the optical power of the eyeball1002of +50 D may result in a small net resultant power profile of about +5 D. Consequently, parallel light rays1011originating from a distant object may form a real image1012off axis well behind the posterior surface of the eyeball1004and contact lens1001. The light rays1013converge toward the focal point1012formed by the contact lens—eyeball optical system behind the retinal image plane1004and intersect at the optical axis1005and form on-axis focal points1014and1015and the distance between the two on axis focal points1016may indicate the extent of light energy dispersion along the optical axis. The collection of reduced energy focal points dispersed widely along the optical axis by the power profile of the resulting optical system of the eyeball1002and the plurality of narrow optical zones e.g.1010in the peripheral region1009, may form at least one or more peak RIQ values and peak RIQ areas on the through focus RIQ curve and a light energy distribution across the retinal image plane within the predetermined acceptable limits that may provide an extended depth of focus useful for vision correction and/or vision treatment and/or also mitigate, reduce and/or prevent night visual disturbances such as glare, haloes and/or starbursts.

Further advantages of the claimed subject matter will become apparent from the following examples describing certain embodiments of the claimed subject matter. In certain embodiments, one or more than one (including for instance all) of the following further embodiments may comprise each of the other embodiments or parts thereof.

EXAMPLES

A Examples

A1. An ophthalmic lens configured to correct and/or treat at least one condition of the eye (e.g., presbyopia, myopia, hyperopia, astigmatism, binocular vision disorders and/or visual fatigue syndrome) comprising: a central optical zone; a peripheral optical zone; a base power profile; and at least one feature selected to modify the base power profile and to form one or more off-axis focal points in front of, on, and/or behind a retinal image plane and reduce a focal point energy level at one or more image planes; wherein the at least one feature may be located on a front surface and/or a back surface of at least one of the central optical zone and the peripheral optical zone.

A2. The ophthalmic lens of any of the A examples, wherein the at least one feature comprises at least one narrow optical zone incorporating one or more cyclical power profiles and forming one or more off-axis focal points and one or more on-axis focal points along the optical axis.

A3. The ophthalmic lens of any of the A examples, wherein the ophthalmic lens provides a through focus retinal image quality (RIQ) with one or more (e.g., 1, 2, 3, 4, or 5) independent peaks (e.g., over a vergence range of about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D)), and wherein (1) the maximum RIQ value of the independent peaks may be between about 0.11 (e.g., 0.09, 0.1, 0.11, 0.12, 0.13, 0.14 or 0.15) and about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48) or (2) the maximum RIQ value of the independent peaks may be less than about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

A4. The ophthalmic lens of any of the A examples, wherein the ophthalmic lens provides a through focus retinal image quality (RIQ) with one or more (e.g., 1, 2, 3, 4, or 5) independent peaks (e.g., over a vergence range of about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D±3D, ±3.1 D±3.2 D, and/or ±3.25 D)), and wherein an RIQ area of the one or more independent peaks may be about 0.16 Units*Diopters (e.g., 0.13, 0.14, 0.15, 0.16, 0.17, 0.18 or 0.19) or less.

A5. The ophthalmic lens of any of the A examples, wherein the ophthalmic lens provides a through focus retinal image quality (RIQ) with one or more (e.g., 1, 2, 3, 4, or 5) independent peaks (e.g., over a vergence range of about ±3.0 D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D)), and wherein there may be at least one or more independent peaks (e.g., 1, 2, 3, 4, or 5 peaks).

A6. The ophthalmic lens of any of the A examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across the central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens.

A7. The ophthalmic lens of any of the A examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across the central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein a peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of the cycle of the cyclical power profile in the sagittal direction may be about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, about 5 D or less, about 4 D less, about 3D or less, and/or about 2D or less.

A8. The ophthalmic lens of any of the A examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across the central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein the peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of the cycle of the cyclical power profile in the tangential direction may be about 600 D, about 500 D, about 400 D, about 300 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, and/or about 30 D or less.

A9. The ophthalmic lens of any of the A examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across the central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein the frequency of the cyclical power profile may be about 0.5, 1, 1.5, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 50 and/or 100 cycles/mm.

A10. The ophthalmic lens of any of the A examples, wherein the at least one feature comprises a line curvature (e.g., a cyclical power profile formed by a line curvature).

A13. The ophthalmic lens of any of the A examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones located on at least one of the front surface and/or the back surface of the ophthalmic lens and formed by line curvatures.

A14. The ophthalmic lens of any of the A examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and a net resultant power profile of the narrow and/or annular zones of the peripheral zone may be at least one of relatively more positive in power than the central zone, relatively more negative in power than the central zone, and/or about the same power as the central zone.

A15. The ophthalmic lens of any of the A examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be conjoined (e.g., the spacing between the two adjacent optical zones may be substantially zero and the innermost and the outermost portion of the surface curvature of the narrow and/or annular concentric zones transition to the base curve) with an adjacent narrow and/or annular concentric optical zone.

A16. The ophthalmic lens of any of the A examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be spaced apart from one another so as to create an alternating pattern where the base power profile (or a power other than the base power) alternates with the narrow and/or annular concentric zones.

A17. The ophthalmic lens of any of the A examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be configured so that the innermost and outermost portions of at least one of the narrow and/or annular concentric optical zones may be geometrically normal to the surface and provides a lateral separation of the focal points (e.g., infinite number of focal points) formed by the narrow and/or annular concentric optical zones from the optical axis.

A18. The ophthalmic lens of any of the A examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and the light energy and/or image quality formed by the plurality of narrow and/or annular concentric optical zones may be substantially similar and/or dissimilar.

A19. The ophthalmic lens of any of the A examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and one of the plurality of narrow and/or annular concentric optical zones form a single cycle of oscillation of power (e.g., one or both of sagittal and tangential) around the base power profile (e.g., the base power profile of the central optical zone).

A20. The ophthalmic lens of any of the A examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and the power range between the absolute powers of “p” and “m” components in the single power profile cycle (e.g., the peak to valley or P-to-V value) may be at least one of constant or varying (e.g., increasing, decreasing, and or randomly changing) in at least one direction across the optical zone.

A21. The ophthalmic lens of any of the A examples, wherein a combination of at least one or more of the central optical zone size, the plurality of narrow and/or annular concentric optical zones, the front surface curvature, lens thickness, back surface curvature, and the refractive index may be configured to form a power profile across the central and peripheral optical zones such that the ophthalmic lens forms on-axis focal points and off-axis focal points over a substantially wide range of vergences to provide an appropriate range of light energy distributions along the optical axis and across the retinal image plane that correct/treat the refractive condition of the eye by extending the depth of focus along the optical axis at least in part on and/or in front of the retina of the eye to extend the depth of focus and/or to reduce, mitigate or prevent one or more night vision disturbances that accompany the use of such ophthalmic devices.

A22. The ophthalmic lens of any of the A examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and wherein light rays from the plurality of narrow and/or annular concentric optical zones provide a low light energy.

A23. The ophthalmic lens of any of the A examples, wherein an interference from light rays created by the plurality of narrow and/or annular concentric optical zones increases and/or decreases from the anterior most image plane from retina to the posterior most (e.g., retinal) image plane or decreases from the retinal image plane (or another image plane) to at least one of the anterior most image plane and the posterior most image plane.

A24. The ophthalmic lens of any of the A examples, wherein any combination of at least one or more of the central optical zone diameter and/or the power profile of at least a portion of the ophthalmic lens may be used to provide a desirable condition to reduce/minimize light interference on in-focus images by out-of-focus images and/or to reduce, mitigate, or prevent one or more night vision disturbances (e.g. by adjusting one or more of on-axis and/or off-axis focal point and image plane location, light energy, image quality, total enclosed energy distribution, and/or depth of focus).

A25. The ophthalmic lens of any of the A examples, wherein, any combination of one or more of the number of narrow and/or annular concentric optical zones and/or width and/or sagittal power profile and/or tangential power profile and/or boundary power profile and/or m:p ratio (e.g., RMS) and/or P-to-V value and/or surface curvature and/or lateral separation and/or spacing and/or surface location of the optical zones may be used to provide a desirable condition to extend depth of focus, to reduce focal point energy levels, to reduce/minimize light interference on in-focus images by out-of-focus images and/or to reduce, mitigate, or prevent one or more night vision disturbances (e.g., by adjusting one or more of on-axis and/or off-axis focal point and image plane location, light energy, image quality, total enclosed energy distribution, and/or depth of focus).

A26. The ophthalmic lens of any of the A examples, wherein the ophthalmic lens provides, at least in part, an extended depth of focus within the useable vergence ranges encountered by a user of the ophthalmic lens.

A27. The ophthalmic lens of any of the A examples, wherein the one or more on-axis focal points has a low light energy along the optical axis of the ophthalmic lens.

A28. The ophthalmic lens of any of the A examples, wherein the ophthalmic lens is configured to provide a low light energy formed on the retina.

A29. The ophthalmic lens of any of the A examples, wherein light rays that form one or more off-axis focal points may be distributed across a substantially wide range of vergences along the optical axis and in front of, on, and/or behind the retinal image plane of an eye in use.

A30. The ophthalmic lens of any of the A examples, wherein the ophthalmic lens has a uniform or relatively uniform light ray intensity distribution across the retinal spot diagram.

A31. The ophthalmic lens of any of the A examples, wherein a total enclosed energy that results at the retinal image plane may be determined from a retinal spot diagram, and at least more than about 50% (e.g., 45%, 50%, and/or 55%) of the total enclosed energy may be distributed beyond a 35 μm, 40 μm, 45 μm, 50 μm, 55 μm, 60 μm, 65 μm, 70 μm, 75 μm, 80 μm, and/or 95 μm half chord diameter of the retinal spot diagram.

A33. The ophthalmic lens of any of the A examples, wherein the central optical zone has a half-chord diameter of about 5 mm, about 4 mm, about 3 mm, about 2 mm, about 1.75 mm, about 1.5 mm, about 1.25 mm, about 1.0 mm, about 0.5 mm, about 0.25 mm, about 0.1 mm or less.

A34. The ophthalmic lens of any of the A examples, wherein the at least one feature may be configured to reduce, mitigate and/or prevent one or more night vision disturbances (e.g., any combination of one or more of glare, haloes and/or starbursts).

A35. The ophthalmic lens of any of the A examples, wherein the ophthalmic lens may be one of a contact lens, an intraocular lens, and/or a spectacle lens.

B Examples

B1. An ophthalmic lens configured to correct and/or treat at least one condition of the eye (e.g., presbyopia, myopia, hyperopia, astigmatism, binocular vision disorders and/or visual fatigue syndrome) comprising: an optical zone; a base power profile; and at least one feature selected to modify the base power profile and to form one or more off-axis focal points in front of, on, and/or behind a retinal image plane and reduce a focal point energy level at one or more image planes; wherein the at least one feature may be located on a front surface and/or a back surface of the optical zone.

B2. The ophthalmic lens of any of the B examples, wherein the at least one feature comprises at least one narrow optical zone incorporating one or more cyclical power profiles and forming one or more off-axis focal points and one or more on-axis focal points along the optical axis.

B3. The ophthalmic lens of any of the B examples, wherein the ophthalmic lens provides a through focus retinal image quality (RIQ) with one or more (e.g., 1, 2, 3, 4, or 5) independent peaks (e.g., over a vergence range of about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D)), and wherein (1) the maximum RIQ value of the independent peaks may be between about 0.11 (e.g., 0.09, 0.1, 0.11, 0.12, 0.13, 0.14 or 0.15) and about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48) or (2) the maximum RIQ value of the independent peaks may be less than about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

B4. The ophthalmic lens of any of the B examples, wherein the ophthalmic lens provides a through focus retinal image quality (RIQ) with one or more (e.g., 1, 2, 3, 4, or 5) independent peaks (e.g., over a vergence range of about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D)), and wherein an RIQ area of the one or more independent peaks may be about 0.16 Units*Diopters (e.g., 0.13, 0.14, 0.15, 0.16, 0.17, 0.18 or 0.19) or less.

B5. The ophthalmic lens of any of the B examples, wherein the ophthalmic lens provides a through focus retinal image quality (RIQ) with one or more (e.g., 1, 2, 3, 4, or 5) independent peaks (e.g., over a vergence range of about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D)), and wherein there may be at least one independent peak (e.g., 1, 2, 3, 4, or 5 peaks).

B6. The ophthalmic lens of any of the B examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a portion of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive than the base power profile of the ophthalmic lens; and wherein the frequency of the cyclical power profile may be about 0.5, 1, 1.5, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 50, and/or 100 cycles/mm.

B7. The ophthalmic lens of any of the B examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and the power range between the absolute powers of “p” and “m” components in the single power profile cycle (e.g., the peak to valley or P-to-V value) may be at least one of constant or varying (e.g., increasing, decreasing, and or randomly changing) in at least one direction across the optical zone.

B8. The ophthalmic lens of any of the B examples, wherein, any combination of one or more of the number of narrow and/or annular concentric optical zones and/or width and/or sagittal power profile and/or tangential power profile and/or boundary power profile and/or m:p ratio (e.g., RMS) and/or P-to-V value and/or surface curvature and/or lateral separation and/or spacing and/or surface location of the optical zones may be used to provide a desirable condition to extend depth of focus, to reduce focal point energy levels, to reduce/minimize light interference on in-focus images by out-of-focus images and/or to reduce, or mitigate, or prevent one or more night vision disturbances (e.g., by adjusting one or more of on-axis and/or off-axis focal point and image plane location, light energy, image quality, total enclosed energy distribution, and/or depth of focus).

B9. The ophthalmic lens of any of the B examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a portion of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens.

B10. The ophthalmic lens of any of the B examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a portion of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and

wherein a peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of the cycle of the cyclical power profile in the sagittal direction may be about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, about 5 D or less, about 4 D or less, about 3D or less, and/or about 2D or less.

B11. The ophthalmic lens of any of the B examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a portion of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein the peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of the cycle of the cyclical power profile in the tangential direction may be about 600 D, about 500 D, about 400 D, about 300 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, and/or about 30 D or less.

B12. The ophthalmic lens of any of the B examples, wherein the at least one feature comprises a line curvature (e.g., a cyclical power profile formed by a line curvature).

B15. The ophthalmic lens of any of the B examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones located on at least one of the front surface and/or the back surface of the ophthalmic lens and formed by line curvatures.

B16. The ophthalmic lens of any of the B examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and a net resultant power profile of the narrow and/or annular zones may be at least one of relatively more positive in power than the base power profile, relatively more negative in power than the central zone, and/or about the same power as the central zone.

B17. The ophthalmic lens of any of the B examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric optical zones may be conjoined (e.g., the spacing between the two adjacent narrow and/or annular concentric optical zones may be substantially zero and the innermost and the outermost portion of the surface curvature of the narrow and/or annular concentric zones transition to the base curve) with an adjacent narrow and/or annular concentric optical zone.

B18. The ophthalmic lens of any of the B examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be spaced apart from one another so as to create an alternating pattern where the base power profile (or a power other than the base power) alternates with the narrow and/or annular concentric zones.

B19. The ophthalmic lens of any of the B examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be configured so that the innermost and outermost portions of at least one of the narrow and/or annular concentric optical zones may be geometrically normal to the surface and provides a lateral separation of the focal points (e.g., infinite number of focal points) formed by the narrow and/or annular concentric optical zones from the optical axis.

B20. The ophthalmic lens of any of the B examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and the light energy and/or image quality formed by the plurality of narrow and/or annular concentric optical zones may be substantially similar and/or dissimilar.

B21. The ophthalmic lens of any of the B examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and one of the plurality of narrow and/or annular concentric optical zones form a single cycle of oscillation of power (e.g., one or both of sagittal and tangential) around the base power profile.

B22. The ophthalmic lens of any of the B examples, wherein a combination of at least one or more of the plurality of narrow and/or annular concentric optical zones, the front surface curvature, lens thickness, back surface curvature, and the refractive index may be configured to form a power profile across the optical zone such that the ophthalmic lens forms on-axis focal points and off-axis focal points over a substantially wide range of vergences to provide an appropriate range of light energy distributions along the optical axis and across the retinal image plane that correct/treat the refractive condition of the eye by extending the depth of focus along the optical axis at least in part on and/or in front of the retina of the eye and reduce the light intensity at a retinal plane during use to extend the depth of focus and/or to reduce, mitigate or prevent one or more night vision disturbances that accompany the use of such ophthalmic devices.

B23. The ophthalmic lens of any of the B examples, wherein the at least one feature comprises a plurality of narrow and/or annular concentric optical zones and wherein light rays from the plurality of narrow and/or annular concentric optical zones provide a low light energy.

B24. The ophthalmic lens of any of the B examples, wherein an interference from light rays created by the plurality of narrow and/or annular concentric optical zones increases and/or decreases from the anterior most image plane from retina to the posterior most (e.g., retinal) image plane or decreases from the retinal image plane (or another image plane) to at least one of the anterior most image plane and the posterior most image plane.

B25. The ophthalmic lens of any of the B examples, wherein any combination of at least one or more of the central optical zone diameter and/or the power profile of at least a portion of the ophthalmic lens may be used to provide a desirable condition to reduce/minimize light interference on in-focus images by out-of-focus images and/or to reduce, or mitigate, or prevent one or more night vision disturbances (e.g. by adjusting one or more of on-axis and/or off-axis focal point and image plane location, light energy, image quality, total enclosed energy distribution, and/or depth of focus).

B26. The ophthalmic lens of any of the B examples, wherein the ophthalmic lens provides, at least in part, an extended depth of focus within the useable vergence ranges encountered by a user of the ophthalmic lens.

B27. The ophthalmic lens of any of the B examples, wherein the one or more on-axis focal points has a low light energy along the optical axis of the ophthalmic lens.

B28. The ophthalmic lens of any of the B examples, wherein the ophthalmic lens is configured to provide a low light energy formed on the retina.

B29. The ophthalmic lens of any of the B examples, wherein light rays that form one or more off-axis focal points may be distributed across a substantially wide range of vergences along the optical axis and in front of, on and/or behind the retinal image plane of an eye in use.

B30. The ophthalmic lens of any of the B examples, wherein the ophthalmic lens has a uniform or relatively uniform light intensity distribution across the retinal spot diagram.

B31. The ophthalmic lens of any of the B examples, wherein a total enclosed energy that results at the retinal image plane may be determined from a retinal spot diagram, and at least more than about 50% (e.g., 45%, 50%, and/or 55%) of the total enclosed energy may be distributed beyond a 35 μm, 40 μm, 45 μm, 50 μm, 55 μm, 60 μm, 65 μm, 70 μm, 75 μm, 80 μm, and/or 95 μm half chord diameter of the retinal spot diagram.

B33. The ophthalmic lens of any of the B examples, wherein the ophthalmic lens comprises a central zone and the central optical zone has a half-chord diameter of about 5 mm, about 4 mm, about 3 mm, about 2 mm, about 1.75 mm, about 1.5 mm, about 1.25 mm, about 1.0 mm, about 0.5 mm, about 0.25 mm, about 0.1 mm or less.

B34. The ophthalmic lens of any of the B examples, wherein the at least one feature may be configured to reduce, mitigate and/or prevent one or more night vision disturbances (e.g., any combination of one or more of glare, haloes and/or starbursts).

B35. The ophthalmic lens of any of the B examples, wherein the ophthalmic lens may be one of a contact lens, an intraocular lens, and/or a spectacle lens.

C Examples

C1. An ophthalmic lens comprising: a front surface; a back surface; a central optical zone; an annular peripheral optical zone surrounding the central optical zone; and an optical design formed on at least one of the front surface or the back surface of the ophthalmic lens; wherein the optical design comprises a power profile (e.g., a cyclical or non-cyclical power profile) in the central optical zone that forms at least one focal point along an optical axis (e.g., in front of, on and/or behind the retinal image plane); and wherein the optical design comprises a power profile in the annular peripheral optical zone comprising at least one or more narrow and/or annular conjoined optical zones that have a cyclical power profile and form one or more off-axis focal points (e.g., in front of, on, and/or behind the retinal image plane)

C2. The ophthalmic lens of any of the C examples, wherein the at least one or more narrow and/or annular conjoined optical zones form one or more on-axis focal points along the optical axis (e.g., in front of, on and/or behind the retinal image plane and/or in front of, on and/or behind the on-axis focal point formed by the central optical zone).

C3. The ophthalmic lens of any of the C examples, wherein the ophthalmic lens provides a through focus retinal image quality (RIQ) with one or more (e.g., 1, 2, 3, 4, or 5) independent peaks (e.g., over a vergence range of about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D)), and wherein (1) the maximum RIQ value of the independent peaks may be between about 0.11 (e.g., 0.09, 0.1, 0.11, 0.12, 0.13, 0.14 or 0.15) and about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48) or (2) the maximum RIQ value of the independent peaks may be less than about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

C4. The ophthalmic lens of any of the C examples, wherein the ophthalmic lens provides a through focus retinal image quality (RIQ) with one or more (e.g., 1, 2, 3, 4, or 5) independent peaks (e.g., over a vergence range of about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D)), and wherein an RIQ area of the one or more independent peaks may be about 0.16 Units*Diopters (e.g., 0.13, 0.14, 0.15, 0.16, 0.17, 0.18 or 0.19) or less.

C5. The ophthalmic lens of any of the C examples, wherein the ophthalmic lens provides a through focus retinal image quality (RIQ) with one or more (e.g., 1, 2, 3, 4, or 5) independent peaks (e.g., over a vergence range of about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D)), and wherein there may be at least one independent peak (e.g., 1, 2, 3, 4, or 5 peaks) peaks.

C6. The ophthalmic lens of any of the C examples, wherein the power profile in the annular peripheral optical zone comprises a plurality of narrow and/or annular conjoined optical zones the power range between the absolute powers of “p” and “m” components in the single power profile cycle (e.g., the peak to valley or P-to-V value) may be at least one of constant or varying (e.g., increasing, decreasing, and or randomly changing) in at least one direction across the optical zone.

C7. The ophthalmic lens of any of the C examples, wherein, any combination of one or more of the number of narrow and/or annular conjoined optical zones and/or width and/or sagittal power profile and/or tangential power profile and/or boundary power profile and/or m:p ratio (e.g., RMS) and/or P-to-V value and/or surface curvature and/or lateral separation and/or spacing and/or surface location of the optical zones may be used to provide a desirable condition to extend depth of focus, to reduce focal point energy levels, to reduce/minimize light interference on in-focus images by out-of-focus images and/or to reduce, mitigate, or prevent one or more night vision disturbances (e.g., by adjusting one or more of on-axis and/or off-axis focal point and image plane location, light energy, image quality, total enclosed energy distribution, and/or depth of focus).

C8. The ophthalmic lens of any of the C examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across the central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens.

C9. The ophthalmic lens of any of the C examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across the central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein a peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of the cycle of the cyclical on-axis power profile in the sagittal direction may be about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, about 5 D or less, about 4 D or less, about 3D or less and/or about 2D or.

C10. The ophthalmic lens of any of the C examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across the central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein the peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of the cycle of the cyclical power profile in the tangential direction may be about 600 D, about 500 D, about 400 D, about 300 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, and/or about 30 D or less.

C11. The ophthalmic lens of any of the C examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across the central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein the frequency of the cyclical power profile may be about 0.5, 1, 1.5, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 50, and/or 100 cycles/mm.

C12. The ophthalmic lens of any of the C examples, wherein the power profile in the annular peripheral optical zone comprises a line curvature (e.g., a cyclical power profile formed by a line curvature).

C15. The ophthalmic lens of any of the C examples, wherein the power profile in the annular peripheral optical zone comprises a plurality of narrow and/or annular conjoined optical zones located on at least one of the front surface and/or the back surface of the ophthalmic lens and formed by line curvatures.

C16. The ophthalmic lens of any of the C examples, wherein the power profile in the annular peripheral optical zone comprises a plurality of narrow and/or annular conjoined optical zones and a net resultant power profile of the narrow and/or annular conjoined optical zones of the annular peripheral optical zone may be at least one of relatively more positive in power than the central optical zone, relatively more negative in power than the central zone, and/or about the same power as the central zone.

C17. The ophthalmic lens of any of the C examples, wherein the power profile in the annular peripheral optical zone comprises a plurality of narrow and/or annular conjoined optical zones and the plurality of narrow and/or annular conjoined optical zones may be conjoined (e.g., the spacing between the two adjacent optical zones may be substantially zero and the innermost and the outermost portion of the surface curvature of the narrow and/or annular conjoined optical zones transition to the base curve) with an adjacent narrow and/or annular conjoined optical zones.

C18. The ophthalmic lens of any of the C examples, wherein the power profile in the annular peripheral optical zone comprises a plurality of narrow and/or annular conjoined optical zones and the plurality of narrow and/or annular conjoined optical zones may be spaced apart from one another so as to create an alternating pattern where the spacing between the two adjacent narrow and/or annular conjoined optical zones may be non-zero.

C19. The ophthalmic lens of any of the C examples, wherein the power profile in the annular peripheral optical zone comprises a plurality of narrow and/or annular conjoined optical zones and the plurality of narrow and/or annular conjoined optical zones may be configured so that the innermost and outermost portions of at least one of the narrow and/or annular conjoined optical zones may be geometrically normal to the surface and provides a lateral separation of the focal points (e.g., infinite number of focal points) formed by the narrow and/or annular conjoined optical zones from the optical axis.

C20. The ophthalmic lens of any of the C examples, wherein the power profile in the annular peripheral optical zone comprises a plurality of narrow and/or annular conjoined optical zones and the light energy and/or image quality formed by the plurality of narrow and/or annular conjoined optical zones may be substantially similar and/or dissimilar.

C21. The ophthalmic lens of any of the C examples, wherein the power profile in the annular peripheral optical zone comprises a plurality of narrow and/or annular conjoined optical zones and one of the plurality of narrow and/or annular conjoined optical zones form a single cycle of oscillation of power (e.g., one or both of sagittal and tangential) around the base power profile (e.g., the base power profile of the central optical zone).

C22. The ophthalmic lens of any of the C examples, wherein a combination of at least one or more of the central optical zone size, the plurality of narrow and/or annular conjoined optical zones, the front surface curvature, lens thickness, back surface curvature, and the refractive index may be configured to form a power profile across the central and peripheral optical zones such that the ophthalmic lens forms on-axis focal points and off-axis focal points over a substantially wide range of vergences to provide an appropriate range of light energy distributions along the optical axis and across the retinal image plane that may correct/treat the refractive condition of the eye by extending the depth of focus along the optical axis at least in part on and/or in front of the retina of the eye to extend the depth of focus and/or to reduce the light intensity at a retinal image plane to reduce, mitigate or prevent one or more night vision disturbances that accompany the use of such ophthalmic devices.

C23. The ophthalmic lens of any of the C examples, wherein the power profile in the annular peripheral optical zone comprises a plurality of narrow and/or annular conjoined optical zones and wherein light rays from the plurality of narrow and/or annular conjoined optical zones provide a low light energy.

C24. The ophthalmic lens of any of the C examples, wherein an interference from light rays created by the plurality of narrow and/or annular conjoined optical zones increases and/or decreases from the anterior most image plane from retina to the posterior most (e.g., retinal) image plane or decreases from the retinal image plane (or another image plane) to at least one of the anterior most image plane and the posterior most image plane.

C25. The ophthalmic lens of any of the C examples, wherein any combination of at least one or more of the central optical zone diameter and/or the power profile of at least a portion of the ophthalmic lens may be used to provide a desirable condition to reduce/minimize light interference on in-focus images by out-of-focus images and/or to reduce, or mitigate, or prevent one or more night vision disturbances (e.g. by adjusting one or more of on-axis and/or off-axis focal point and image plane location, light energy, image quality, total enclosed energy distribution, and/or depth of focus).

C26. The ophthalmic lens of any of the C examples, wherein the ophthalmic lens provides, at least in part, an extended depth of focus within the useable vergence ranges encountered by a user of the ophthalmic lens.

C27. The ophthalmic lens of any of the C examples, wherein the one or more on-axis focal points has a low light energy along the optical axis of the ophthalmic lens.

C28. The ophthalmic lens of any of the C examples, wherein the ophthalmic lens is configured to provide a low light energy formed on the retina.

C29. The ophthalmic lens of any of the C examples, wherein light rays that form one or more off-axis focal points may be distributed across a substantially wide range of vergences along the optical axis and in front of, on and/or behind the retinal image plane of an eye in use.

C30. The ophthalmic lens of any of the C examples, wherein the ophthalmic lens has a uniform or relatively uniform light intensity distribution across the retinal spot diagram.

C31. The ophthalmic lens of any of the C examples, wherein a total enclosed energy that results at the retinal image plane may be determined from a retinal spot diagram, and at least more than about 50% (e.g., 45%, 50%, and/or 55%) of the total enclosed energy may be distributed beyond a 35 μm, 40 μm, 45 μm, 50 μm, 55 μm, 60 μm, 65 μm, 70 μm 75 μm, 80 μm, and/or 95 μm half chord diameter of the retinal spot diagram.

C33. The ophthalmic lens of any of the C examples, wherein the central optical zone has a half-chord diameter of about 5 mm, about 4 mm, about 3 mm, about 2 mm, about 1.75 mm, about 1.5 mm, about 1.25 mm, about 1.0 mm, about 0.5 mm, about 0.25 mm, about 0.1 mm or less.

C34. The ophthalmic lens of any of the C examples, wherein the ophthalmic lens may be one of a contact lens, an intraocular lens, and/or a spectacle lens.

D Examples

D1. An ophthalmic lens comprising: an optical axis; and an optical zone comprising simultaneous vision and/or extended depth of focus optics; wherein the ophthalmic lens may be configured to provide low light energy levels within a usable vergence range of the ophthalmic lens.

D2. The ophthalmic lens of and of the D examples, wherein the ophthalmic lens has a uniform or relatively uniform light intensity distribution across the retinal spot diagram.

D4. The ophthalmic lens of any of the D examples, wherein a through focus retinal image quality (RIQ) of the ophthalmic lens comprises one or more independent peaks (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, and/or 10 peaks), and wherein the maximum RIQ value of the one or more independent peaks may be less than about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

D5. The ophthalmic lens of any of the D examples, wherein a through focus retinal image quality (RIQ) of the ophthalmic lens comprises one or more independent peaks (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, and/or 10 peaks) over a vergence range of about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D), and wherein the maximum RIQ value of the one or more independent peaks may be less than about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

D6. The ophthalmic lens of any of the D examples, wherein a through focus retinal image quality (RIQ) of the ophthalmic lens comprises one or more independent peaks (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, and/or 10 peaks), and wherein the maximum RIQ value of the one or more independent peaks may be between about 0.11 (e.g., 0.09, 0.1, 0.11, 0.12, 0.13, 0.14 or 0.15) and about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

D8. The ophthalmic lens of any of the D examples, wherein the RIQ Area of the one or more independent peaks may be about 0.16 Units*Diopters (e.g., 0.13, 0.14, 0.15, 0.16, 0.17, 0.18 or 0.19) or less.

D9. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the power range between the absolute powers “p” and “m” components in the single power profile cycle (e.g., the peak to valley or P-to-V value) may be at least one of constant or varying (e.g., increasing, decreasing, and or randomly changing) in at least one direction across the optical zone.

D10. The ophthalmic lens of any of the D examples, wherein the ophthalmic lens (e.g., at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens.

D11. The ophthalmic lens of any of the D examples, wherein the ophthalmic lens (e.g., at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across the central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein a peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of the cycle of the cyclical on-axis power profile in the sagittal direction may be about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, about 5 D or less, about 4 D or less, about 3D or less, and/or about 2D or less.

D12. The ophthalmic lens of any of the D examples, wherein the ophthalmic lens (e.g., at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein the peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of the cycle of the cyclical power profile in the tangential direction may be about 600 D, about 500 D, about 400 D, about 300 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, and/or about 30 D or less.

D13. The ophthalmic lens of any of the D examples, wherein the ophthalmic lens (e.g., at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein the frequency of the cyclical power profile may be about 0.5, 1, 1.5, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 50, and/or 100 cycles/mm.

D14. The ophthalmic lens of any of the D examples, wherein the optical zone comprises a central optical zone, a peripheral optical zone, and at least one feature forming part of the optics of the optical zone located in at least one of the central optical zone and the peripheral optical zone, and selected to modify the base power profile and to form one or more off-axis focal points in front of, on, and/or behind a retinal image plane and reduce a focal point energy level at one or more image planes.

D15. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone may be configured to form one or more off-axis focal points in front of, on, and/or behind a retinal image plane.

D16. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone comprise at least one narrow optical zone incorporating one or more cyclical power profiles and forming one or more off-axis focal points and one or more on-axis focal points along the optical axis.

D17. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone comprise a line curvature (e.g., a cyclical power profile formed by a line curvature).

D20. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones located on at least one of a front surface and/or a back surface of the ophthalmic lens and formed by line curvatures.

D21. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and a net resultant power profile of the narrow and/or annular zones of the peripheral zone may be at least one of relatively more positive in power than the central zone, relatively more negative in power than the central zone, and/or about the same power as the central zone.

D22. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be conjoined (e.g., the spacing between the two adjacent optical zones may be substantially zero and the innermost and the outermost portion of the surface curvature of the narrow and/or annular concentric zones transition to the base curve) with an adjacent narrow and/or annular concentric optical zone.

D23. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be spaced apart from one another so as to create an alternating pattern where the spacing between the two adjacent optical zones may be non-zero.

D24. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be configured so that the innermost and outermost portions of at least one of the narrow and/or annular concentric optical zones may be geometrically normal to the surface and provides a lateral separation of the focal points (e.g., infinite number of focal points) formed by the annular narrow optical zones from the optical axis.

D25. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the light energy and/or image quality formed by the plurality of narrow and/or annular concentric optical zones may be substantially similar and/or dissimilar.

D26. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and one of the plurality of narrow and/or annular concentric optical zones form a single cycle of oscillation of power (e.g., one or both of sagittal and tangential) around the base power profile (e.g., the base power profile of the central optical zone).

D27. The ophthalmic lens of any of the D examples, wherein a combination of at least one or more of the central optical zone size, the plurality of narrow and/or annular concentric optical zones, the front surface curvature, lens thickness, back surface curvature, and the refractive index may be configured to form a power profile across the central and peripheral optical zones such that the ophthalmic lens forms on-axis focal points and off-axis focal points over a substantially wide range of vergences to provide an appropriate range of light energy distributions along the optical axis and across the retinal image plane that correct/treat the refractive condition of the eye by extending the depth of focus along the optical axis at least in part on and/or in front of the retina of the eye to extend the depth of focus and reduce the light intensity at a retinal plane during use to reduce, mitigate or prevent one or more night vision disturbances that accompany the use of such ophthalmic devices.

D28. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and wherein light rays from the plurality of narrow and/or annular concentric optical zones has a lower light intensity.

D29. The ophthalmic lens of any of the D examples, wherein an interference from light rays created by the plurality of narrow and/or annular concentric optical zones increases and/or decreases from the anterior most image plane from retina to the posterior most (e.g., retinal) image plane or decreases from the retinal image plane (or another image plane) to at least one of the anterior most image plane and the posterior most image plane.

D30. The ophthalmic lens of any of the D examples, wherein any combination of at least one or more of a central optical zone diameter and/or a power profile of at least a portion of the ophthalmic lens may be used to provide a desirable condition to reduce or reduce/minimize light interference on in-focus images by out-of-focus images and/or to reduce, mitigate, or prevent one or more night vision disturbances (e.g. by adjusting one or more of on-axis and/or off-axis focal point and image plane location, light energy, image quality, total enclosed energy distribution, and/or depth of focus).

D31. The ophthalmic lens of any of the D examples, wherein, any combination of one or more of the number of narrow and/or annular concentric optical zones and/or width and/or sagittal power profile and/or tangential power profile and/or boundary power profile and/or m:p ratio (e.g., RMS) and/or P-to-V value and/or surface curvature and/or lateral separation and/or spacing and/or surface location of the optical zones may be used to provide a desirable condition to extend depth of focus, to reduce focal point energy levels, to reduce/minimize light interference on in-focus images by out-of-focus images and/or to reduce, or mitigate, or prevent one or more night vision disturbances (e.g., by adjusting one or more of on-axis and/or off-axis focal point and image plane location, light energy, image quality, total enclosed energy distribution, and/or depth of focus).

D32. The ophthalmic lens of any of the D examples, wherein light rays that form one or more off-axis focal points may be distributed across a substantially wide range of vergences along the optical axis and in front of, on and/or behind the retinal image plane of an eye in use.

D33. The ophthalmic lens of any of the D examples, wherein a central optical zone has a half-chord diameter of about 5 mm, about 4 mm, about 3 mm, about 2 mm, about 1.75 mm, about 1.5 mm, about 1.25 mm, about 1.0 mm, about 0.5 mm, about 0.25 mm, about 0.1 mm or less.

D34. The ophthalmic lens of any of the D examples, wherein the optics in the optical zone may be configured to reduce, mitigate or prevent one or more night vision disturbances (e.g., any combination of one or more of glare, haloes and/or starbursts).

D35. The ophthalmic lens of any of the D examples, wherein the ophthalmic lens may be one of a contact lens, an intraocular lens, and/or a spectacle lens.

E Examples

E2. The ophthalmic lens of and of the E examples, wherein the ophthalmic lens has a uniform or relatively uniform light intensity distribution across the retinal spot diagram.

E3. The ophthalmic lens of any of the E examples, wherein a through focus retinal image quality (RIQ) of the ophthalmic lens comprises one or more independent peaks (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, and/or 10 peaks), and wherein the maximum RIQ value of the one or more independent peaks may be less than about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

E4. The ophthalmic lens of any of the E examples, wherein a through focus retinal image quality (RIQ) of the ophthalmic lens comprises one or more independent peaks (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, and/or 10 peaks) over a vergence range of about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D), and wherein the maximum RIQ value of the one or more independent peaks may be less than about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

E5. The ophthalmic lens of any of the E examples, wherein a through focus retinal image quality (RIQ) of the ophthalmic lens comprises one or more independent peaks (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, and/or 10 peaks), and wherein the maximum RIQ value of the one or more independent peaks may be between about 0.11 (e.g., 0.09, 0.1, 0.11, 0.12, 0.13, 0.14 or 0.15) and about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

E7. The ophthalmic lens of any of the E examples, wherein the RIQ Area of the one or more independent peaks may be about 0.16 Units*Diopters (e.g., 0.13, 0.14, 0.15, 0.16, 0.17, 0.18 or 0.19) or less.

E8. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the power range between the absolute powers of “p” and “m” components in the single power profile cycle (e.g., the peak to valley or P-to-V value) may be at least one of constant or varying (e.g., increasing, decreasing, and or randomly changing) in at least one direction across the optical zone.

E9. The ophthalmic lens of any of the E examples, wherein, any combination of one or more of the number of narrow and/or annular concentric optical zones and/or width and/or sagittal power profile and/or tangential power profile and/or boundary power profile and/or m:p ratio (e.g., RMS) and/or P-to-V value and/or surface curvature and/or lateral separation and/or spacing and/or surface location of the optical zones may be used to provide a desirable condition to extend depth of focus, to reduce focal point energy levels, to reduce/minimize light interference on in-focus images by out-of-focus images and/or to reduce, mitigate, or prevent one or more night vision disturbances (e.g., by adjusting one or more of on-axis and/or off-axis focal point and image plane location, light energy, image quality, total enclosed energy distribution, and/or depth of focus).

E10. The ophthalmic lens of any of the E examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens.

E11. The ophthalmic lens of any of the E examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across the central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein a peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of the cycle of the cyclical power profile in the sagittal direction may be about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, about 5 D or less, about 4 D or less, about 3D or less, and/or about 2D or less.

E12. The ophthalmic lens of any of the E examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein the peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of the cycle of the cyclical off-axis power profile in the tangential direction may be about 600 D, about 500 D, about 400 D, about 300 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, and/or about 30 D or less.

E13. The ophthalmic lens of any of the E examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein the frequency of the cyclical power profile may be about 0.5, 1, 1.5, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 50, and/or 100 cycles/mm.

E14. The ophthalmic lens of any of the E examples, wherein the optical zone comprises a central optical zone, a peripheral optical zone, and at least one feature forming part of the optics of the optical zone located in at least one of the central optical zone and the peripheral optical zone, and selected to modify the base power profile and to form one or more off-axis focal points in front of, on, and/or behind a retinal image plane and reduce a focal point energy level at one or more image planes.

E15. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone may be configured to form one or more off-axis focal points in front of, on, and/or behind a retinal image plane.

E16. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone comprise at least one narrow optical zone incorporating one or more cyclical power profiles and forming one or more off-axis focal points and one or more on-axis focal points along the optical axis.

E17. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone comprise a line curvature (e.g., a cyclical power profile formed by a line curvature).

E20. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones located on at least one of a front surface and/or a back surface of the ophthalmic lens and formed by line curvatures.

E21. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and a net resultant power profile of the narrow and/or annular zones of the peripheral zone may be at least one of relatively more positive in power than the central zone, relatively more negative in power than the central zone, and/or about the same power as the central zone.

E22. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be conjoined (e.g., the spacing between the two adjacent optical zones may be substantially zero and the innermost and the outermost portion of the surface curvature of the narrow and/or annular concentric zones transition to the base curve) with an adjacent narrow optical zone.

E23. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be spaced apart from one another so as to create an alternating pattern where the spacing between the two adjacent optical zones may be non-zero.

E24. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be configured so that the innermost and outermost portions of at least one of the narrow and/or annular concentric optical zones may be geometrically normal to the surface and provides a lateral separation of the focal points (e.g., infinite number of focal points) formed by the narrow and/or annular concentric optical zones from the optical axis.

E25. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the light energy and/or image quality formed by the plurality of narrow and/or annular concentric optical zones may be substantially similar and/or dissimilar.

E26. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and one of the plurality of narrow and/or annular concentric optical zones form a single cycle of oscillation of power (e.g., one or both of sagittal and tangential) around the base power profile (e.g., the base power profile of the central optical zone).

E27. The ophthalmic lens of any of the E examples, wherein a combination of at least one or more of the central optical zone size, the plurality of narrow and/or annular concentric optical zones, the front surface curvature, lens thickness, back surface curvature, and the refractive index may be configured to form a power profile across the central and peripheral optical zones such that the ophthalmic lens forms on-axis focal points and off-axis focal points over a substantially wide range of vergences to provide an appropriate range of light energy distributions along the optical axis and across the retinal image plane that correct/treat the refractive condition of the eye by extending the depth of focus along the optical axis at least in part on and/or in front of the retina of the eye to extend the depth of focus and/or to and reduce the light intensity at a retinal plane during use to reduce, mitigate or prevent one or more night vision disturbances that accompany the use of such ophthalmic devices.

E28. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and wherein light rays from the plurality of narrow and/or annular concentric optical zones has a lower light intensity.

E29. The ophthalmic lens of any of the E examples, wherein an interference from light rays created by the plurality of narrow and/or annular concentric optical zones increases and/or decreases from the anterior most image plane from retina to the posterior most (e.g., retinal) image plane or decreases from the retinal image plane (or another image plane) to at least one of the anterior most image plane and the posterior most image plane.

E30. The ophthalmic lens of any of the E examples, wherein and combination of at least one or more of a central optical zone diameter and/or a power profile of at least a portion of the ophthalmic lens may be used to provide a desirable condition to reduce or reduce/minimize light interference on in-focus images by out-of-focus images and/or to reduce, or mitigate, or prevent one or more night vision disturbances (e.g., by adjusting one or more of on-axis and/or off-axis focal point and image plane location, light energy, image quality, total enclosed energy distribution, and/or depth of focus).

E31. The ophthalmic lens of any of the E examples, wherein light rays that form one or more off-axis focal points may be distributed across a substantially wide range of vergences along the optical axis and in front of, on and/or behind the retinal image plane of an eye in use.

E32. The ophthalmic lens of any of the E examples, wherein a central optical zone has a half-chord diameter of about 5 mm, about 4 mm, about 3 mm, about 2 mm, about 1.75 mm, about 1.5 mm, about 1.25 mm, about 1.0 mm, about 0.5 mm, about 0.25 mm, about 0.1 mm or less.

E33. The ophthalmic lens of any of the E examples, wherein the optics in the optical zone may be configured to reduce, mitigate or prevent one or more night vision disturbances (e.g., any combination of one or more of glare, haloes and/or starbursts).

E34. The ophthalmic lens of any of the E examples, wherein the ophthalmic lens may be one of a contact lens, an intraocular lens, and/or a spectacle lens.

F Examples

F1. An ophthalmic lens comprising: an optical axis; an optical zone comprising simultaneous vision and/or extended depth of focus optics; wherein a through focus retinal image quality (RIQ) of the ophthalmic lens comprises one or more independent peaks (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, and/or 10 peaks), and wherein the maximum RIQ value of the one or more independent peaks may be less than about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

F2. The ophthalmic lens of any of the F examples, wherein a through focus retinal image quality (RIQ) of the ophthalmic lens comprises one or more independent peaks (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, and/or 10 peaks) over a vergence range of about ±3D (e.g., ±2.75 D, ±2.8 D, ±2.9 D, ±3D, ±3.1 D, ±3.2 D, and/or ±3.25 D), and wherein the maximum RIQ value of the one or more independent peaks may be less than about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

F3. The ophthalmic lens of any of the F examples, wherein a through focus retinal image quality (RIQ) of the ophthalmic lens comprises one or more independent peaks (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, and/or 10 peaks), and wherein the maximum RIQ value of the one or more independent peaks may be between about 0.11 (e.g., 0.09, 0.1, 0.11, 0.12, 0.13, 0.14 or 0.15) and about 0.45 (e.g., 0.42, 0.43, 0.44, 0.45, 0.46, 0.47 or 0.48).

F5. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and between the power range between the absolute powers of “p” and “m” components in the single power profile cycle (e.g., the peak to valley or P-to-V value) may be at least one of constant or varying (e.g., increasing, decreasing, and or randomly changing) in at least one direction across the optical zone.

F6. The ophthalmic lens of any of the F examples, wherein, any combination of one or more of the number of narrow and/or annular concentric optical zones and/or width and/or sagittal power profile and/or tangential power profile and/or boundary power profile and/or m:p ratio (e.g., RMS) and/or P:V value and/or surface curvature and/or lateral separation and/or spacing and/or surface location of the optical zones may be used to provide a desirable condition to extend depth of focus, to reduce focal point energy levels, to reduce/minimize light interference on in-focus images by out-of-focus images and/or to reduce, or mitigate, or prevent one or more night vision disturbances (e.g., by adjusting one or more of on-axis and/or off-axis focal point and image plane location, light energy, image quality, total enclosed energy distribution, and/or depth of focus).

F7. The ophthalmic lens of any of the F examples, wherein the ophthalmic lens (e.g., at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens.

F8. The ophthalmic lens of any of the F examples, wherein the ophthalmic lens (e.g., at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across the central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein a peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of the cycle of the cyclical on-axis power profile in the sagittal direction may be about 200 D, about 150 D, about 100 D, about 75 D, about 50 D, about 40 D, about 30 D, about 20 D, about 10 D, about 5 D or less, about 4 D or less, about 3D or less, and/or about 2D or less.

F9. The ophthalmic lens of any of the F examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein the peak-to-valley (P-to-V) power range between the absolute powers of the “m” and “p” components of the cycle of the cyclical off-axis power profile in the tangential direction about 600 D, about 500 D, about 400 D, about 300 D, about 200 D, about 175 D, about 150 D, about 125 D, about 100 D, about 75 D, about 60 D, about 50 D, about 40 D, about 35 D, and/or about 30 D or less.

F10. The ophthalmic lens of any of the F examples, wherein the ophthalmic lens (e.g., the at least one feature of the ophthalmic lens) comprises a cyclical power profile comprising one or more cycles across a central and/or peripheral optical zone of the ophthalmic lens and the cycle of the cyclical power profile incorporates a “m” component that may be relatively more negative in power than the base power profile of the ophthalmic lens and a “p” component that may be relatively more positive in power than the base power profile of the ophthalmic lens; and wherein the frequency of the cyclical power profile may be about 0.5, 1, 1.5, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 50, and/or 100 cycles/mm.

F11. The ophthalmic lens of any of the F examples, wherein the ophthalmic lens may be configured to provide low light energy levels within a usable vergence range of the ophthalmic lens.

F12. The ophthalmic lens of any of the F examples, wherein the ophthalmic lens has a uniform or relatively uniform light intensity distribution across the retinal spot diagram.

F14. The ophthalmic lens of any of the F examples, wherein the RIQ Area of the one or more independent peaks may be about 0.16 Units*Diopters (e.g., 0.13, 0.14, 0.15, 0.16, 0.17, 0.18 or 0.19) or less.

F15. The ophthalmic lens of any of the F examples, wherein the optical zone comprises a central optical zone, a peripheral optical zone, and at least one feature forming part of the optics of the optical zone located in at least one of the central optical zone and the peripheral optical zone, and selected to modify the base power profile and to form one or more off-axis focal points in front of, on, and/or behind a retinal image plane and reduce a focal point energy level at one or more image planes.

F16. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone may be configured to form one or more off-axis focal points in front of, on, and/or behind a retinal image plane.

F17. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone comprise at least one narrow optical zone incorporating one or more cyclical power profiles and forming one or more off-axis focal points and one or more on-axis focal points along the optical axis.

F18. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone comprise a line curvature (e.g., a cyclical power profile formed by a line curvature).

F21. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones located on at least one of a front surface and/or a back surface of the ophthalmic lens and formed by line curvatures.

F22. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and a net resultant power profile of the narrow and/or annular zones of the peripheral zone may be at least one of relatively more positive in power than the central zone, relatively more negative in power than the central zone, and/or about the same power as the central zone.

F23. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be conjoined (e.g., the spacing between the two adjacent optical zones may be substantially zero and the innermost and the outermost portion of the surface curvature of the narrow and/or annular concentric zones transition to the base curve) with an adjacent narrow and/or annular concentric optical zone.

F24. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be spaced apart from one another so as to create an alternating pattern where the spacing between the two adjacent optical zones may be non-zero.

F25. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the plurality of narrow and/or annular concentric zones may be configured so that the innermost and outermost portions of at least one of the narrow and/or annular concentric optical zones may be geometrically normal to the surface and provides a lateral separation of the focal points (e.g., infinite number of focal points) formed by the narrow and/or annular optical zones from the optical axis.

F26. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and the light energy and/or image quality formed by the plurality of narrow and/or annular concentric optical zones may be substantially similar and/or dissimilar.

F27. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and one of the plurality of narrow and/or annular concentric optical zones form a single cycle of oscillation of power (e.g., one or both of sagittal and tangential) around the base power profile (e.g., the base power profile of the central optical zone).

F28. The ophthalmic lens of any of the F examples, wherein a combination of at least one or more of the central optical zone size, the plurality of narrow and/or annular concentric optical zones, the front surface curvature, lens thickness, back surface curvature, and the refractive index may be configured to form a power profile across the central and peripheral optical zones such that the ophthalmic lens forms on-axis focal points and off-axis focal points over a substantially wide range of vergences to provide an appropriate range of light energy distributions along the optical axis and across the retinal image plane that may correct/treat the refractive condition of the eye by extending the depth of focus along the optical axis at least in part on and/or in front of the retina of the eye to extend the depth of focus and/or to reduce the light intensity at a retinal plane during use to reduce, mitigate or prevent one or more night vision disturbances that accompany the use of such ophthalmic devices.

F29. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone comprise a plurality of narrow and/or annular concentric optical zones and wherein light rays from the plurality of narrow and/or annular concentric optical zones has a lower light intensity.

F30. The ophthalmic lens of any of the F examples, wherein an interference from light rays created by the plurality of narrow and/or annular concentric optical zones zones increases and/or decreases from the anterior most image plane from retina to the posterior most (e.g., retinal) image plane or decreases from the retinal image plane (or another image plane) to at least one of the anterior most image plane and the posterior most image plane.

F31. The ophthalmic lens of any of the F examples, wherein and combination of at least one or more of a central optical zone diameter and/or a power profile of at least a portion of the ophthalmic lens may be used to provide a desirable condition to reduce or reduce/minimize light interference on in-focus images by out-of-focus images and/or to reduce, mitigate, or prevent one or more night vision disturbances (e.g. by adjusting one or more of on-axis and/or off-axis focal point and image plane location, light energy, image quality, total enclosed energy distribution, and/or depth of focus).

F32. The ophthalmic lens of any of the F examples, wherein light rays that form one or more off-axis focal points may be distributed across a substantially wide range of vergences along the optical axis and in front of, on and/or behind the retinal image plane of an eye in use.

F33. The ophthalmic lens of any of the F examples, wherein a central optical zone has a half-chord diameter of about 5 mm, about 4 mm, about 3 mm, about 2 mm, about 1.75 mm, about 1.5 mm, about 1.25 mm, about 1.0 mm, about 0.5 mm, about 0.25 mm, about 0.1 mm or less.

F34. The ophthalmic lens of any of the F examples, wherein the optics in the optical zone may be configured to reduce, mitigate or prevent one or more night vision disturbances (e.g., any combination of one or more of glare, haloes and/or starbursts).

F35. The ophthalmic lens of any of the F examples, wherein the ophthalmic lens may be one of a contact lens, an intraocular lens, and/or a spectacle lens.

G Examples

G1. A method for managing an ocular condition comprising: utilizing an ophthalmic lens of any of the A, B, C, D, E, and F examples wherein the ophthalmic lens may be configured to provide low light energy levels within a usable vergence range of the ophthalmic lens.

H Examples

H1. A system for managing an ocular condition comprising: any combination of one or more of the ophthalmic lens of any of the A, B, C, D, E, and F examples wherein the one or more ophthalmic lens may be configured to provide low light energy levels within a usable vergence range of the ophthalmic lens.