Ophthalmic lenses for reducing, minimizing, and / or eliminating interference of out-of-focus light with a focused image

Abstract

1. An ophthalmic lens comprising: at least one first optical zone having a first axis, the at least one first optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one first optical zone to a first focal point on the first axis; and at least one second optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one second optical zone to one or more focal points; wherein the at least one second optical zone is configured to provide an extended depth of focus for light extending beyond the one or more focal points.

Description

[Technical Field]

[0001] (Related Applications) This disclosure claims priority to U.S. Provisional Application No. 62 / 890,809, filed August 23, 2019, which priority application is incorporated herein by reference in its entirety. This disclosure is also related to International Application No. PCT / AU2017 / 051173, filed October 25, 2017, and International Application No. PCT / IB2020 / 056079, filed June 26, 2020, each of which is incorporated herein by reference in its entirety.

[0002] (Technical field) The present disclosure relates to ophthalmic lenses, and more particularly to spectacle lenses for suppressing, reducing, minimizing, and / or eliminating interference of out-of-focus images with in-focus images to alter (e.g., improve) the quality of retinal images. [Background technology]

[0003] (background) The eye's optical system determines whether an image is focused on the eye's retina. Images focused on or near the eye's retina are typically perceived as good or acceptable image quality. Images that are far enough away from the eye's retina (focused in front of or behind the retina) are typically perceived as degraded and blurred. Myopia, commonly referred to as nearsightedness, is an optical disorder of the eye that causes on-axis images to focus in front of the retina. An on-axis image is one that is substantially aligned with the fovea or foveal region of the retina (the area where visual acuity is highest). Presbyopia is an optical disorder of the eye in which the lens's ability to accommodate is reduced, resulting in blurred vision at close distances.

[0004] Ophthalmic lenses may be designed to correct distance, intermediate, and / or near vision by providing one or more focal points from one or more optical zones. Ophthalmic lenses with multiple zones (e.g., simultaneous vision lenses) can result in reduced visual acuity because light passing through such lenses can result in overlapping images due to the focal point from one optical zone interfering with the focal point from another optical zone, thus reducing the quality and / or contrast of the retinal image.

[0005] Therefore, there is a need for an ophthalmic lens that inhibits, reduces, minimizes, and / or eliminates interference between focused light (e.g., a focused image) and an out-of-focus image to improve image quality. Exemplary embodiments may reduce, substantially reduce, and / or eliminate the effects of optical disorders, including one or more of myopia, presbyopia, and / or may have other advantages and / or improvements as discussed herein. The present disclosure is directed to solving these and other problems as disclosed herein. The present disclosure is also directed to pointing out one or more advantages for using the exemplary ophthalmic lenses described herein. Summary of the Invention [Means for solving the problem]

[0006] (overview) The present disclosure is directed, at least in part, to overcoming and / or ameliorating one or more of the problems set forth herein.

[0007] The present disclosure is directed, at least in part, to an ophthalmic lens for reducing interference of out-of-focus light with a focused image and improving image quality.

[0008] The present disclosure is directed, at least in part, to an ophthalmic lens for reducing the overlap of out-of-focus light onto an in-focus image and extending depth of focus.

[0009] The present disclosure is directed, at least in part, to an ophthalmic lens for reducing overlap of one or more focal points in a predetermined image plane with one or more defocused images or light rays by separating or shifting the focal points associated with an image in the predetermined image plane from the focal points associated with the one or more defocused images or light rays.

[0010] The present disclosure is directed, at least in part, to an ophthalmic lens for reducing overlap between one or more on-axis foci and one or more off-axis rays to improve image quality and / or extend depth of focus.

[0011] The present disclosure is directed, at least in part, to an ophthalmic lens for reducing overlap of one or more foci of an in-focus image and one or more foci of an out-of-focus image in a given image plane by using one or more light separation means to separate and / or shift one or more foci associated with an in-focus image in the image plane from one or more foci associated with an out-of-focus image.

[0012] The present disclosure is directed, at least in part, to an ophthalmic lens that reduces overlap of one or more foci of an in-focus image and one or more foci of an out-of-focus image at a given image plane by using one or more laterally spaced optical systems to separate and / or shift one or more foci associated with an in-focus image from foci associated with one or more out-of-focus images.

[0013] The present disclosure is directed, at least in part, to optical separation means that utilize one or more optical surfaces having an optical surface including two or more optical elements (e.g., spherical, elliptical, conical, aspherical, or other suitable elements including non-spherical torus elements such as linear, conical, etc.) to separate and / or displace a focal point associated with an in-focus image at a predetermined image plane from a focal point associated with one or more out-of-focus images or rays, wherein the two or more optical elements are positioned, shifted, rotated, tilted, or displaced relative to one another such that all or a portion of the two or more optical elements do not share a common optical axis.

[0014] The present disclosure is directed, at least in part, to laterally spaced optical systems that utilize one or more optical surfaces having optical surfaces including two or more optical elements (e.g., spherical, elliptical, conical, aspherical, or other suitable elements including non-spherical torus elements such as rectilinear, conical, etc.) to space and / or offset a focal point associated with a focused image at a predetermined image plane from a focal point associated with one or more defocused images or rays, wherein the two or more optical elements are positioned, shifted, rotated, tilted, or offset relative to one another such that all or a portion of the two or more optical elements do not share a common optical axis.

[0015] The present disclosure is directed, at least in part, to exemplary devices configured, in use, to utilize one or more optical surfaces including two or more optical elements (e.g., spherical, elliptical, conical, aspherical, or other suitable elements including non-spherical torus elements such as rectilinear, conical, etc.) to space and / or offset at least one focal point associated with a focused image in a predetermined image plane from focal points associated with one or more defocused images or rays, wherein the two or more optical elements are positioned, shifted, rotated, tilted, or offset relative to one another such that all or a portion of the two or more optical elements do not share a common optical axis.

[0016] SUMMARY The present disclosure is directed, at least in part, to an ophthalmic lens for improving image quality.

[0017] The present disclosure is directed, at least in part, to an ophthalmic lens for improving image contrast.

[0018] The present disclosure is directed, at least in part, to an ophthalmic lens for improving the quality of a focused image at a given image plane by reducing overlap between a focal point associated with the focused image at the given image plane and a focal point associated with one or more defocused images.

[0019] The present disclosure is directed, at least in part, to an ophthalmic lens for improving the quality of a focused image at a predetermined image plane by suppressing overlap between a focal point associated with the focused image and a focal point associated with one or more defocused images at the predetermined image plane, wherein the improvement can be a reduction in RMS spot size of about 1 μm or more (e.g., about 0.8 μm, about 0.9 μm, about 1 μm, about 1.1 μm, about 1.2 μm, about 1.3 μm, about 1.4 μm, about 1.5 μm, about 1.6 μm, about 1.7 μm, about 1.8 μm, or about 1.9 μm).

[0020] The present disclosure is directed, at least in part, to ophthalmic lenses having one or more optical zones that do not share a common optical axis.

[0021] The present disclosure is directed, at least in part, to an ophthalmic lens having multiple optical zones or segments, where the optical axes of the multiple optical zones or segments are independent of one another and do not share a common axis.

[0022] The present disclosure is directed, at least in part, to ophthalmic lenses having multiple optical zones or segments, where displacement of the optical axes of the multiple optical zones or segments can produce prismatic power.

[0023] The present disclosure is directed, at least in part, to an ophthalmic lens comprising a plurality of optical zones or segments, wherein the displacement of the optical axis of one of the plurality of optical zones or segments from one of the optical axes of another of the plurality of optical zones or segments is from about 0.05Δ diopters to about 15 prism diopters (Δ) (e.g., about 0.025Δ, about 0.05Δ, about 0.075Δ, about 0.1Δ, about 0.125Δ, about 0.15Δ, about 0.1Δ, about 0.2 ... The present invention is directed to ophthalmic lenses that generate prism powers of approximately 0.175△, approximately 0.2△, approximately 0.25△, approximately 0.3△, approximately 0.35△, approximately 0.4△, approximately 0.45△, approximately 0.5△, approximately 0.6△, approximately 0.7△, approximately 0.8△, approximately 0.9△, approximately 1△, approximately 2△, approximately 3△, approximately 4△, approximately 5△, approximately 6△, approximately 7△, approximately 8△, approximately 9△, approximately 10△, approximately 11△, approximately 12△, approximately 13△, approximately 14△, approximately 15△, approximately 16△, approximately 17△, and approximately 18△.

[0024] The present disclosure provides an ophthalmic lens directed at an ophthalmic lens comprising: a first optical zone defined at least in part by a spherical surface having a first radius and having a first axis, wherein the first optical zone is configured, in use on an eye, to refract light passing through the first optical zone to a first focal point on the first axis; and a second optical zone defined at least in part by a spherical surface having a second radius different from the first radius, wherein the second optical zone is configured, in use on the eye, to refract light passing through the second optical zone to a second focal point (e.g., on the second axis), the second focal point being offset from the first axis by an amount substantially equal to a central zone diameter of the ophthalmic lens.

[0025] The present disclosure is directed, at least in part, to an ophthalmic lens comprising a plurality of optical zones (e.g., 2, 3, 4, or 5 optical zones) configured such that, in use with an eye, light passing through the plurality of optical zones is refracted to a corresponding plurality of one or more focal points on a corresponding plurality of axes, at least two of the plurality of optical zones not sharing a common axis.

[0026] The present disclosure is directed, at least in part, to an ophthalmic lens comprising at least one first optical zone having a first axis, the at least one first optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one first optical zone to a first focal point on the first axis; and at least one second optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one second optical zone to one or more focal points; wherein the one or more focal points from the at least one second optical zone are not on the first axis.

[0027] In some embodiments, the first power may be constant or may vary over different portions of the first optical zone. In some embodiments, the ophthalmic lens may include a third optical zone having a third power. In some embodiments, the third optical zone may be one or more concentric zones adjacent to (e.g., surrounding) the central optical zone. In some embodiments, the third optical zone may be a section, meridian, or portion of the lens other than the section, meridian, or portion occupied by the first optical zone and the second optical zone.

[0028] In some embodiments, the at least one first optical zone and the at least one second optical zone may define an optical zone of the ophthalmic lens.

[0029] In some embodiments, the at least one first optical zone and the at least one second optical zone may occupy a substantial portion (eg, substantially all) of the optical zone of the ophthalmic lens.

[0030] In some embodiments, the at least one first optical zone and the at least one second optical zone may occupy at least 90%, 95%, 98% or 99% of the surface area of ​​the optical zones of the ophthalmic lens.

[0031] In some embodiments, the ophthalmic lens may be configured such that, in use on an eye, out-of-focus light associated with the at least one second optical zone does not substantially interfere with the focal point associated with the at least one first optical zone.

[0032] In some embodiments, the ophthalmic lens may be configured such that, in use on an eye, out-of-focus light associated with at least one first optical zone does not substantially interfere with a focal point associated with at least one second optical zone.

[0033] In some embodiments, the Ophthalmic Lens may be configured such that, when in use on the eye, interference from out-of-focus light at the focused focal point is reduced.

[0034] In some embodiments, at least one first optical zone may have a first optical power and at least one second optical zone has one or more second optical powers different from the first optical power.

[0035] In some embodiments, at least one first optical zone may have a first optical power and at least one second optical zone has a second optical power that is relatively more positive than the first optical power.

[0036] In some embodiments, at least one first optical zone may have a first optical power and at least one second optical zone has a second optical power that is relatively less positive than the first optical power.

[0037] In some embodiments, at least one first optical zone may be configured to correct one or more of distance, intermediate, and near vision, and / or at least one second optical zone is configured to correct a different one of distance, intermediate, or near vision.

[0038] In some embodiments, at least one first optical zone may be configured to correct distance vision and at least one second optical zone is configured to correct near vision.

[0039] In some embodiments, at least one first optical zone in conjunction with one second optical zone is configured to correct one or more of distance vision, intermediate vision, and near vision.

[0040] In some embodiments, at least one first optical zone may be configured to correct near vision and at least one second optical zone is configured to correct distance vision.

[0041] In some embodiments, at least one first optical zone may occupy an upper portion of the optical zone and a second optical zone may occupy a lower portion of the optical zone.

[0042] In some embodiments, the first axis may be an axis of symmetry about which the optical zone of the ophthalmic lens is rotationally symmetric.

[0043] In some embodiments, the first axis can be the optical axis of at least one first optical zone.

[0044] In some embodiments, the first focal point may be on a first axis at a first distance from the ophthalmic lens, and the second focal point may be at a second distance from the ophthalmic lens, the second distance being different from the first distance and offset from the first axis.

[0045] In some embodiments, the second optical zone can have a second axis associated with it, and the second axis can be offset from the first axis.

[0046] In some embodiments, the lateral separation between the first axis and the second axis at the surface of the Ophthalmic Lens may be about 0.5 mm (e.g., about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, about 0.6 mm, about 0.65 mm, about 0.7 mm, about 0.75 mm, about 0.8 mm, about 0.85 mm, about 0.9 mm, or 1 mm). In some embodiments, the lateral separation between the first axis and the second axis at the surface of the Ophthalmic Lens may be about 0.25 mm, about 0.5 mm, or about 0.75 mm. In some embodiments, the lateral separation of the first axis and the second axis at the surface of the ophthalmic lens may be about 1 mm, about 2 mm, or about 3 mm, about 4 mm, about 5 mm, about 6 mm, about 7 mm, or about 8 mm.

[0047] In some embodiments, the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens may be about 0.5 mm or less (e.g., about 50 μm, about 60 μm, about 70 μm, about 80 μm, about 90 μm, about 0.1 mm, about 0.15 mm, about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, or about 0.6 mm or less). In some embodiments, the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens may be about 0.1 mm, about 0.25 mm, or about 0.5 mm or less.

[0048] In some embodiments, the lateral separation between the first axis and the second axis at the surface of the Ophthalmic Lens may be about 50 μm or more (e.g., about 50 μm, about 60 μm, about 70 μm, about 80 μm, about 90 μm, about 0.1 mm, about 0.15 mm, about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, or about 0.6 mm or more). In some embodiments, the lateral separation between the first axis and the second axis at the surface of the Ophthalmic Lens may be about 0.1 mm, about 0.25 mm, or about 0.5 mm or more.

[0049] In some embodiments, the at least one first optical zone may have a substantially circular shape.

[0050] In some embodiments, the at least one First Optical Zone is located in the center of the ophthalmic lens.

[0051] In some embodiments, the at least one first optical zone may have a substantially circular shape located in the center of the ophthalmic lens, and the at least one second optical zone has a substantially annular shape surrounding the at least one first optical zone.

[0052] In some embodiments, at least a portion of the at least one first optical zone may have a substantially circular shape located in the center of the ophthalmic lens, and at least a portion of the at least one second optical zone has a substantially annular shape surrounding the at least one first optical zone.

[0053] In some embodiments, the at least one first optical zone may comprise a first portion having a substantially circular shape located in the center of the ophthalmic lens and a second portion having a substantially annular shape surrounding the first portion.

[0054] In some embodiments, the at least one second optical zone may comprise a first portion having a substantially annular shape surrounding the at least one first optical zone and a second portion having a substantially annular shape surrounding the first portion.

[0055] In some embodiments, the at least one first optical zone and the at least one second optical zone may be concentric (eg, substantially concentric and / or partially concentric).

[0056] In some embodiments, the at least one first optical zone and the at least one second optical zone may be substantially concentric, but do not share a common axis.

[0057] In some embodiments, the at least one first optical zone and / or the at least one second optical zone may be rotationally symmetric about a first axis.

[0058] In some embodiments, at least one first optical zone may be directly adjacent to at least one second optical zone.

[0059] In some embodiments, a blend zone may be located between at least one first optical zone and at least one second optical zone.

[0060] In some embodiments, the at least one first optical zone may occupy 50% or more (eg, about 55%, 60%, 65%, 70%, or 75%) of the surface area of ​​the optical zone of the ophthalmic lens.

[0061] In some embodiments, the at least one first optical zone may occupy 50% or less (eg, about 45%, 40%, 35%, 30%, or 25%) of the surface area of ​​the optical zone of the ophthalmic lens.

[0062] In some embodiments, the at least one first optical zone may occupy about 60% (e.g., about 55%, 56%, 57%, 58%, 59%, 60%, 61%, 62%, 63%, 64%, or 65%) of the surface area of ​​the optical zone of the ophthalmic lens.

[0063] In some embodiments, the at least one first optical zone may occupy about 40% (e.g., about 35%, 36%, 37%, 38%, 39%, 40%, 41%, 42%, 43%, 44%, or 45%) of the surface area of ​​the optical zone of the ophthalmic lens.

[0064] In some embodiments, the at least one first optical zone may occupy about 75% or less (eg, about 55%, 60%, 65%, 70%, or 75%) of the surface area of ​​the optical zone of the ophthalmic lens.

[0065] In some embodiments, the at least one first optical zone may occupy about 25% or more (eg, about 25%, 30%, 35%, 40%, or 45%) of the surface area of ​​the optical zone of the ophthalmic lens.

[0066] In some embodiments, at least one first optical zone may be defined, at least in part, by a spherical surface having a first radius, and / or at least one second optical zone is defined, at least in part, by a spherical surface having a second radius different from the first radius.

[0067] In some embodiments, at least one first optical zone may be defined, at least in part, by a spherical surface having a first radius, and / or at least one second optical zone is defined, at least in part, by a spherical surface having a second radius that is smaller than the first radius.

[0068] In some embodiments, at least one first optical zone may be defined, at least in part, by a spherical surface having a first radius, and / or at least one second optical zone is defined, at least in part, by a spherical surface having a second radius that is greater than the first radius.

[0069] In some embodiments, the at least one first optical zone may be substantially circular in shape and have a diameter of about 3 mm (e.g., in some embodiments, the diameter may be about 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 2-4 mm, 2-3 mm, 3-4 mm, 4 mm or less, 3.5 mm or less, and / or 3 mm or less).

[0070] In some embodiments, the at least one second optical zone may be substantially annular in shape and may have an inner diameter of about 2 mm (e.g., in some embodiments, the inner diameter may be about 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 2-4 mm, 2-3 mm, 3-4 mm, 4 mm or less, 3.5 mm or less, and / or 3 mm or less), and an outer diameter of about 7 mm (e.g., in some embodiments, the outer diameter may be about 3 mm, 4 mm, 5 mm, 5.5 mm, 6 mm, 6.5 mm, 7 mm, 7.5 mm, 8 mm, 5-8 mm, 6-7 mm, 6-8 mm, 8 mm or less, 7.5 mm or less, and / or 7 mm or less).

[0071] In some embodiments, the at least one first optical zone can be substantially circular in shape, the at least one second optical zone can be substantially annular in shape, and the inner diameter of the at least one second optical zone can be substantially equal to the diameter of the at least one first optical zone.

[0072] In some embodiments, the location of the second focal point may be determined, at least in part, by reducing and / or eliminating the slope of the outer surface of the second optical zone relative to the radius of curvature of the first optical zone.

[0073] In some embodiments, the second optical zone may be configured such that, in use in an eye, light passing through at least one second optical zone is refracted to multiple (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, or 16) focal points rather than on the first axis.

[0074] SUMMARY The present disclosure is directed, at least in part, to an ophthalmic lens having an extended depth of focus.

[0075] The present disclosure is directed, at least in part, to an ophthalmic lens comprising at least one first optical zone having a first axis, the at least one first optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one first optical zone to a first focal point on the first axis; and at least one second optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one second optical zone to one or more focal points; wherein the at least one second optical zone is configured to provide an extended depth of focus for light extending beyond the one or more focal points.

[0076] The present disclosure is directed, at least in part, to an ophthalmic lens comprising at least one first optical zone having a first axis, the at least one first optical zone configured, when in use on an eye, to refract at least a portion of light passing through the at least one first optical zone to a first focal point on the first axis; and at least one second optical zone configured, when in use on an eye, to refract at least a portion of light passing through the at least one second optical zone to one or more focal points; wherein the at least one first optical zone is configured such that the first focal point is located anterior to the retinal surface, and the at least one second optical zone is configured such that light refracted to the first focal point, as well as light extending beyond the one or more focal points, provides an extended depth of focus.

[0077] The present disclosure is directed, at least in part, to an ophthalmic lens comprising: at least one first optical zone having a first axis, the at least one first optical zone configured such that, in use on an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focal point on the first axis; and at least one second optical zone configured such that, in use on an eye, at least a portion of light passing through the at least one second optical zone is refracted to one or more focal points; wherein the at least one first optical zone is configured such that the first focal point is located anterior to the retinal surface, and the at least one second optical zone is configured such that light refracted to the first focal point, as well as light extending beyond the one or more focal points, provides an extended depth of focus extending from a retinal image plane to an anterior surface located anterior to the first focal point, where the first focal point is substantially equidistant from the anterior surface and the retinal surface.

[0078] The present disclosure is directed, at least in part, to an ophthalmic lens comprising at least one first optical zone having a first axis, the at least one first optical zone configured, when in use on an eye, to refract at least a portion of light passing through the at least one first optical zone to a first focal point on the first axis; and at least one second optical zone configured, when in use on an eye, to refract at least a portion of light passing through the at least one second optical zone to one or more focal points; wherein the at least one first optical zone is configured such that the first focal point is located anterior to the retinal surface, and the at least one second optical zone is configured such that light refracted to the first focal point, as well as light extending beyond the one or more focal points, provides an extended depth of focus located entirely within the eye.

[0079] In some embodiments, the at least one first optical zone may have a substantially circular shape and be located in the center of the ophthalmic lens, and the at least one second optical zone may have a substantially annular shape surrounding the at least one first optical zone.

[0080] In some embodiments, the at least one first optical zone and the at least one second optical zone may be concentric.

[0081] In some embodiments, the one or more foci located off-axis relative to the first focus may have a finite number of foci (e.g., 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 180, 360, or 720 foci).

[0082] In some embodiments, the one or more foci located off-axis relative to the first focal point have an infinite number of foci.

[0083] In some embodiments, the one or more focal points located off-axis relative to the first focal point may be located on at least two focal planes (eg, at least two, three, four, or five focal planes).

[0084] In some embodiments, the number and position of the one or more foci may be determined, at least in part, based on any combination of one or more of the width of the at least one second optical zone, the curvature of the at least one second optical zone, the position of the at least one second optical zone, the base power of the at least one second optical zone, and / or the lateral spacing of the at least one second optical zone.

[0085] In some embodiments, the depth of focus provided by the ophthalmic lens may be determined, at least in part, based on the width of the at least one second optical zone, the curvature of the at least one second optical zone, the position of the at least one second optical zone, the base power of the at least one second optical zone, the lateral separation value of the at least one second optical zone, and / or any combination of one or more of the m and p components.

[0086] In some embodiments, the at least one second optical zone may have a substantially annular shape with a lateral separation value on the surface of the lens of between 0.2 and 1 mm (e.g., the lateral separation on the surface of the lens may be about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, about 0.6 mm, about 0.65 mm, about 0.7 mm, about 0.75 mm, about 0.8 mm, about 0.85 mm, about 0.9 mm, or 1 mm).

[0087] In some embodiments, the at least one second optical zone may have a substantially annular shape with a lateral separation value on the surface of the lens of between 0.2 and 1 mm (e.g., the lateral separation on the surface of the lens may be less than or equal to about 50 μm, 60 μm, 70 μm, 80 μm, 90 μm, 0.1 mm, 0.15 mm, 0.2 mm, 0.25 mm, 0.3 mm, 0.35 mm, 0.4 mm, 0.45 mm, 0.5 mm, 0.55 mm, and / or 0.6 mm).

[0088] In some embodiments, the at least one second optical zone may have a substantially annular shape with a lateral separation value on the surface of the lens of between 0.2 and 1 mm (e.g., the lateral separation on the surface of the lens may be about 50 μm, 60 μm, 70 μm, 80 μm, 90 μm, 0.1 mm, 0.15 mm, 0.2 mm, 0.25 mm, 0.3 mm, 0.35 mm, 0.4 mm, 0.45 mm, 0.5 mm, 0.55 mm, and / or 0.6 mm or more).

[0089] In some embodiments, at least one focal plane may be in front of, behind, or substantially in the same plane as the first focal point.

[0090] In some embodiments, light rays extending beyond at least one focal plane may form a depth of focus behind and in front of the first focal point.

[0091] In some embodiments, the ratio of the amount of depth of focus in front of the first focus to the amount of depth of focus behind the first focus may be about 100:0 (completely in front of the first focus), 90:10, 80:20, 75:25, 70:30, 60:40, 50:50 (equal in front and behind the first focus), 40:60, 30:70, 25:75, 20:80, 10:90, and / or 0:100 (completely behind the first focus).

[0092] In some embodiments, the cross section of the at least one Second Zone may have a focal length that is independent in two dimensions from the remainder of the Ophthalmic Lens.

[0093] In some embodiments, the at least one second zone may be formed by adjusting the curvature of the base lens on at least one of the outer surface of the ophthalmic lens and / or the inner surface of the ophthalmic lens.

[0094] In some embodiments, the at least one second zone may be formed by adjusting the curvature of the base lens at the outer surface of the ophthalmic lens to form one of a plus optical zone or a minus optical zone.

[0095] In some embodiments, the at least one second zone may be formed by adjusting the curvature of the base lens on the inner surface of the ophthalmic lens to form one of a plus optical zone or a minus optical zone.

[0096] In some embodiments, the at least one second optical zone may have a substantially annular shape that includes an oblique curvature to affect (eg, shift) the depth of focus.

[0097] In some embodiments, at least one second optical zone may have a substantially annular shape with multi-curve infusions (e.g., 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 curve infusions) having the same or different optical properties.

[0098] In some embodiments, at least one second optical zone may have a substantially annular shape with multiple bond curvatures (eg, 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 bond curvatures).

[0099] In some embodiments, at least one second optical zone may have a substantially annular shape formed by replacing at least one (or both) surface curvatures of the lens with straight lines (e.g., a surface with no or substantially no curvature).

[0100] In some embodiments, the depth of focus provided by the ophthalmic lens and / or annular zone may range from about 0.25D to 5D (e.g., about 0.25D, 0.5D, 0.75D, 1D, 1.25D, 1.5D, 1.75D, 2D, 2.25D, 2.5D, 2.75D, 3D, 3.25D, 3.5D, 3.75D, 4D, 4.25D, 4.5D, 4.75D, and / or 5D).

[0101] In some embodiments, the ophthalmic lens may be configured to be used to slow, reduce, or stop the progression of myopia in the eye.

[0102] In some embodiments, the ophthalmic lens may be configured to be used for the correction of myopia.

[0103] In some embodiments, the ophthalmic lens may be configured to be used to correct presbyopia.

[0104] In some embodiments, the ophthalmic lens may be a simultaneous vision lens.

[0105] In some embodiments, the ophthalmic lens may be a split vision lens and / or a progressive addition multifocal (PAL) lens.

[0106] In some embodiments, the ophthalmic lens may be one or more of a spectacle lens, a contact lens, a corneal onlay, a corneal inlay, and an anterior or posterior chamber intraocular lens.

[0107] Other features and advantages of the subject matter described herein will become apparent from the detailed description and drawings, and from the claims. [Brief explanation of the drawings]

[0108] Aspects of the embodiments described herein can be readily understood from the following detailed description when read in conjunction with the accompanying drawings.

[0109] [Figure 1] 1A and 1B are schematic diagrams showing a plan view of a bifocal ophthalmic lens incorporating a central vision correction zone surrounded by zone(s) powered to create myopic defocus for myopia suppression.

[0110] [Figure 2] 2A and 2B are schematic diagrams illustrating ray tracing of a distant object imaged through the ophthalmic lens of FIGS. 1A and 1B.

[0111] [Figure 3] 3A and 3B are schematic diagrams showing spot diagrams of a focal point DF1 of an object point OP1 formed on the retinal plane by the ophthalmic lens of FIGS. 1A and 1B.

[0112] [Figure 4] 4A and 4B are schematic diagrams showing a plan view of an ophthalmic lens (e.g., a contact lens) incorporating a central vision correction zone surrounded by a zone powered to produce myopic defocus for myopia suppression, according to certain embodiments.

[0113] [Figure 5]5A and 5B are schematic diagrams illustrating ray tracing of a distant object imaged through the ophthalmic lens of FIGS. 4A and 4B, according to certain embodiments.

[0114] [Figure 6] 6A and 6B are schematic diagrams illustrating spot diagrams and RMS values ​​of the focal point DF1 of the object point OP1 formed on the retinal plane by the ophthalmic lens of FIGS. 4A and 4B, according to certain embodiments.

[0115] [Figure 7] 7A and 7B are schematic diagrams illustrating a plan view of an ophthalmic lens (e.g., a spectacle lens) configured for myopia suppression and incorporating a central vision correction zone and multiple annular zones with alternating power therebetween to produce myopic defocus, according to certain embodiments.

[0116] [Figure 8] 8A and 8B are schematic diagrams illustrating ray tracing of a distant object imaged through the ophthalmic lens of FIGS. 7A and 7B, according to certain embodiments.

[0117] [Figure 9] 9A and 9B are schematic diagrams illustrating spot diagrams and RMS values ​​of the focal point DF1 of the object point OP1 formed on the retinal plane by the ophthalmic lens of FIGS. 7A and 7B, according to certain embodiments.

[0118] [Figure 10] 10A and 10B are schematic diagrams showing the plan view of an ophthalmic lens (e.g., a presbyopic bifocal soft contact lens) incorporating a central vision correction zone and zone(s) powered to correct near vision for presbyopia.

[0119] [Figure 11] 11A and 11B are schematic diagrams showing ray tracing of a distant object and a near object imaged through the ophthalmic lens of FIGS. 10A and 10B.

[0120] [Figure 12] 12A, 12B, 12C and 12D are schematic diagrams showing spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIGS. 10A and 10B.

[0121] [Figure 13] FIG. 13 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a soft bifocal contact lens) including laterally spaced optics for a distance optical zone and a near optical zone, according to certain embodiments.

[0122] [Figure 14] FIG. 14 is a schematic diagram illustrating ray tracing of a far object and a near object imaged through the ophthalmic lens of FIG. 13 in accordance with certain embodiments.

[0123] [Figure 15] 15A and 15B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 13 according to certain embodiments.

[0124] [Figure 16] FIG. 16 is a schematic diagram illustrating an exemplary design of an ophthalmic lens using a spherical structure, according to certain embodiments.

[0125] [Figure 17] FIG. 17 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a soft bifocal contact lens) including laterally spaced optics for a distance optical zone and a near optical zone, according to certain embodiments.

[0126] [Figure 18] FIG. 18 is a schematic diagram illustrating ray tracing of a far object and a near object imaged through the ophthalmic lens of FIG. 17, in accordance with certain embodiments.

[0127] [Figure 19] 19A and 19B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 17, according to certain embodiments.

[0128] [Figure 20] FIG. 20 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a soft bifocal contact lens) including laterally spaced optics for a distance optical zone and a near optical zone, according to certain embodiments.

[0129] [Figure 21] FIG. 21 is a schematic diagram illustrating ray tracing of a far object and a near object imaged through the ophthalmic lens of FIG. 20 in accordance with certain embodiments.

[0130] [Figure 22] 22A and 22B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 20 according to certain embodiments.

[0131] [Figure 23] FIG. 23 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a soft bifocal contact lens) including laterally spaced optics for a distance optical zone and a near optical zone, according to certain embodiments.

[0132] [Figure 24] FIG. 24 is a schematic diagram illustrating ray tracing of a far object and a near object imaged through the ophthalmic lens of FIG. 23 in accordance with certain embodiments.

[0133] [Figure 25] 25A and 25B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 23 according to certain embodiments.

[0134] [Figure 26] FIG. 26 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a bifocal lens) including laterally spaced optics for a distance optical zone and a near optical zone, according to certain embodiments.

[0135] [Figure 27] FIG. 27 is a schematic diagram illustrating ray tracing of a far object and a near object imaged through the ophthalmic lens of FIG. 26 in accordance with certain embodiments.

[0136] [Figure 28] 28A and 28B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 26 according to certain embodiments.

[0137] [Figure 29A] FIG. 29A is a schematic diagram showing a plan view of an executive bifocal spectacle lens of an embodiment.

[0138] [Figure 29B] FIG. 29B is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a bifocal lens) including laterally spaced optics for a distance optical zone and a near optical zone, according to certain embodiments.

[0139] [Figure 30] FIG. 30 is a schematic diagram illustrating ray tracing of a far object and a near object imaged through the ophthalmic lens of FIG. 29B, in accordance with certain embodiments.

[0140] [Figure 31] 31A and 31B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 29B, according to certain embodiments.

[0141] [Figure 32] FIG. 32 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a bifocal lens) including laterally spaced optics for a distance optical zone and a near optical zone, according to certain embodiments.

[0142] [Figure 33] FIG. 33 is a schematic diagram illustrating ray tracing of a far object and a near object imaged through the ophthalmic lens of FIG. 32 in accordance with certain embodiments.

[0143] [Figure 34] 34A and 34B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 32 according to certain embodiments.

[0144] [Figure 35] FIG. 35 is a schematic diagram illustrating a plan view of an ophthalmic lens (eg, a progressive spectacle lens) including laterally spaced optics for a distance optical zone and a near optical zone, according to certain embodiments.

[0145] [Figure 36] FIG. 36 is a schematic diagram illustrating ray tracing of a far object and a near object imaged through the ophthalmic lens of FIG. 35 in accordance with certain embodiments.

[0146] [Figure 37] 37A and 38B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 35 according to certain embodiments.

[0147] [Figure 38] FIG. 38 is a schematic diagram of a progressive addition (PAL) spectacle lens, according to certain embodiments.

[0148] [Figure 39]FIG. 39 is a geometric diagram showing more details of the outer surfaces used to form the exemplary progressive addition spectacle lens (PAL) shown in FIG. 38, according to certain embodiments.

[0149] [Figure 40] FIG. 40 details the power map of the PAL eyeglass lens design shown in FIG. 39, according to certain embodiments.

[0150] [Figure 41] FIG. 41 is a schematic diagram of an ophthalmic lens illustrating an exemplary embodiment of a geometric normal to the surface of the optic zone, according to certain embodiments.

[0151] [Figure 42] FIG. 42 is a schematic diagram illustrating an exemplary embodiment of a normal to the surface curvature of an optic zone of an ophthalmic lens, according to certain embodiments.

[0152] [Figure 43] 43A and 43B are schematic diagrams illustrating exemplary embodiments of an ophthalmic lens having a geometric normal to the surface line curvature of the optic zone, according to certain embodiments.

[0153] [Figure 44] 44A and 44B are schematic diagrams illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to form an off-axis focal plane and depth of focus, according to certain embodiments.

[0154] [Figure 45] FIG. 45 is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to form an off-axis focal plane and depth of focus, according to certain embodiments.

[0155] [Figure 46]FIG. 46 is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to form an off-axis focal plane and depth of focus, according to certain embodiments.

[0156] [Figure 47] FIG. 47 is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to form an off-axis focal plane and depth of focus, according to certain embodiments.

[0157] [Figure 48] FIG. 48 is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to form an off-axis focal plane and depth of focus, according to certain embodiments.

[0158] [Figure 49] 49A and 49B are schematic diagrams illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to form an off-axis focal plane and depth of focus, according to certain embodiments.

[0159] [Figure 50] FIG. 50 is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to form an off-axis focal plane and depth of focus, according to certain embodiments.

[0160] [Figure 51] 51A and 51B are schematic diagrams illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to form an off-axis focal plane and depth of focus, according to certain embodiments.

[0161] [Figure 52] Figure 52 shows a comparison of retinal image quality (RIQ) between an existing lens design and the lens designs shown in Figures 44A, 44B, and 51B, which have a concentric annular ring design. DETAILED DESCRIPTION OF THE INVENTION

[0162] (Detailed explanation) The following disclosure provides many different embodiments, or examples, for implementing different features of the provided subject matter. Specific examples of components and arrangements are described below to simplify the disclosure. Of course, these are merely examples and are not intended to be limiting. Furthermore, the disclosure may repeat reference numerals and / or letters in various examples. This repetition is for purposes of simplicity and clarity and does not in itself dictate a relationship between the various embodiments and / or configurations discussed.

[0163] The subject headings used in the detailed description are included for ease of reference to the reader and should not be used to limit the subject matter found throughout this disclosure or the claims. The subject headings should not be used in interpreting the scope or limitations of the claims.

[0164] As used in this disclosure, the term "about" is understood to be interchangeable with the term "approximately" or "approximately."

[0165] As used herein, the term "comprises" and its derivatives (e.g., comprises, comprising) are deemed to be inclusive of the features it refers to and are not meant to exclude the presence of additional features unless specifically stated or implied.

[0166] In this disclosure, the terms "offset" or "spaced apart" or "laterally spaced apart" as used in reference to two or more optical axes means that the two or more optical axes or light rays associated with the optical axes are substantially non-coincident and / or do not lie on a substantially common axis, but may be parallel, oblique, tilted, or combinations thereof relative to one another. Furthermore, as used in this disclosure, the terms "offset" or "spaced apart" or "laterally spaced apart" mean that the focal points from one or more other optical zones or the optical axes of one or more other optical zones may be spaced apart in at least one of the following directions: lateral, vertical, superior, inferior, other angular directions relative to one another, or combinations thereof.

[0167] As used in this disclosure, the terms "suppressed" or "suppress" mean to change, alter or reduce the overlap of one or more foci of an in-focus image and a defocused image on the retina.

[0168] The term "interfere" or "interference" as used in this disclosure with reference to light and / or images means that at least some of the light, at least some of the light rays, one or more focal points from different optical zones interfere, overlap, superimpose, collide, co-occur, are on top of each other, or a combination thereof.

[0169] As used in this disclosure, the terms "light quality" or "image quality" refer to the performance of an Ophthalmic Lens, which may be determined, for example, by root mean square (RMS) reduction in spot size, contrast, subjective visual performance measures such as halo and ghosting, and / or combinations thereof. Other suitable methods of determining the performance of an Ophthalmic Lens may also be used.

[0170] As used in this disclosure, the term "depth of focus" or "extended depth of focus" refers to the distance or range, either in front of and / or behind the image plane, at which one or more images can be positioned / located / focused without substantial degradation of image quality to the system (such as a biological eye or an eye model).

[0171]

[0172] The term "ophthalmic lens" as used in this disclosure is intended to include one or more of a spectacle lens, a contact lens, a film, a sheet, a corneal onlay, a corneal inlay, an intraocular lens, an anterior chamber lens, a lens used to reshape the cornea, and a clip-on feature configured to attach to a spectacle lens.

[0173] As used in this disclosure, the term "ophthalmic lens" is intended to include a lens blank, a finished product, or a substantially finished ophthalmic lens.

[0174] The term "out-of-focus" image or light as used in this disclosure is intended to describe an image that appears blurry to a particular user and has a focal point that is substantially located at a plane other than the retina.

[0175] The term "in focus" image, as used in this disclosure, is intended to describe an image that appears sharp, substantially sharp, or suitably sharp to a particular user.

[0176] As used in this disclosure, the term "optical axis" refers to the optical axis of one or more of a lens, an optical zone, and an optical zone segment.

[0177] As described in more detail below for various embodiments, ophthalmic lenses (e.g., simultaneous vision lenses) are configured to correct one or more combinations of distance vision, intermediate vision, and near vision. In the case of simultaneous vision ophthalmic lenses, the design provides multiple focal points corresponding to multiple optical zones that share a common axis. In such designs, light passing through the ophthalmic lens is shared by multiple optical zones, which can result in overlapping of focused and defocused images from one optical zone and another optical zone, potentially resulting in interference between focused and defocused images. This can result in reduced image quality (e.g., contrast, sharpness) of the focused image.

[0178] Examples of simultaneous vision ophthalmic lenses include bifocal lenses (e.g., contact lenses for presbyopia). Most commonly, such lenses have a central optical zone powered to correct the distance refractive error of presbyopia, surrounded by one or more annular or concentric zones with alternating zones powered to correct the refractive error at near distances. In some other designs, bifocal lenses may be central near lenses, whose designs have a central optical zone powered to correct the near refractive error, surrounded by one or more annular or concentric zones with alternating concentric zones powered to correct the distance refractive error. Typically, the optical zones are configured to be concentric and coaxial, so that the focal points from multiple optical zones can be located on a common axis of symmetry of the ophthalmic lens.

[0179] Considering the example of a progressive lens, when viewing a distant object, the Ophthalmic Lens may provide a focused image resulting from light rays refracted by the distance power optical zone while simultaneously generating an out-of-focus image resulting from light rays refracted by one or more concentric near power optical zones. As a result, the out-of-focus image may interfere with the focused image, reducing image quality (e.g., image contrast and / or sharpness). Similarly, when viewing a near object, the Ophthalmic Lens may provide a focused image resulting from light rays refracted by one or more near power optical zones while simultaneously, or substantially simultaneously, generating an out-of-focus image resulting from light rays refracted by one or more distance power optical zones that interferes with the focused image, reducing image quality (e.g., image contrast and / or sharpness).

[0180] 1A and 1B are schematic diagrams showing plan views of bifocal ophthalmic lenses incorporating a central vision correction zone 101 surrounded by zone(s) 102 powered to create myopic defocus for myopia control. The bifocal soft contact lenses of FIGS. 1A and 1B incorporate a central vision correction zone 101 surrounded by zone(s) powered to create myopic defocus for myopia control. FIG. 1A has a single ring of myopic defocus 102 power (e.g., a relatively more positive power compared to the central vision correction zone 101), while FIG. 1B has two rings (annular ones) of myopic defocus power (102) separated by a zone 101 that corrects distance refractive error. In both lenses, the vision correction zones are coaxial with the myopic defocus zone and incorporate, for example, +2.5D myopic defocus in the annular zone(s).

[0181] 2A and 2B are schematic diagrams illustrating ray tracing of a distant object imaged through the ophthalmic lens of FIGS. 1A and 1B. As shown, light rays pass through the lens and the eye, forming an image of the distant object on the retinal plane. Light rays passing through each zone are represented as a focal point on the image plane for rays passing through vision correction zone 101 and as a defocused, blurred circle on the image plane for rays passing through myopic defocus zone 102. In the example of FIGS. 2A and 2B, the distant object is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3), located approximately 0.5 degrees on either side of OP1.

[0182] In the high-magnification inset of the ray trace formed at and near the image plane, the focal points of OP1, OP2, and OP3 are shown as DF1, DF2, and DF3 at the image plane. Figures 2A and 2B show the extent of interaction of the out-of-focus rays of object points OP1, OP2, and OP3 from the myopic defocus zone with the in-focus images of OP1, OP2, and OP3 produced by the distance power zone(s) in these coaxial-based optical designs.

[0183] 3A and 3B are schematic diagrams of spot diagrams of a focal point DF1 of an object point OP1 formed at an image plane by the ophthalmic lens of FIGS. 1A and 1B configured with coaxial optics. The spot diagrams represent the size of the focal point at the image plane. In some embodiments, the size of the focal point may be expressed as the root mean square (RMS) of the spot radius in microns. A smaller spot size may indicate a sharper focus (good focused image quality). Conversely, a larger spot radius may indicate poor image quality due to, for example, overlap or interference of out-of-focus light from other optical zones at the focal point, resulting in a less sharply focused and / or broadened image.

[0184] In this example, DF1 has RMS sizes of 0.52 μm and 0.4 μm on the image plane for the single-ring and double-ring optical designs, respectively. These values ​​would be similar to those expected for a focal spot produced by a single-vision optical design. However, the image quality of DF1 can be affected by the interaction of rays from neighboring points on the distant object, such as OP2 and OP3. Considering the effect of the defocused rays of OP2 and OP3 from the myopic defocus annular zone of the lens described in Figure 2A on DF1, the RMS spot size of DF1 increases significantly on the image plane from 0.52 μm to 145.2 μm (an overall average of 118.55 μm) for OP2 and OP3, respectively. Similarly, the defocused rays of OP2 and OP3 formed by the myopic defocus annular zone of the lens described in Figure 2B also increase significantly on the image plane from 0.4 μm to 147.05 μm (an overall average of 120.06 μm). Thus, the focal point DF1 of small OP1 considered alone becomes blurred and increases in size due to the overlapping rays of adjacent object points OP2 and OP3 caused by the out-of-focus light created by the myopic defocus zone. In some embodiments, this may imply that the formed image of OP1 is degraded (e.g., substantially degraded) by the out-of-focus rays of adjacent object points created by the coaxial myopic defocus zone.

[0185] In some embodiments, interference of one or more defocused images with a focused image may be suppressed; and / or the visual performance, contrast and / or sharpness of the image, or the range of extended depth of focus may be improved by designing one or more of the optical zones of the ophthalmic device to have optics that are laterally spaced or offset relative to at least one other optical zone.

[0186] Some embodiments may relate to ophthalmic lens designs that reduce overlap of one or more foci of an image due to defocused light. In some embodiments, overlap of one or more foci of an image due to defocused light may be at least partially or completely reduced. In other embodiments, the overlap of one or more images with one or more out-of-focus images can be reduced by about 5% to 100%, about 10% to 100%, about 15% to 100%, about 20% to 100%, about 25% to 100%, about 30% to 100%, about 35% to 100%, about 40% to 100%, about 45% to 100%, about 50% to 100%, about 55% to 100%, about 60% to 100%, about 65% to 100%, about 70% to 100%, about 75% to 100%, about 80% to 100%, about 85% to 100%, or about 90% to 100%.

[0187] In some embodiments, overlap of an image-related focus with one or more out-of-focus image-related focuses can be at least partially or completely suppressed by separating or offsetting the image-related focus or focuses from the out-of-focus image-related focus or focuses, e.g., by about 0.01 to about 4 mm, about 0.01 to about 5 mm, or about 0.01 to about 6 mm. In other embodiments, overlap of an in-focus image with a defocused image(s) can be reduced by separating or offsetting one or more focal points associated with the in-focus image from one or more focal points associated with the one or more defocused image(s), e.g., by about 0.01 to about 3.5 mm, about 0.01 to about 3 mm, about 0.01 to about 2.5 mm, about 0.01 to about 2 mm, about 0.01 to about 1.5 mm, about 0.01 to about 1 mm, about 0.01 to about 0.5 mm, about 0.01 to about 0.1 mm, about 0.1 to about 1.5 mm, about 0.1 to about 2 mm, or about 0.1 to about 2.5 mm. In some embodiments, the separation can be about 0.1 mm, about 0.5 mm, about 1 mm, about 1.5 mm, about 2 mm, or about 2.5 mm.

[0188] Some embodiments described herein relate to ophthalmic lens designs that improve image quality by suppressing overlap of focal points at a given image plane with focal points associated with one or more out-of-focus images or lights, whereby the RMS spot size at the image plane may be reduced by 1 μm or more. In some embodiments, the reduction in RMS spot size radius achieved by suppressing overlap of one or more focal points associated with one or more out-of-focus images with a focal point at a given image plane may be about 1 μm or more. In some embodiments, by suppressing overlap between the focal point at a given image plane and the focal points associated with one or more out-of-focus images, the reduction in RMS spot size radius at the image plane can be about 5 μm, about 10 μm, about 15 μm, about 20 μm, about 25 μm, about 30 μm, about 35 μm, about 40 μm, about 45 μm, about 50 μm, about 55 μm, about 60 μm, about 65 μm, about 70 μm, about 80 μm, about 90 μm, about 100 μm, about 110 μm, about 120 μm, about 130 μm, about 140 μm, about 150 μm, about 160 μm, about 170 μm, about 180 μm, about 190 μm, about 200 μm, or about 250 μm. In some embodiments, by suppressing overlap of the focal point associated with one or more out-of-focus images with the focal point at a given image plane, the reduction in RMS spot size radius can be about 1 μm, about 10 μm, about 25 μm, or about 50 μm.

[0189] In some embodiments, the first focal point may be on a first axis at a first distance from the ophthalmic lens, and the second focal point may be at a second distance from the ophthalmic lens, the second distance being different from the first distance and offset from the first axis.

[0190] In some embodiments, overlap of image-related foci at a given image plane due to foci related to out-of-focus images can be substantially reduced by designing an ophthalmic lens having multiple optical zones or segments such that the optical axes for the multiple optical zones or segments are different from one another and the multiple optical zones or segments do not share a common axis. In some embodiments, the optical axes of the multiple optical zones or segments may not lie on a common axis. In some embodiments, some of the optical axes of the multiple optical zones or segments may lie on a common axis. In some embodiments, the optical axes of the multiple optical zones associated with a first power may lie on a first optical axis, and the optical axes of the multiple optical zones or segments associated with a second power may lie on a second optical axis. In some embodiments, the optical axes of the multiple optical zones associated with a first power may lie on a first optical axis, and the optical axes of the multiple optical zones or segments associated with a second power may lie on corresponding axes (e.g., a second optical axis, a third optical axis, a fourth optical axis, a fifth optical axis, etc.) that are different from the first axis.

[0191] In some embodiments, the optical axes of multiple optical zones associated with a first power may lie on the first optical axis, the optical axes of multiple optical zones or segments associated with a second power may lie on the second optical axis, the optical axes of multiple optical zones or segments associated with a third power may lie on the third optical axis, and so on.

[0192] In some embodiments, by configuring an ophthalmic lens to have multiple optical zones or segments, overlap of foci associated with images at a predetermined image plane due to foci or light rays associated with defocused images may be reduced. One or more optical zones or segments may have an optical axis, or one or more optical zones or segments may not share a common axis (e.g., may have different optical axes). Thus, foci resulting from one or more optical zones or segments may be offset relative to the optical axis and foci from other optical zones or segments of the ophthalmic lens. In some embodiments, the offset of the foci resulting from light directed through one or more optical zones or segments relative to foci resulting from light directed through other optical zones or segments of the ophthalmic lens results in a correction or change of the defocused or defocused light with the image at the predetermined image plane, thereby improving the quality (e.g., contrast and / or sharpness) of the retinal image and / or providing an extended depth of focus.

[0193] In some embodiments, a defocus resulting from light directed through one or more Optical Zones or segments relative to a focus resulting from light directed through other Optical Zones and / or segments of an Ophthalmic Lens may be addressed by one or more light separation means (e.g., laterally spaced optics). In some embodiments, a light separation means (e.g., laterally spaced optics) for defocusing a focus resulting from light directed through one or more Optical Zones or segments relative to a focus resulting from light directed through other Optical Zones and / or segments on an Ophthalmic Lens may include utilizing one or more optical surfaces having two or more optical elements (e.g., spherical, elliptical, conical, aspherical, or other suitable elements including aspherical torus elements such as rectilinear, conical, etc.), where the two or more optical elements are positioned, shifted, rotated, tilted, or offset relative to one another such that at least a substantial portion or at least a portion of the two or more optical elements do not share a common optical axis. In some embodiments, a light separation means (e.g., laterally spaced optics) for shifting the focus resulting from light directed through one or more optical zones or segments relative to the focus resulting from light directed through other optical zones and / or segments on an ophthalmic lens may include utilizing an optical surface having two or more optical elements (e.g., spherical, elliptical, conical, aspherical, or other suitable elements, including aspherical torus elements such as rectilinear, conical, etc.), where the two or more optical elements may have different radii. The optical surface of an ophthalmic lens may be the outer surface, the inner surface, or both surfaces of the lens.

[0194] In some embodiments, the optical zone having a first power may be located at or substantially at the center of the lens, and the optical zone having a second power may surround the central optical zone as concentric or substantially concentric zones. In some embodiments, the optical zone having a first power may occupy a section, meridian, or portion of the lens, and the optical zone having a second power may occupy the remaining section, meridian, or portion of the lens (e.g., a split ophthalmic lens). In some embodiments, the optical zone having a first power may occupy multiple portions of the lens and may alternate with the optical zone having a second power (e.g., multi-ring). In some embodiments, the first power may be constant or may vary in different portions of the first optical zone. In some embodiments, the ophthalmic lens may include a third optical zone having a third power. In some embodiments, the third optical zone may be one or more concentric zones adjacent to (e.g., surrounding) the central optical zone. In some embodiments, the third optical zone can be a section, meridian, or portion of the lens other than the section, meridian, or portion of the lens occupied by the first optical zone and the second optical zone.

[0195] In some embodiments, for example, in a split ophthalmic lens, the optic having a first power may be a first optical zone, and the first axis may be the optical axis of the first optical zone. In some embodiments, the optic having a second power may be a second optical zone. The second optical zone may have a second axis, and the second axis may be offset or laterally spaced from the first axis.In some embodiments, the separation of the centers of the two optical elements relative to the center of the ophthalmic lens is in the range of about 0.01 to about 20 mm (e.g., about 0.01 mm, about 0.02 mm, about 0.03 mm, about 0.04 mm, about 0.05 mm, about 0.06 mm, about 0.07 mm, about 0.08 mm, about 0.09 mm, about 0.1 mm, about 0.15 mm, about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, about 0.6 mm, about 0.65 mm, Approximately 0.7mm, approximately 0.75mm, approximately 0.8mm, approximately 0.85mm, approximately 0.9mm, approximately 0.95mm, approximately 1mm, approximately 1.25mm, approximately 1.5mm, approximately 1.75mm, approximately 2mm, approximately 2.25mm, approximately 2.5mm, approximately 2.75mm, approximately 3mm, approximately 3.25 mm, approximately 3.5mm, approximately 3.75mm, approximately 4mm, approximately 4.25mm, approximately 4.5mm, approximately 4.75mm, approximately 5mm, approximately 5.25mm, approximately 5.5mm, approximately 5.75mm, approximately 6mm, approximately 6.25mm, approximately 6.5mm, approximately 6.75mm, approximately 7mm, approximately 7.2 5mm, approximately 7.5mm, approximately 7.75mm, approximately 8mm, approximately 8.25mm, approximately 8.5mm, approximately 8.75mm, approximately 9mm, approximately 9.25mm, approximately 9.5mm, approximately 9.75mm, approximately 10mm, approximately 10.25mm, approximately 10.5mm, approximately 10.75mm, approximately 11m m, approx. 11.25 mm, approx. 11.5 mm, approx. 11.75 mm, approx. 12 mm, approx. 12.25 mm, approx. 12.5 mm, approx. 12.75 mm, approx. The spacing may be about 5 mm, about 14.75 mm, about 15 mm, about 15.25 mm, about 15.5 mm, about 15.75 mm, about 16 mm, about 16.25 mm, about 16.5 mm, about 16.75 mm, about 17 mm, about 17.25 mm, about 17.5 mm, about 17.75 mm, about 18 mm, about 18.25 mm, about 18.5 mm, about 18.75 mm, about 19 mm, about 19.25 mm, about 19.5 mm, about 19.75 mm, about 20 mm, about 20.25 mm, about 20.5 mm, about 20.75 mm, or about 21 mm. In some embodiments, the spacing may be about 10 mm for eyeglass lenses and about 2 mm for contact lenses.In some embodiments, the spacing may be about 9 mm, about 9.25 mm, about 9.5 mm, about 9.75 mm, about 10 mm, about 10.25 mm, about 10.5 mm, about 10.75 mm, or about 11 mm for eyeglass lenses, and about 1 mm, about 1.25 mm, about 1.5 mm, about 1.75 mm, about 2 mm, about 2.25 mm, about 2.5 mm, about 2.75 mm, or about 3 mm for contact lenses.

[0196] In some embodiments, a shift in focus resulting from light directed through one or more optical zones or segments relative to a focus resulting from light directed through other optical zones and / or segments of an Ophthalmic Lens that employs a light separation means (e.g., laterally spaced optics) can result in prismatic power that a wearer of the Ophthalmic Lens may perceive as shifting objects during use. In some embodiments, it may be desirable to maintain and reduce image (e.g., foci) separation, which results in a trade-off between low prismatic power (reduced image separation) and high image quality of vision within the lens (increased image separation).

[0197] In some embodiments, the optical zone having a first power can be a first optical zone, and the first axis can be the optical axis of the first optical zone. In some embodiments, the optical zone having a second power can be a second optical zone. The second optical zone can have a second axis, and the second axis can be offset or laterally spaced from the first axis.

[0198] In some embodiments, the second optical zone may be configured such that, in use on an eye, light passing through the second optical zone is refracted to multiple second foci, the multiple second foci being on corresponding one or more of multiple second axes associated with the one or more second optical zones, and the multiple second axes being offset from the first axis. In some embodiments, the second optical zone may have multiple foci. In some embodiments, the second optical zone may be configured such that, in use on an eye, light passing through the second optical zone is refracted to multiple (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, or 16) foci rather than on the first axis. In some embodiments, light passing through the second optical zone may be refracted to 3, 3, 4, or 5 foci rather than on the first axis. In some embodiments, this configuration may be useful for ophthalmic lenses used to address myopia.

[0199] In some embodiments, the ophthalmic lens may have a first optical zone having a first power, a second optical zone having a constant (or varying) power, a third optical zone having a constant (or varying) power, etc.

[0200] In some embodiments, the offset of the first axis from the second axis can result in a prismatic power in the Ophthalmic Lens. In some embodiments, the prismatic power resulting from the offset of the first axis from the second axis can be from about 0.01Δ diopters to about 15Δ diopters (e.g., about 0.01Δ, about 0.015Δ, about 0.02Δ, about 0.025Δ, about 0.05Δ, about 0.075Δ, about 0.1Δ, about 0.125Δ, about 0.15Δ, about 0.175Δ, about 0.2Δ, about 0.25Δ, about 0.3Δ, about 0.35Δ, about 0.4Δ, about 0.5Δ, about 0.6Δ, about 0.7Δ, about 0.8Δ, about 0.9Δ, about 10Δ, about 11Δ, about 12Δ, about 13Δ, about 14Δ, about 15Δ, about 16Δ, about 17Δ, about 18Δ, about 19Δ, about 20Δ, about 21Δ, about 22Δ, about 23Δ, about 24Δ, about 25Δ, about 26Δ, about 27Δ, about 28Δ, about 29Δ, about 30Δ, about 31Δ, about 32Δ, about 33Δ, about 34Δ, about 35Δ, about 36Δ, about 37Δ, about 38Δ, about 39Δ, about 40Δ, about 41Δ, about 42Δ, about 43Δ, about 44Δ, about 45Δ, about 46Δ, about 47Δ, about 48Δ, about 49Δ, about 50Δ, about 51Δ, about 52Δ, about 53Δ, about 54Δ, about 55 .4△, approx. 0.45△, approx. 0.5△, approx. 0.6△, approx. 0.7△, approx. 0.8△, approx. 0.9△, approx. 1△, approx. 1.25△, approx. 1.5△, approx. 1.75△, approx. 2△, approx. 2.25△, approx. 2.5△, approx. 2.75△, approx. 3△, approx. 3.25△, approx. 3.5△, approx. 3.75△, approx. 4△, approx. 4.25△, approx. 4.5△, approx. 4.75△, approx. 5△, approx. 5.25△, approx. 5.5△, approx. 5.75△, approx. 6△, approx. 6.25△, approx. 6 .5△, approximately 6.75△, approximately 7△, approximately 7.25△, approximately 7.5△, approximately 7.75△, approximately 8△, approximately 8.1△, approximately 8.2△, approximately 8.3△, approximately 8.4△, approximately 8.5△, approximately 8.6△, approximately 8.7△, approximately 8.8△, approximately 8.9△, approximately 9△, approximately 9.1△, approximately 9.2△, approximately 9.3△, approximately 9.4△, approximately 9.5△, approximately 9.6△, approximately 9.7△, approximately 9.8△, approximately 9.9△, approximately 10△, approximately 10.1△, approximately 10.2△, approximately 10 In some embodiments, the prismatic power resulting from the offset of the first axis from the second axis may be about 1Δ, about 2Δ, about 3Δ, about 4Δ, about 5Δ, about 6Δ, about 7Δ, about 8Δ, about 9Δ, about 10Δ, about 11Δ, about 11.25Δ, about 11.5Δ, about 11.75Δ, about 12Δ, about 12.25Δ, about 12.5Δ, about 12.75Δ, about 13Δ, about 13.25Δ, about 13.5Δ, about 13.75Δ, about 14Δ, about 14.25Δ, about 14.5Δ, about 14.75Δ, or about 15Δ. In some embodiments, the prismatic power resulting from the offset of the first axis from the second axis may be about 1Δ, about 2Δ, about 3Δ, about 4Δ, about 5Δ, about 6Δ, about 7Δ, about 8Δ, or about 9Δ.

[0201] In some embodiments, the one or more Optical Zones having a first power may occupy 50% or more (e.g., about 55%, about 60%, about 65%, about 70%, about 75%, about 80%, about 85%, or about 90%) of the surface area of ​​the Optical Zone of the Ophthalmic Lens (e.g., the surface area of ​​the outer or inner surface of the lens). In some embodiments, the one or more Optical Zones having a first power may occupy 50% or less (e.g., about 45%, about 40%, about 35%, about 30%, about 25%, or about 20%) of the surface area of ​​the Optical Zone of the Ophthalmic Lens (e.g., the surface area of ​​the outer or inner surface of the lens). In some embodiments, the one or more Optical Zones having a first power may occupy about 60% (e.g., about 55%, about 56%, about 57%, about 58%, about 59%, about 60%, about 61%, about 62%, about 63%, about 64%, or about 65%) of the surface area of ​​the Optical Zone of the Ophthalmic Lens (e.g., the surface area of ​​the outer or inner surface of the lens). In some embodiments, the one or more Optical Zones having a first power may occupy about 40% (e.g., about 35%, about 36%, about 37%, about 38%, about 39%, about 40%, about 41%, about 42%, about 43%, about 44%, or about 45%) of the surface area of ​​the Optical Zone of the Ophthalmic Lens (e.g., the surface area of ​​the outer or inner surface of the lens). In some embodiments, the one or more Optical Zones having a first power may occupy about 75% (e.g., about 55%, about 60%, about 65%, about 70%, or about 75%) of the surface area of ​​the Optical Zone of the Ophthalmic Lens (e.g., the surface area of ​​the outer or inner surface of the lens). In some embodiments, the one or more Optical Zones having a first power may occupy about 10% or more (e.g., about 15%, about 20%, about 25%, about 30%, about 35%, about 40%, or about 45%) of the surface area of ​​the Optical Zone of the Ophthalmic Lens (e.g., the surface area of ​​the outer or inner surface of the lens).

[0202] In some embodiments, an optical zone having a first power may be defined at least in part by a spherical surface having a first radius, and / or an optical zone having a second power may be defined at least in part by a spherical surface having a second radius that is different from the first radius. In some embodiments, an optical zone having a first power may be defined at least in part by a spherical surface having a first radius, and / or an optical zone having a second power may be defined at least in part by a spherical surface having a second radius that is smaller than the first radius. In some embodiments, an optical zone having a first power may be defined at least in part by a spherical surface having a first radius, and / or an optical zone having a second power may be defined at least in part by a spherical surface having a second radius that is larger than the first radius.

[0203] In some embodiments, the one or more optical zones having the second power may have one or more spherical surfaces with one or more radii that are different from the one or more optical zones having the first power and first radii.

[0204] In some embodiments (e.g., in the case of contact lenses), the first optical zone may be substantially circular in shape and may have a diameter of about 3 mm (e.g., in some embodiments, the diameter may be about 2 mm, about 2.5 mm, about 3 mm, about 3.5 mm, about 4 mm, about 2-4 mm, about 2-3 mm, about 3-4 mm, about 4 mm or less, about 3.5 mm or less, and / or about 3 mm or less). In some embodiments, the second optical zone may be substantially annular in shape and may have an inner diameter of about 3 mm (e.g., in some embodiments, the inner diameter may be about 2 mm, about 2.5 mm, about 3 mm, about 3.5 mm, about 4 mm, about 2-4 mm, about 2-3 mm, about 3-4 mm, about 4 mm or less, about 3.5 mm or less, and / or about 3 mm or less), and may have an outer diameter of about 7 mm (e.g., in some embodiments, the outer diameter may be about 5 mm, about 5.5 mm, about 6 mm, about 6.5 mm, about 7 mm, about 7.5 mm, about 8 mm, about 5-8 mm, about 6-7 mm, about 6-8 mm, about 8 mm or less, about 7.5 mm or less, and / or about 7 mm or less). In some embodiments, the first optical zone may be substantially circular in shape and the second optical zone may be substantially annular in shape, and the inner diameter of the second optical zone may be substantially equal to the diameter of the first optical zone.

[0205] In some embodiments (e.g., in the case of eyeglass lenses), the first optical zone may be substantially circular and may have a diameter of about 10 mm (e.g., in some embodiments, the diameter may be about 7 mm, about 7.5 mm, about 8 mm, about 8.5 mm, about 9 mm, about 9.5 mm, about 10 mm, about 10.5 mm, about 11 mm, about 11.5 mm, about 12 mm, about 12.5 mm, about 13 mm, about 14 mm, about 15 mm, about 16 mm, about 17 mm, about 18 mm, about 19 mm, about 20 mm, about 21 mm, about 22 mm, about 23 mm, about 24 mm, about 25 mm, about 26 mm, about 27 mm, about 28 mm, about 29 mm, about 30 mm, about 31 mm, about 32 mm, about 33 mm, about 34 mm, about 35 mm, about 36 mm, about 37 mm, about 38 mm, about 39 mm, about 40 mm, about 41 mm, about 42 mm, about 43 mm, about 44 mm, about 45 mm, about 46 mm, about 47 mm, about 48 mm, about 49 mm, about 50 mm, about 51 mm, about 52 mm, about 53 mm, about 54 mm, about 55 mm, about 56 mm, about 57 mm, about 58 mm, about 59 mm, about 60 mm, about 61 mm, about 62 mm, about 63 mm, about 64 mm, about 65 mm, about 66 mm, about 67 mm, about 68 mm, about 69 mm, about 70 mm, about 71 mm, about 72 mm, about 73 mm, about 74 mm, about 75 mm, about 76 mm, The diameter may be 3.5 mm, about 14 mm, about 14.5 mm, about 15 mm, about 15.5 mm, about 16 mm, about 16.5 mm, about 17 mm, about 17.5 mm, about 18 mm, about 18.5 mm, about 19 mm, about 19.5 mm, about 20 mm, about 8-10 mm, about 10-12 mm, about 9-11 mm, about 12-14 mm, about 10 mm or less, about 12.65 mm or less, and / or about 15 mm or less). In some embodiments, the second optical zone can be substantially annular in shape and have an inner diameter of about 10 mm (e.g., in some embodiments, the inner diameter can be about 7 mm, about 7.5 mm, about 8 mm, about 8.5 mm, about 9 mm, about 9.5 mm, about 10 mm, about 10.5 mm, about 11 mm, about 11.5 mm, about 12 mm, about 12.5 mm, about 13 mm, about 7-9 mm, about 8-10 mm, about 10-12 mm, about 10 mm or less, about 11 mm or less, and / or about 12 mm or less). It may have an outer diameter of about 15 mm (e.g., in some embodiments, the outer diameter may be about 12 mm, about 12.5 mm, about 13 mm, about 13.5 mm, about 14 mm, about 14.5 mm, about 15 mm, about 15.5 mm, about 16 mm, about 16.5 mm, about 17 mm, about 17.5 mm, about 18 mm, about 18.5 mm, about 19 mm, about 19.5 mm, about 20 mm, about 12-15 mm, about 13-16 mm, about 15-18 mm, about 15 mm or less, about 17.5 mm or less, and / or about 20 mm or less). In some embodiments, the first optical zone may be substantially circular in shape and the second optical zone may be substantially annular in shape, and the inner diameter of the second optical zone may be substantially equal to the diameter of the first optical zone.

[0206] The teachings of the present disclosure can be applied to ophthalmic lenses for presbyopia and / or myopia. The ophthalmic lenses described herein may include one or more of spectacle lenses, contact lenses, corneal onlays, corneal inlays, films or sheets applied to lenses, clip-on lenses, and intraocular lenses. For example, a bifocal ophthalmic lens (e.g., a contact lens or spectacle lens) may be configured to have one or more optical zones with a first power for correcting either distance vision, intermediate vision, or near vision, and one or more optical zones with a second power greater than the first power. In some embodiments, the optical zones may be configured such that, when viewing an object, a focal point resulting from light rays (or at least a portion of the light rays) refracted from one or more optical zones having a second power is offset from a focal point resulting from light rays (or at least a portion of the light rays) refracted from one or more optical zones having a first power, thereby improving image quality associated with the first image (e.g., the amount of overlap of light rays from one or more optical zones having a second power may be reduced) and / or providing an extended depth of focus. In some embodiments, when viewing a distant object, light directed through one or more optical zones having a first power may be focused at a first focal point that is offset from light directed through one or more optical zones having a second power, such that the focal point resulting from light directed through the optical zones having the first power may be minimally interfered with (e.g., less, substantially less, and / or not interfered with) by the focal point resulting from light directed through the optical zones having the second power. In some embodiments, the one or more optical zones having a first power and the one or more optical zones having a second power have independent optical axes that are offset relative to one another, with partial or reduced overlap of the resulting images.In some embodiments, during distance and / or near vision, interference between out-of-focus images from one or more optical zones having a second power and images from one or more optical zones having a first power may be suppressed by using an optical surface having two or more optical elements (e.g., spherical, elliptical, conical, aspherical, or other suitable elements, including aspherical torus elements such as rectilinear, conical, etc.), which are positioned, shifted, tilted, rotated, or offset relative to one another so that they do not share a common optical axis.

[0207] 4A and 4B are schematic diagrams illustrating a plan view of an ophthalmic lens (e.g., a contact lens) incorporating a central zone 401 having a first power surrounded by zones 402 powered to generate myopic defocus relative to zone 401 for myopia suppression, according to certain embodiments. As shown, the central zone 401 and the surrounding myopic defocus power zones 402 are configured to be non-coaxial, such that the foci generated by the myopic defocus zones are spaced laterally apart from each other and away from the axis along which the distance focus is generated. FIG. 4A has a single ring of myopic defocus power, while FIG. 4B has two rings of myopic defocus power spaced apart by a zone having the first power. While both lenses include a zone having the first power on the axis, the foci of the myopic defocus zones are configured to be spaced laterally apart, for example, by 0.5 mm in FIG. 4A and 0.6 mm in FIG. 4B. In this example, both lens types incorporate +2.5D myopic defocus in an annular arrangement. While Figures 4A and 4B show continuous peripheral zones, discontinuous or combinations of continuous and discontinuous peripheral zones are also contemplated. While Figures 4A and 4B show concentric zones, other shapes are contemplated, including other suitable elements, such as spherical, elliptical, conical, aspherical, or non-spherical torus elements, such as rectilinear, conical, etc. While Figures 4A and 4B show concentric zones, substantially concentric and / or partially concentric zones are also contemplated.

[0208] 5A and 5B are schematic diagrams illustrating ray tracing of a distant object imaged through the ophthalmic lens of FIGS. 4A and 4B according to certain embodiments. Rays passing through each zone are represented as a focal point on the image plane for rays passing through the first power zone and as a defocused blurred circle on the image plane for rays passing through the myopic defocus zone. In FIGS. 5A and 5B, the distant object is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) located 0.5 degrees on either side of OP1.

[0209] Figures 5A and 5B also show high-magnification insets of ray traces formed at and near the retinal plane. The insets show the focal points of OP1, OP2, and OP3 as DF1, DF2, and DF3 at the image plane. Also, defocused rays of OP1, OP2, and OP3 that pass through the myopic defocus zone constitute the remaining rays located at the image plane. Figures 5A and 5B show the extent of interaction of defocused rays of object points OP1, OP2, and OP3 from the myopic defocus zone with the images of OP1, OP2, and OP3 from the distance power zone(s) for these lenses configured to laterally space the focal points.

[0210] 6A and 6B are schematic diagrams illustrating the spot diagrams and RMS values ​​of the focal point DF1 of the object point OP1 formed on the retinal plane by the ophthalmic lenses of FIGS. 4A and 4B according to certain embodiments based on an optical design that creates lateral separation of the focal points. DF1 has RMS values ​​of 0.46 μm and 0.41 μm for the single-ring and double-ring optical designs, respectively. These values ​​would be similar to those expected for the focal point of a single-vision optical design. However, unlike the example of an ophthalmic lens configured with a coaxial optical system such as FIGS. 2A and 2B, there may be no interaction from the defocused rays of object points OP2 and OP3 formed by the myopic defocus zone (e.g., RMS value = 0). Because the lens design has laterally separated foci, the RMS spot size of the focal point DF1 is not increased by the overlap of defocused rays from adjacent object points, and the overall average RMS values ​​remain relatively small at 0.46 μm and 0.41 μm. Similarly, DF2 and DF3 are not affected by defocused light from adjacent object points. Therefore, the laterally spaced optical system described in this example exhibits improved sharpness and higher image quality than the coaxial-based design of Figures 2A and 2B.

[0211] 7A and 7B are schematic diagrams illustrating a plan view of an ophthalmic lens (e.g., a spectacle lens) configured for myopia suppression and incorporating a central zone 701 having a first power surrounded by multiple annular zones 702 with alternating powers to generate myopic defocus, according to certain embodiments. The lens illustrated in FIG. 7A has a configuration in which the zone 701 having the first power and the myopic defocus zone are coaxial, and the myopic defocus annular zone is configured to incorporate a myopic defocus of +2.5D. The lens illustrated in FIG. 7B has an optical system in which the zone 701 having the first power and the myopic defocus zone 702 are laterally spaced apart, and the myopic defocus annular zone is configured to incorporate a myopic defocus of +2.5D. While FIGS. 7A and 7B illustrate continuous peripheral zones, discontinuous or combinations of continuous and discontinuous peripheral zones are also contemplated. 7A and 7B show concentric zones, other suitable elements are contemplated, including other shapes, e.g., spherical, ellipsoidal, conical, non-spherical, or non-spherical torus elements such as rectilinear, conical, etc. While Figures 7A and 7B show concentric zones, substantially concentric and / or partially concentric zones are also contemplated.

[0212] 8A and 8B are schematic diagrams illustrating ray tracing of a distant object imaged through the ophthalmic lens of FIGS. 7A and 7B, according to certain embodiments. Rays passing through each zone are represented as a focal point on the retina for rays passing through the distance power zone and as a defocused blurred circle on the image plane for rays passing through the myopic defocus zone. The distant object is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3), located 0.45 degrees on either side of OP1.

[0213] Figures 8A and 8B also include high-magnification insets of ray traces formed at and near the retinal plane. The insets show the focal points of distant object points OP1, OP2, and OP3 at the image plane as DF1, DF2, and DF3. The defocused rays of OP1, OP2, and OP3 that pass through the myopic defocus zone constitute the remaining rays located at the image plane. Figures 8A and 8B show the extent of interaction of the defocused rays of object points OP1, OP2, and OP3 from the myopic defocus zone with the focused images of OP1, OP2, and OP3 from the first power zone for these lenses, configured with either a coaxial optical design (Figure 8A) or a laterally spaced-foci optical design (Figure 8B).

[0214] 9A and 9B are schematic diagrams illustrating the spot diagram and RMS value of the focal point DF1 of object point OP1 formed on the retinal surface by the ophthalmic lens of FIGS. 7A and 7B according to certain embodiments. FIG. 9A illustrates the spot diagram and RMS value of the focal point F1 of object point OP1 formed on the retinal surface by the myopia suppression lens of FIG. 8a based on a coaxial optical design. DF1 has an RMS value of 0.38 μm, which is comparable to what would be expected for the focal point of a single-vision optical design. However, the image quality of DF1 may be affected by the interaction of rays from neighboring points on distant objects, such as OP2 and OP3. Considering the influence of the defocused rays of OP2 and OP3 from the myopic defocus annular zone of the lens described in FIG. 8A on F1, the RMS spot size of DF1 increases significantly from 0.38 μm to 126.39 μm (overall average of 103.19 μm) for OP2 and OP3, respectively. Thus, the defined focal point F1 of OP1 considered alone is blurred and enlarged in size due to the influence of the myopic defocus rays of the neighboring object points OP2 and OP3 formed by the myopic defocus zone. This indicates that the image formation of OP1 can be degraded by the defocused rays of the neighboring object points generated by the coaxial myopic defocus zone.

[0215] Figure 9B shows the spot diagram and RMS value of the focus DF1 of object point OP1 formed at the retinal plane by the myopia suppression lens of Figure 8B, which is based on an optical design that creates lateral separation of foci. DF1 has an RMS value of 0.36 μm, which is similar to what would be expected for a focus of a single-vision optical design, as in Figure 9A. However, unlike the cases of lenses configured with coaxial optics such as Figures 2A and 8A, contact lenses, and eyeglasses with coaxial optical designs, there appears to be no interaction from the defocused rays of object points OP2 and OP3 formed by the myopic defocus zone (RMS value = 0.0). In the example of Figure 9B, the focus DF1 does not increase the RMS spot size due to overlapping defocused rays from adjacent object points, so the overall average RMS value remains small at 0.36 μm for this eyeglass lens configured with laterally separated foci. Similarly, F2 and F3 are not affected by defocused rays from adjacent object points. Thus, the laterally spaced optical system described in this exemplary embodiment exhibits improved sharpness and / or higher image quality than coaxial-based designs.

[0216] 10A and 10B are schematic diagrams illustrating plan views of ophthalmic lenses (e.g., presbyopic bifocal soft contact lenses) incorporating a central vision correction zone surrounded by zone(s) powered to correct the presbyopic's near vision, according to certain embodiments. Figure 10A illustrates a plan view of a presbyopic bifocal soft contact lens incorporating a central distance vision correction zone 1001 surrounded by a single zone 1002 powered to correct the presbyopic's near vision. The distance and near correction zones are configured coaxially, and a surrounding annular zone may incorporate a +2.5D near add power.

[0217] FIG. 10B shows a plan view of a soft bifocal contact lens incorporating a central distance vision correction zone 1011 surrounded by a zone 1012 powered to correct near vision for a presbyope. The distance zone and peripheral near power zones may be configured with laterally spaced optics such that the foci produced by the zones are laterally spaced from each other and from the axis on which the distance focus is produced. The lens of FIG. 10B may be configured such that the focus from the distance zone is formed on axis, while the focus formed by the near vision zone is laterally spaced 0.5 mm from the optical axis. In this exemplary embodiment, the near annular zone does not focus light to a single focus, but rather forms a continuous ring of foci surrounding and spaced from the optical axis where the distance focus is located. Thus, the near focus ring is laterally spaced 0.5 mm from the optical axis. The bifocal lens in this example incorporates a near add power of +2.50D. While Figure 10B depicts a continuous peripheral zone, discontinuous or a combination of continuous and discontinuous peripheral zones are also contemplated. While Figures 10A and 10B depict concentric zones, other shapes are contemplated, including other suitable elements, e.g., spheres, ellipses, cones, non-spheres, or non-spherical torus elements such as rectilinear cones. While Figures 10A and 10B depict concentric zones, substantially concentric and / or partially concentric zones are also contemplated.

[0218] 11A and 11B are schematic diagrams showing ray tracing of a distant object and a near object imaged through the ophthalmic lens of FIGS. 10A and 10B.

[0219] FIG. 11A shows a ray trace of a distant object imaged through the contact lens of FIG. 10A. Light rays pass through the lens and the eye, forming an image of the distant object on the retinal plane. Rays passing through each zone are represented as a focal point on the retina for rays passing through the distance power zone and as a defocused, blurred circle on the image plane for rays passing through the near addition zone. The distant object is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3), located 0.5 degrees on either side of OP1 for the distant object and 0.15 degrees on either side of OP1 for the near object.

[0220] FIG. 11A also shows high-magnification insets of ray tracings formed at the retinal plane when a distant object is in focus (distance vision) and when a near image is in focus (near vision). FIG. 11A shows that the focal points of distant objects OP1, OP2, and OP3 are designated DF1, DF2, and DF3 at the image plane, and that out-of-focus rays of OP1, OP2, and OP3 that pass through the near addition zone constitute the remaining rays located at the image plane. FIG. 11A also shows that the focal points of near objects OP1, OP2, and OP3 are designated NF1, NF2, and NF3 at the image plane. Out-of-focus rays of OP1, OP2, and OP3 that pass through the distance vision zone constitute the remaining rays located at the image plane. FIG. 11A shows the extent of interaction of defocused rays of object points OP1, OP2, and OP3 with the images of OP1, OP2, and OP3 produced by the distance or near power zone(s) in these coaxial-based optical designs.

[0221] FIG. 11B shows a cross-section of a ray trace of a distant object imaged through the contact lens of FIG. 10B. Light rays pass through the lens and the eye, forming an image of the distant object on the retinal plane. Rays passing through each zone are represented as a focal point on the retina for rays passing through the distance power zone and as a defocused, blurred circle on the image plane for rays passing through the near addition zone. The distant object may be further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2, OP3), located 0.5 degrees on either side of OP1 for the distant object and 0.15 degrees on either side of OP1 for the near object.

[0222] FIG. 11B also shows high-magnification insets of ray tracings formed at the retinal plane when a distant object is in focus (distance vision) and when a near image is in focus (near vision). FIG. 11B illustrates that the focal points of distant objects OP1, OP2, and OP3 are designated DF1, DF2, and DF3 at the image plane, and that out-of-focus rays of OP1, OP2, and OP3 that pass through the near addition zone constitute the remaining rays located at the image plane. This example further illustrates that the focal points of near objects OP1, OP2, and OP3 are designated NF1, NF2, and NF3 at the image plane, and that out-of-focus rays of OP1, OP2, and OP3 that pass through the distance vision zone constitute the remaining rays located at the image plane. FIG. 11B shows the extent of interaction of defocused rays of object points OP1, OP2, and OP3 with the focused images of OP1, OP2, and OP3 produced by the distance or near power zone(s) for these laterally spaced optical designs.

[0223] 12A, 12B, 12C and 12D are schematic diagrams showing spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIGS. 10A and 10B.

[0224] FIG. 12A shows the spot diagram and RMS value of the focal spot DF1 of a distant object point OP1 formed on the retinal surface by the progressive contact lens of FIG. 11A. DF1 has an RMS size of 0.71 μm. These values ​​are similar to the focal spot produced by a single-vision optical design at this aperture size. However, the image quality of DF1 may be affected by the interaction of rays from neighboring points on the distant object, such as OP2 and OP3. When considering the influence of the defocused rays of OP2 and OP3 on D-F1 from the near power annular zone of the lens described in FIG. 10A, the RMS spot size of DF1 increases significantly from 0.71 μm to 110.99 μm (an overall average of 90.62 μm) for OP2 and OP3, respectively. Thus, the focal spot DF1 of OP1, considered alone, is blurred and enlarged in size by the net effect of the defocused rays of the neighboring object points OP2 and OP3 formed by the near power zone. In some embodiments, this means that the formed image of OP1 is degraded by out-of-focus rays of adjacent object points produced by the coaxial near power zone.

[0225] FIG. 12B shows the spot diagram and RMS values ​​of the focal spot NF1 of the near object point OP1 formed on the retinal surface by the progressive contact lens of FIG. 11A. NF-1 has an RMS size of 0.2 μm. These values ​​are similar to those expected for a focal spot produced by a monofocal optical design at this aperture size. However, the image quality of NF1 can be affected by the interaction of rays from adjacent points on the near object, such as OP2 and OP3. When considering the influence of the defocused rays of OP2 and OP3 on N-F1 from the distance power central zone of the lens described in FIG. 10A, the RMS spot size of N-F1 increases significantly from 0.2 μm to 44.15 μm (an overall average of 36.05 μm) for OP2 and OP3, respectively. Thus, the focal spot N-F1 of OP1, considered alone, is blurred and enlarged in size due to the influence of the defocused rays of the adjacent near object points OP2 and OP3 formed by the distance power zone. In some embodiments, this means that the near image formed by OP1 is degraded by out-of-focus rays of adjacent object points produced by the coaxial distance power zone.

[0226] FIG. 12C shows the spot diagram and RMS value of the focal point DF1 of the distant object point OP1 formed at the retinal surface by the bifocal contact lens of FIG. 11B with laterally spaced optics for the distance and near optical zones. DF1 has an RMS size of 0.7 μm. These values ​​are similar to those expected for foci generated by a single-vision optical design. However, unlike the case of a lens configured with coaxial optics such as FIG. 10A, there is no interaction from the defocused rays of object points OP2 and OP3 formed by the near zone (RMS value = 0). Because the defocused rays from adjacent object points do not overlap with the focal point DF1 to increase its RMS spot size, the overall average RMS value remains small at 0.7 μm for the lens configured with laterally spaced foci. Similarly, DF2 and DF3 are not affected by the defocused rays from adjacent object points. Thus, the laterally spaced optical system described herein exhibits improved sharpness and / or higher image quality than the coaxial-based design of FIG. 10A.

[0227] FIG. 12D shows the spot diagram and RMS value of the near focus N-F1 of the near object point OP1 formed on the retinal surface by the bifocal contact lens of FIG. 11B. NF1 has an RMS size of 0.05 μm. However, unlike the case of a lens configured with a coaxial optical system such as FIG. 10A, there may be no interaction from defocused rays of near object points OP2 and OP3 formed by the distance zone (RMS value = 0.0). Because the focus NF1 does not increase its RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 0.05 μm for a lens configured with a laterally spaced near focus ring. Similarly, NF2 and NF3 are not affected by defocused rays from adjacent object points. Therefore, the laterally spaced optical system described herein exhibits significantly improved sharpness and / or higher image quality than the coaxial-based design of FIG. 10A.

[0228] FIG. 13 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a soft bifocal contact lens) including laterally spaced optics for the distance and near optical zones, according to certain embodiments. FIG. 13 illustrates a plan view of a soft bifocal contact lens having laterally spaced optics for the distance and near optical zones. In this example, both the distance power zone 1301 and the near power zone 1302 are configured with single focal lengths with their optical axes laterally spaced apart by 0.5 mm. This example differs from the example of FIG. 12B in that the near optical axes are laterally spaced apart to form a ring of near foci surrounding the distance optical axis. The near zone has a power of +2.5D. The lens of FIG. 13 is also configured so that the near focus is laterally spaced apart or inferior to the distance focus. The plan view illustrates the optical zones divided into two hemispheres: an upper zone and a lower zone.

[0229] FIG. 14 is a schematic diagram illustrating ray tracing of a distant object and a near object imaged through the ophthalmic lens of FIG. 13 according to certain embodiments. FIG. 14 also shows high-magnification insets of ray tracings formed when the distant object is focused at the retinal plane (distance vision) and when the near object is focused at the image plane (near vision). In each figure, rays passing through each out-of-focus zone are represented as out-of-focus blurred circles at the image plane. The distant object in FIG. 14 is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) located 0.5 degrees on either side of OP1. Similarly, the near object in FIG. 14b is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) located 0.15 degrees on either side of OP1.

[0230] As shown in the distance focus chart, the focal points of distant objects OP1, OP2, and OP3, designated DF1, DF2, and DF3, are at the image plane, and the defocused rays of OP1, OP2, and OP3 that pass through the near addition zone constitute the remaining rays located at the image plane (below the focused distant object points). The near focus chart shows that the focal points of near objects OP1, OP2, and OP3 are designated NF1, NF2, and NF3 at the image plane, and the defocused rays of OP1, OP2, and OP3 that pass through the distance vision zone constitute the remaining rays located above the near focal points at the image plane. The ray tracing in Figure 14 shows that in the example of a laterally spaced ring bifocal contact lens design, there is no interaction between the defocused rays of object points OP1, OP2, and OP3 and the focused images of OP1, OP2, and OP3 created by the distance and / or near power zone(s).

[0231] 15A and 15B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 13 according to certain embodiments.

[0232] FIG. 15A shows the spot diagram and RMS value of the focal point DF1 of a distant object point OP1 formed at the retinal surface by the bifocal contact lens of FIG. 13 having laterally spaced optics for the distance and near optical zones. In this example, DF1 has an RMS size of 2.16 μm. These values ​​are similar to those expected for foci produced by a single-vision optical design. However, unlike a lens configured with coaxial optics such as FIG. 10A, there may be no interaction from defocused rays of object points OP2 and OP3 formed by the near zone (RMS value = 0). Because defocused rays from adjacent object points do not overlap with the focal point DF1 to increase its RMS spot size, the overall average RMS value remains small at 2.16 μm for the exemplary lens configured with laterally spaced foci. Similarly, DF2 and DF3 may also be unaffected by defocused rays from adjacent object points.

[0233] FIG. 15B shows the spot diagram and RMS value of the near focus NF1 of the near object point OP1 formed on the retinal surface by the bifocal contact lens of FIG. 13. In this example, NF1 has an RMS size of 1.80 μm. These values ​​are similar to those expected for foci produced by a single-vision optical design. However, unlike a lens configured with a coaxial optical system such as FIG. 10A, there may be no interaction from defocused rays of the near object points OP2 and OP3 formed by the distance zone (RMS value = 0). Because the focus NF1 does not increase its RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 1.8 μm for a lens configured with laterally spaced near foci. Similarly, NF2 and NF3 may also be unaffected by defocused rays from adjacent object points.

[0234] Thus, the lens of FIG. 15 (e.g., FIGS. 13-15), configured with the laterally spaced optics described herein, exhibits improved sharpness and high distance and near image quality.

[0235] FIG. 16 is a schematic diagram illustrating an exemplary design of an ophthalmic lens using a spherical structure, according to certain embodiments. In some embodiments, as in the embodiment shown in FIG. 13, an ophthalmic lens 700 may be formed utilizing two spherical surfaces 702, 704 to reduce discontinuities between the two optical zones. The spherical surfaces 702, 704 may have different diameters (the diameter of the spherical surface 702 is larger than the diameter of the spherical surface 704) and may intersect at a boundary 706. An optical zone 708 is defined and includes a first optical zone 710 and a second optical zone 712. The characteristics of the first optical zone 710 are defined by the spherical surface 702, and the characteristics of the second optical zone 712 are defined by the spherical surface 704. Because the spherical surfaces intersect at the interface 706, discontinuities are reduced, potentially reducing the need for blending (e.g., a blending zone). In some embodiments, a blending zone may not be present. The resulting lens 700 can be characterized using several parameters. In some embodiments, the first optical zone 710 has a first optical power and the second optical zone 712 has a second optical power different from the first optical power. In some embodiments, the first optical zone has a first optical power and the second optical zone has a second optical power that is relatively more positive than the first optical power. In some embodiments, the first optical zone has a first optical power and the second optical zone has a second optical power that is relatively more positive than the first optical power by about +0.25D to about +3D. In some embodiments, the second optical zone has a second optical power that is relatively more positive than the first optical power by about +0.25D to +2.5D, about +0.25D to +2D, about +0.25D to +1.5D, about +0.25D to +1D, and about +0.25D to +0.5D. In some embodiments, the first optical zone has a first optical power and the second optical zone has a second optical power that is relatively greater than the first optical power by about +3D or more, hi some embodiments, the first optical zone has a first optical power and the second optical zone has a second optical power that is relatively less than the first optical power.In some embodiments, the first optical zone has a first optical power and the second optical zone has a second optical power that is relatively more positive than the first optical power by about -0.25D to about -3D. In some embodiments, the first optical zone may occupy an upper portion of the ophthalmic lens. In some embodiments, the second optical zone may occupy a lower portion of the ophthalmic lens. In some embodiments, the first optical zone may be configured to correct one of distance vision, intermediate vision, or near vision, and / or the second optical zone may be configured to correct a different one of distance vision, intermediate vision, or near vision. In some embodiments, the first optical zone may be configured to correct distance vision and the second optical zone may be configured to correct near vision. In some embodiments, the first optical zone may be configured to correct near vision and the second optical zone may be configured to correct distance vision. The use of two spherical surfaces 702 and 704 and the radii of the first and second optical zones that do not intersect along the surface of the lens allows the images to be optically spaced (e.g., laterally displaced), which can result in a reduced RMS spot size of the retinal image.

[0236] FIG. 17 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a soft bifocal contact lens) including laterally spaced optics for the distance and near optical zones, according to certain embodiments. FIG. 17 illustrates a plan view of a soft bifocal contact lens configured with laterally spaced optics for the distance and near optical zones. In this example, both the distance power zone 1701 and the near power zone 1702 are configured with single focal points with their optical axes laterally spaced apart by 0.5 mm. The near add power is +2.5D. The lens in this example is configured with the near focus laterally spaced downward. The plan view illustrates two hemispherical optical zones, an upper zone and a lower zone. This example differs from the example in FIG. 13 in that the lateral spacing of the near optical axes is configured without changing the interface between the laterally spaced distance and near optical zones. The intersection of the two zones in the lens of Figure 17 is curved, and the junction between the distance and near zones is configured to be substantially seamless and / or substantially jointless. The improved junction is achieved through the use of spherical surface curvatures as discussed in this disclosure. In some embodiments, spherical surface curvatures may be utilized without utilizing a substantially seamless and / or substantially jointless configuration (e.g., a blend zone or step may still be utilized).

[0237] FIG. 18 is a schematic diagram illustrating ray tracing of a distant object and a near object imaged through the ophthalmic lens of FIG. 17 according to certain embodiments. FIG. 18 also provides high-magnification insets of ray tracings formed when a distant object is focused at the retinal plane (distance vision) and when a near object is focused at the retinal plane (near vision). In each figure, defocused rays passing through the out-of-focus zone are represented as defocused blurred circles at the image plane. The distant object is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2, OP3) located 0.5 degrees apart on either side of OP1. Similarly, the near object in FIG. 18 is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2, OP3) located 0.15 degrees apart on either side of OP1.

[0238] The distance focus chart in Figure 18 shows that the focal points of distant objects OP1, OP2, and OP3 are designated DF1, DF2, and DF3 at the image plane, and that the defocused rays of OP1, OP2, and OP3 that pass through the near addition zone constitute the remaining rays located at the image plane (below the focused distant object point). The near focus chart shows that the focal points of near objects OP1, OP2, and OP3 are designated NF1, NF2, and NF3 at the image plane, and that the defocused rays of OP1, OP2, and OP3 that pass through the distance vision zone constitute the remaining rays located above the near focal point at the image plane. Figure 18 shows that in these laterally spaced progressive contact lens designs, there is no interaction between the defocused rays of object points OP1, OP2, and OP3 and the focused images of OP1, OP2, and OP3 created by the distance or near power zone(s).

[0239] 19A and 19B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 17, according to certain embodiments.

[0240] FIG. 19A shows the spot diagram and RMS value of the focal point DF1 of the distant object point OP1 formed at the retinal surface by the bifocal contact lens of FIG. 17 having laterally spaced optics for the distance and near optical zones. In this example, DF1 has an RMS size of 2.32 μm. These values ​​are similar to those of foci produced by a single-vision optical design. However, unlike the case of a lens configured with coaxial optics such as FIG. 10A, there may be no interaction from defocused rays of object points OP2 and OP3 formed by the near zone (RMS value = 0). Because the focal point DF1 does not increase its RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 2.32 μm for a lens configured with laterally spaced foci. Similarly, DF2 and DF3 may also be unaffected by defocused rays from adjacent object points.

[0241] FIG. 19B shows the spot diagram and RMS value of the near focus NF1 of the near object point OP1 formed on the retinal surface by the bifocal contact lens of FIG. 17. In this example, NF1 has an RMS size of 1.98 μm. These values ​​are similar to those of foci produced by a single-vision optical design. However, unlike a lens configured with a coaxial optical system such as FIG. 10a, there may be no interaction from defocused rays of the near object points OP2 and OP3 formed by the distance zone (RMS value = 0). Because the focus NF1 does not increase its RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 1.98 μm for a lens configured with laterally spaced near foci. Similarly, NF2 and NF3 may also be unaffected by defocused rays from adjacent object points.

[0242] Thus, the lens of FIG. 17, configured with laterally spaced optics, exhibits improved sharpness and high distance and near image quality over the coaxial-based design of FIG. 10A. Further examples of incorporating laterally spaced optical structures into contact or spectacle lenses can include: (1) designing partial overlap of object images; and (2) introducing lateral separation between both the distance and near optics, which can be equal or unequal, and in the same, opposite, relative, or independent amounts. Furthermore, varying the lateral separation can affect the shape of the interface between the two optical zones, with a relatively small separation resulting in a more curved interface and a relatively large separation resulting in a less curved interface.

[0243] FIG. 20 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a soft bifocal contact lens) including laterally spaced optics for the distance and near optical zones, according to certain embodiments. In this example, both the distance power zone 2001 and the near power zone 2002 are configured as single-focus lenses with their optical axes laterally spaced apart by 0.25 mm. The near add power is +2.5D. This exemplary lens is configured with near foci spaced laterally downward. The plan view shows the optical zones separated into two hemispheres, an upper zone and a lower zone. This example differs from the example of FIG. 13 in that the near optical axes are spaced apart laterally with no joint between the laterally spaced distance and near optical zones. The intersection of the two zones in the lens of FIG. 20 is curved, resulting in a substantially seamless and / or substantially jointless interface between the distance and near zones. An improved joint is achieved through the use of a spherical surface curvature.

[0244] FIG. 21 is a schematic diagram illustrating ray tracing of a distant object and a near object imaged through the ophthalmic lens of FIG. 20 according to certain embodiments. FIG. 21 also provides high-magnification insets of ray tracings formed when a distant object is focused at the retinal plane (distance vision) and when a near object is focused at the retinal plane (near vision). In each figure, defocused rays passing through the out-of-focus zone are represented as blurred, out-of-focus circles at the image plane. The distant object on the far-focus chart is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2, OP3), located 0.5 degrees apart on either side of OP1. Similarly, the near object on the near-focus chart is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2, OP3), located 0.15 degrees apart on either side of OP1.

[0245] The distance focus chart shows that the focal points of distant objects OP1, OP2, and OP3 are designated DF1, DF2, and DF3 at the image plane, and that the defocused rays of OP1, OP2, and OP3 that pass through the near addition zone constitute the remaining rays located at the image plane (below the focused distant object point). The near focus chart shows that the focal points of near objects OP1, OP2, and OP3 are designated NF1, NF2, and NF3 at the image plane, and that the defocused rays of OP1, OP2, and OP3 that pass through the distance vision zone constitute the remaining rays located above the near focus at the image plane. Figure 21 shows the interaction between the defocused rays of distant object points passing through the near zones on DF-1 and DF-2 but not on DF-3, while the near focus chart shows the interaction between the defocused rays of near object points passing through the distance zone on NF-3 due to the distance power zones of these laterally spaced progressive contact lens designs.

[0246] 22A and 22B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 20 according to certain embodiments.

[0247] FIG. 22A shows the spot diagram and RMS value of the focal point DF1 of the distant object point OP1 formed at the retinal surface by the bifocal contact lens of FIG. 20, which has laterally spaced optics for the distance and near optical zones. In this example, DF1 has an RMS size of 1.93 μm. These values ​​are similar to those of foci produced by a single-vision optical design. However, unlike the lens configured with widely spaced foci in FIG. 17, there is interaction from the defocused rays of object point OP3 (RMS value = 162.6 μm) formed by the near zone on DF-1, but there is no defocused ray from OP2 (0 μm) on DF-1. Therefore, with this lens with laterally spaced foci, the overall blurring effect of focal point D-F1 may remain due to the overlap of defocused rays from adjacent object points, resulting in a larger RMS spot size (overall average RMS value of 93.88 μm). Ray tracing also shows that D-F2 is similarly affected by defocus light from adjacent object points, while DF-3 is not.

[0248] FIG. 22B shows the spot diagram and RMS value of the near focal point NF1 of the near object point OP1 formed on the retinal surface by the bifocal contact lens of FIG. 20. NF1 has an RMS size of 1.84 μm. These values ​​are similar to those of foci produced by a single-vision optical design. However, unlike focusing a distant object as in FIG. 22A, there may be no interaction from defocused rays of the near object points OP2 and OP3 formed by the distance zone (RMS value = 0). Because the focal point NF1 does not increase its RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 1.84 μm for a lens configured with laterally spaced near foci.

[0249] Thus, the lens of FIG. 20 illustrates that a lens constructed with the laterally spaced optics described herein can differentially manipulate image quality between the far and near foci.

[0250] FIG. 23 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a soft bifocal contact lens) including laterally spaced optics for the distance and near optical zones, according to certain embodiments. In this example, both the distance power zone 2301 and the near power zone 2302 are configured with single focal lengths with their distance and near optical axes laterally spaced 0.25 mm below and 0.50 mm above the optical center of the contact lens. The near add power is +2.5D. This exemplary lens is configured with the near focus located inferiorly. The plan view shows the optical zones separated into two hemispheres: an upper zone and a lower zone. This example differs from the example of FIG. 13 in that the lateral spacing of the near optical axes is configured without changing the interface between the laterally spaced distance and near optical zones. The intersection of the two zones in the lens of Figure 26 is curved to provide a substantially seamless and / or substantially no interface between the distance and near zones. The improved interface is achieved through the use of spherical surface curvature.

[0251] FIG. 24 is a schematic diagram showing ray tracing of a distant object and a near object imaged through the ophthalmic lens of FIG. 23. FIG. 24 also presents high-magnification insets of ray tracings formed when a distant object is in focus at the retinal plane (distance vision) and when a near object is in focus at the retinal plane (near vision). In each figure, defocused rays passing through the out-of-focus zone are represented as blurred, out-of-focus circles on the image plane. The distant object on the distance focus chart is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3), located 0.5 degrees on either side of OP1. Similarly, the near object in FIG. 24 is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3), located 0.15 degrees on either side of OP1.

[0252] The distance focus chart shows that the focal points of the distant objects OP1, OP2, and OP3 are DF1, DF2, and DF3 at the image plane, and that the defocused rays of OP1, OP2, and OP3 that pass through the near addition zone constitute the remaining rays located at the image plane (below the focused distant object point). The near focus chart shows that the focal points of the near objects OP1, OP2, and OP3 are NF1, NF2, and NF3 at the image plane, and that the defocused rays of OP1, OP2, and OP3 that pass through the distance vision zone constitute the remaining rays located above the near focus at the image plane. Figure 24 shows that for these laterally spaced progressive contact lens designs, there is no interaction between the defocused rays of the object points OP1, OP2, and OP3 and the focused images of OP1, OP2, and OP3 created by the distance or near power zone(s).

[0253] 25A and 25B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 23 according to certain embodiments.

[0254] FIG. 25A shows the spot diagram and RMS value of the focal point D-F1 of the distant object point OP1 formed at the retinal surface by the bifocal contact lens of FIG. 17 having laterally spaced optics for the distance and near optical zones. In this example, DF1 has an RMS size of 5.71 μm. These values ​​are similar to those expected for foci produced by a single-vision optical design. However, unlike the case of a lens configured with coaxial optics such as FIG. 10A, there may be no interaction from defocused rays of object points OP2 and OP3 formed by the near zone (RMS value = 0). Because the focal point DF1 does not increase its RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 5.71 μm for the lens configured with laterally spaced foci. Similarly, D-F2 and D-F3 may also be unaffected by defocused rays from adjacent object points.

[0255] FIG. 25B shows the spot diagram and RMS value of the near focus N-F1 of the near object point OP1 formed on the retinal surface by the bifocal contact lens of FIG. 23. In this example, NF1 has an RMS size of 2.01 μm. These values ​​are similar to those of foci generated by a single-vision optical design. However, unlike a lens configured with a coaxial optical system such as FIG. 10A, there may be no interaction from defocused rays of the near object points OP2 and OP3 formed by the distance zone (RMS value = 0). Because the focus NF1 does not increase its RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 2.01 μm for a lens configured with laterally spaced near foci. Similarly, NF2 and NF3 may also be unaffected by defocused rays from adjacent object points.

[0256] Thus, the lens of FIG. 23 configured with far and near foci laterally spaced apart by different amounts can still maintain improved sharpness and high far and near image quality over, for example, the coaxial-based design of FIG. 10A.

[0257] FIG. 26 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a bifocal lens) including laterally spaced optics for the distance and near optical zones, according to certain embodiments. In this example, both the distance power zone 2601 and the near power zone 2602 are configured with single focal points with their optical axes laterally spaced apart by 0.5 mm. The near add power is +2.5D. The lens of FIG. 26 is also configured with the near focus laterally spaced apart or downwardly shifted. The plan view shows the optical zones separated into two regions: an upper zone and a lower zone. Similar to the contact lens described in FIG. 23, this example spectacle lens is configured with a substantially seamless and / or substantially no interface between the distance and near zones. The improved interface is achieved by using a spherical outer curvature, and in this example the lateral and inferior distances of the near focus were chosen to be 0.5 mm, which may result in a nonlinear interface.

[0258] FIG. 27 is a schematic diagram illustrating ray tracing of a distant object and a near object imaged through the ophthalmic lens of FIG. 26 according to certain embodiments. FIG. 27 also provides high-magnification insets of ray tracings formed when a distant object is focused at the retinal plane (distance vision) and when a near object is focused at the retinal plane (near vision). In each figure, rays passing through each out-of-focus zone are represented as out-of-focus blurred circles at the image plane. The distant object on the far-focus chart is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2, OP3), located 0.50 degrees on either side of OP1. Similarly, the near object on the near-focus chart is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2, OP3), located 0.15 degrees on either side of OP1.

[0259] The distance focus chart shows that the focal points of distant objects OP1, OP2, and OP3 are DF1, DF2, and DF3 at the image plane, and that the defocused rays of OP1, OP2, and OP3 that pass through the near addition zone constitute the remaining rays located at the image plane (below the focused distant object point). The near focus chart shows that the focal points of near objects OP1, OP2, and OP3 are NF1, NF2, and NF3 at the image plane, and that the defocused rays of OP1, OP2, and OP3 that pass through the distance vision zone constitute the remaining rays located above the near focal point at the image plane. Figure 27 shows that in these laterally spaced ring spectacle lens designs, there is no interaction between the defocused rays of object points OP1, OP2, and OP3 and the images of OP1, OP2, and OP3 created by the distance or near power zone(s).

[0260] 28A and 28B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 26, according to certain embodiments.

[0261] FIG. 28A shows the spot diagram and RMS values ​​of the focal spot DF1 of a distant object point OP1 formed at the retinal plane by the spectacle lens of FIG. 26 having laterally spaced optics for the distance and near optical zones, sampled over a 5-mm aperture at the spectacle lens surface. In this example, DF1 has an RMS size of 0.49 μm. These values ​​are similar to those of foci produced by a single-vision optical design with a similar aperture size. However, unlike the case of a lens configured with coaxial optics such as FIG. 10A, there may be no interaction from defocused rays of object points OP2 and OP3 formed by the near zone (RMS value = 0). Because the focal spot DF1 does not increase the RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 0.49 μm for a lens configured with laterally spaced foci. Similarly, DF2 and DF3 may also be unaffected by defocused rays from adjacent object points.

[0262] FIG. 28B shows the spot diagram and RMS value of the near focus NF1 of the near object point OP1 formed on the retinal surface by the spectacle lens of FIG. 26. In this example, NF1 has an RMS size of 0.42 μm. These values ​​are similar to the expected value of a focus produced by a single-vision optical design (RMS value = 0) because there is no interaction from defocused rays of near object points OP2 and OP3 formed by the distance zone. Because the focus NF1 does not increase its RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 0.42 μm for a lens configured with laterally spaced near foci. Similarly, NF2 and NF3 may also be unaffected by defocused rays from adjacent object points.

[0263] Thus, the spectacle lens of FIG. 26 configured with the laterally spaced optics described herein exhibits improved sharpness and high distance and near image quality over, for example, the coaxial-based design of FIG. 10A.

[0264] 29A is a schematic diagram showing a plan view of an executive bifocal lens according to an embodiment. As shown in FIG. 29A, the executive bifocal lens has a discontinuous interface between a distance zone 2901 and a near zone 2902.

[0265] FIG. 29B is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a bifocal lens) including laterally spaced optics for a distance optical zone 2911 and a near optical zone 2912, according to certain embodiments. In this example, both the distance power zone and the near power zone are configured with single focal points whose optical axes are laterally spaced apart by 1 mm. The near add power is +2.5D. The lens of FIG. 29B is also configured with the near focus laterally spaced apart or downwardly shifted. The plan view shows the optical zones separated into two regions: an upper zone and a lower zone. Similar to the spectacle lens described in FIG. 26, this example spectacle lens of FIG. 29B is configured with a substantially seamless and / or substantially no interface between the distance and near zones. An improved interface may be achieved by using a spherical outer surface curvature, and in this example, the interface may be nonlinear due to the selection of a 1 mm lateral and inferior distance for the near focus. However, compared to the example shown in FIG. 26 with a lateral distance of 0.5 mm, the lens in FIG. 29B with a 1 mm lateral distance has a less curved interface between the distance and near zones, allowing for a wider near zone of the spectacle lens and a wider field of view through the near zone.

[0266] FIG. 30 is a schematic diagram showing ray tracing of a distant object and a near object imaged through the ophthalmic lens of FIG. 29B according to certain embodiments. FIG. 30 also presents high-magnification insets of ray tracings formed when a distant object is focused at the retinal plane (distance vision) and when a near object is focused at the retinal plane (near vision). In each figure, rays passing through each out-of-focus zone are represented as out-of-focus blurred circles at the image plane. The distant object in the far-focus inset is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2, OP3), located 0.50 degrees on either side of OP1. Similarly, the near object in the near-focus inset is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2, OP3), located 0.15 degrees on either side of OP1.

[0267] The distance focus chart shows that the focal points of distant objects OP1, OP2, and OP3 are DF1, DF2, and DF3 at the image plane, and that the defocused rays of OP1, OP2, and OP3 that pass through the near addition zone constitute the remaining rays located at the image plane (below the focused distant object point). The near focus chart shows that the focal points of near objects OP1, OP2, and OP3 are NF1, NF2, and NF3 at the image plane, and that the defocused rays of OP1, OP2, and OP3 that pass through the distance vision zone constitute the remaining rays located above the near focus at the image plane. Figure 30 illustrates the larger separation between the focused and defocused rays at the image plane and the lack of interaction between the defocused rays of object points OP1, OP2, and OP3 and the images of OP1, OP2, and OP3 created by the distance or near power zone(s) in these laterally separated ring spectacle lens designs.

[0268] 31A and 31B are schematic diagrams illustrating spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal plane by the ophthalmic lens of FIG. 29B, according to certain embodiments.

[0269] FIG. 31A shows the spot diagram and RMS values ​​of the focal spot DF1 of a distant object point OP1 formed at the retinal plane by the spectacle lens of FIG. 29B with laterally spaced optics for the distance and near optical zones, sampled across a 5-mm aperture at the spectacle lens surface. In this example, DF1 has an RMS size of 0.72 μm. These values ​​are similar to those of focal spots produced by a single-vision optical design with a similar aperture size. However, unlike the case of a lens configured with coaxial optics such as FIG. 10A, there may be no interaction from defocused rays of object points OP2 and OP3 formed by the near zone (RMS value = 0). Because the focal spot DF1 does not increase its RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 0.72 μm for a lens configured with laterally spaced foci. Similarly, DF2 and DF3 may also be unaffected by defocused rays from adjacent object points.

[0270] FIG. 31B shows the spot diagram and RMS value of the near focus NF1 of the near object point OP1 formed on the retinal surface by the spectacle lens of FIG. 29B. In this example, NF1 has an RMS size of 0.8 μm. These values ​​are similar to the expected value of a focus produced by a single-vision optical design (RMS value = 0) because there is no interaction from defocused rays of near object points OP2 and OP3 formed by the distance zone. Because the focus NF1 does not increase its RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 0.8 μm for a lens configured with laterally spaced near foci. Similarly, NF2 and NF3 may also be unaffected by defocused rays from adjacent object points.

[0271] Thus, a spectacle lens of Fig. 29B constructed with the laterally spaced optics described herein may exhibit improved sharpness and higher distance and near image quality than, for example, the coaxial-based design of Fig. 10 A. Furthermore, the increased lateral separation of the foci may increase the field of view through the near zone and near vision zone compared to a lens constructed with a smaller focal separation, for example, as described in Fig. 26.

[0272] FIG. 32 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a bifocal lens) including laterally spaced optics for a distance optical zone 3201 and a near optical zone 3202, according to certain embodiments. In this example, both the distance and near power zones are configured with single foci whose optical axes are laterally spaced apart by 0.5 mm. The near add power is +2.5D. However, unlike the lens of FIG. 29B, in which only the near focus is laterally spaced apart or downshifted, the lens of FIG. 32 is configured such that the distance focus is upshifted by 0.25 mm and the near focus is downshifted by an equal and opposite amount of 0.25 mm, for a total net lateral separation between the foci of 0.5 mm. The plan view shows the optical zones separated into two regions: an upper zone and a lower zone. Similar to the spectacle lens depicted in Figure 29B, this example spectacle lens is also configured to have a substantially seamless and / or substantially no interface between the distance and near zones. The improved interface can be achieved through the use of a spherical outer surface curvature.

[0273] FIG. 33 is a schematic diagram illustrating ray tracing of a distant object and a near object imaged through the ophthalmic lens of FIG. 32 according to certain embodiments. FIG. 33 also presents high-magnification insets of ray tracings formed when a distant object is focused at the retinal plane (distance vision) and when a near object is focused at the retinal plane (near vision). In each figure, rays passing through each out-of-focus zone are represented as out-of-focus blurred circles at the image plane. The distant object in the far-focus chart is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2, OP3), located 0.5 degrees on either side of OP1. Similarly, the near object in the near-focus inset is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2, OP3), located 0.15 degrees on either side of OP1.

[0274] The far focus chart shows that the focal points of distant objects OP1, OP2, and OP3 are DF1, DF2, and DF3 on the image plane, and that the out-of-focus rays of OP1, OP2, and OP3 that pass through the near addition zone constitute the remaining rays located on the image plane (below the focused distant object point). The near focus chart shows that the focal points of near objects OP1, OP2, and OP3 are NF1, NF2, and NF3 on the image plane, and that the out-of-focus rays of OP1, OP2, and OP3 that pass through the distance vision zone constitute the remaining rays located above the near focal point on the image plane. Figure 33 shows the separation between the in-focus and defocused light at the image planes on either side of the geometric center of the 5 mm aperture on the spectacle lens surface and the lack of interaction between the defocused light rays of object points OP1, OP2 and OP3 in these laterally separated ring spectacle lens designs and the images of OP1, OP2 and OP3 produced by the distance or near power zone(s).

[0275] 34A and 34B are schematic diagrams showing spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal surface by the ophthalmic lens of FIG.

[0276] FIG. 34A shows the spot diagram and RMS values ​​of the focal spot DF1 of a distant object point OP1 formed at the retinal plane by the spectacle lens of FIG. 32 with laterally spaced optics for the distance and near optical zones, sampled over a 5-mm aperture at the spectacle lens surface. In this example, DF1 has an RMS size of 0.8 μm. These values ​​are similar to those of foci produced by a single-vision optical design with a similar aperture size. However, unlike the case of a lens configured with coaxial optics such as FIG. 10A, there may be no interaction from defocused rays of object points OP2 and OP3 formed by the near zone (RMS value = 0). Because the focal spot DF1 does not increase the RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 0.84 μm for the lens configured with laterally spaced foci. Similarly, DF2 and DF3 may also be unaffected by defocused rays from adjacent object points.

[0277] FIG. 34B shows the spot diagram and RMS value of the near focus NF1 of the near object point OP1 formed on the retinal surface by the spectacle lens of FIG. 32. In this example, NF1 has an RMS size of 1.49 μm. These values ​​are similar to the expected values ​​of the focus produced by a single-vision optical design (RMS value = 0) because there is no interaction from defocused rays of near object points OP2 and OP3 formed by the distance zone. Because the focus NF1 does not increase its RMS spot size due to overlapping defocused rays from adjacent object points, the overall average RMS value remains small at 1.49 μm for a lens configured with laterally spaced near foci. Similarly, NF2 and NF3 may also be unaffected by defocused rays from adjacent object points.

[0278] Thus, the spectacle lens of Figure 32 constructed with the laterally spaced optics described herein exhibits improved sharpness and high distance and near image quality over, for example, the coaxial-based design of Figure 10A. Also, the desirable image quality of the focal points DF-1 and NF-1 is not affected by the fact that both the distance and near foci are spaced above and below, respectively.

[0279] FIG. 35 is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a bifocal lens) including laterally spaced optics for a distance optical zone 3501 and a near optical zone 3502, according to certain embodiments. In this example, both the distance power zone and the near power zone are configured as single focuses with their optical axes and foci separated laterally by 0.5 mm. The near add power is +2.5D. However, like the lens of FIG. 35, the lens of FIG. 35 is configured such that the distance focus is shifted up by 0.25 mm and the near focus is shifted down by an equal and opposite amount of 0.25 mm, for a total net lateral separation between the foci of 0.5 mm. The plan view shows the optical zones separated into two regions: an upper zone and a lower zone. In this example, the upper zone contains the distance power, while the lower zone contains both the near power area and the peripheral distance power area. Similar to the spectacle lens depicted in FIG. 32, this example spectacle lens is configured such that the junction between the distance and near zones is substantially seamless and / or substantially joint-free. A substantially seamless and / or joint-free intersection between the zones can be achieved through the use of a spherical outer surface curvature. Lateral separation of the optical axis and focal point can introduce prismatic power into the spectacle lens. The lens of FIG. 35 is designed with an inner spherical surface curvature that creates an equal and opposite amount of lateral separation (−0.25 mm) to that provided for the outer distance and near zones. As a result of the inner surface design, the prismatic power introduced by the outer surface design is eliminated, while retaining the advantage that the lateral separation of the distance and near optical zones creates a substantially seamless and / or joint-free intersection.

[0280] Figure 36 is a schematic diagram showing ray tracing of a distant object and a near object imaged through the ophthalmic lens of Figure 35. Figure 36 also presents high-magnification insets of ray tracings formed when a distant object is focused at the retinal plane (distance vision) and when a near object is focused at the retinal plane (near vision). In each figure, rays passing through each out-of-focus zone are represented as out-of-focus blurred circles on the image plane. The distant object in the far-focus chart is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3), located 0.5 degrees on either side of OP1. Similarly, the near object in the near-focus inset is further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3), located 0.15 degrees on either side of OP1.

[0281] The far focus chart shows that the focal points of distant objects OP1, OP2, OP3 are DF1, DF2, DF3 at the image plane, and that the out-of-focus rays of OP1, OP2, OP3 that pass through the near addition zone constitute the remaining rays located at the image plane (above the focused distant object point). The near focus chart shows that the focal points of near objects OP1, OP2, OP3 are NF1, NF2, NF3 at the image plane, and that the out-of-focus rays of OP1, OP2, OP3 that pass through the far vision zone constitute the remaining rays located at the image plane. FIG. 36 illustrates the separation between focused and defocused light at the image plane on either side of the geometric center of a 5 mm aperture on the spectacle lens surface and the extent of interaction between the defocused light rays of object points OP1, OP2, and OP3 and the images of OP1, OP2, and OP3 produced by the distance or near power zone(s) for these laterally spaced spectacle lens designs incorporating laterally spaced optical axes and foci.

[0282] 37A and 37B are schematic diagrams showing spot diagrams and RMS values ​​of focal points DF1 and NF1 of object point OP1 formed on the retinal surface by the ophthalmic lens of FIG. 35 according to certain embodiments. In this example, DF1 has an RMS size of 5.79 μm. The small lateral separation of the foci (0.25 mm) was not enough to eliminate the overlap of defocused light from OP1 passing through the near zone of DF1. However, unlike the case of an ophthalmic lens configured with a coaxial optical system such as that of FIG. 10A, even with the relatively small lateral separation (0.25 mm) used in the example, there is still no interaction (RMS value = 0) from the defocused rays of object points OP2 and OP3 formed by the distance zone. Because the RMS spot size at focal point DF1 is less likely to be increased by the overlap of defocused rays from the object points, the overall average RMS value remains small at 5.79 μm for lenses configured with laterally spaced foci. Similarly, DF2 and DF3 will also be affected by defocused light from adjacent object points.

[0283] Figure 37B shows the spot diagram and RMS value of the near focus NF1 of the near object point OP1 formed on the image plane by the spectacle lens of Figure 36. In this example, NF1 has an RMS size of 1.84 μm. These values ​​are similar to the expected value of the focus produced by a single-vision optical design (RMS value = 0) because there is no interaction from the defocused rays of the near object points OP2 and OP3 formed by the distance zone. However, because the back surface is optically designed to eliminate the lateral separation of the focus points to nullify the introduced prismatic power of the entire lens, the focus NF1 is increased in RMS spot size to 41.29 μm due to the overlap of the defocused rays from the adjacent object point OP2, resulting in an overall average RMS value of 23.86 μm for a lens without prismatic power. Similarly, NF2 and NF3 can also be affected by defocused rays from adjacent object points where there is no remaining lateral separation of the focus points.

[0284] Thus, the spectacle lens of Figure 36 configured with laterally spaced optics on its outer and inner surfaces exhibits a substantially seamless and / or substantially joint-free surface with no prismatic power, but with some compromise in image quality, which can be improved to single vision quality by slightly increasing the lateral spacing and introducing a small amount of prismatic power.

[0285] FIG. 38 is a schematic diagram of a progressive addition (PAL) spectacle lens, according to certain embodiments. A PAL lens may be designed with a distance area 3801 that is larger than the distance area available in conventional PAL-type lenses, and a lower-located near power area 3802 surrounded by one or more progressive power areas. The progressive power zone in this example progresses in three steps from the distance power to a maximum near power of +2.5D. In some embodiments, a distribution of increasing power progression may be incorporated into such a lens design based on the patient's refractive and visual requirements and the desired length of power progression. In this example, the length of the power progression is approximately 17 mm. The three power areas and their foci in this example progressive power area are spaced laterally from the distance focus. The first, second, and third power areas of the progressive power area are spaced laterally 1.5 mm from the distance power focus. In this example, the outer surface curvatures of the distance area and the progressive power area are spherical, and the junctions between the areas are substantially seamless and / or substantially junction-free (e.g., little blending is required). The diameter of a first area of ​​the progressive power zone is larger than that of the second progressive power zone, and both the first and second areas are larger in diameter than the third progressive power zone. The locations of the improved junctions in this example are shown in FIG. 38 as lines B, C, D, and E, but are substantially invisible to the observer, and no actual lines or marks are present on the ophthalmic lens. FIG. 38 includes a schematic diagram illustrating the profile of a PAL spectacle lens. The intersection of the smooth progressive power profile, the spherical surface curvature, and the substantially seamless and / or substantially junction-free surface curvature is depicted, along with the imaginary locations of the junction lines B, C, D, and E.

[0286] The PAL lens shown in FIG. 38 is designed with a 1.5 mm lateral separation between the optical axis of the distance area, where the distance focus is formed, and the first optical axis and first focus of the three power areas of the progressive power area. Therefore, prismatic power is introduced due to the difference in surface curvature of the outer surface area of ​​the PAL spectacle lens. However, like the lens of FIG. 35, the PAL spectacle lens of FIG. 38 is designed with an inner surface that creates an opposite (or substantially opposite) amount of lateral separation (e.g., −1.5 mm) to that provided for the outer progressive power zone in the lower area of ​​the lens. Incorporating this opposite amount of lateral separation into the inner surface curvature eliminates the prismatic power introduced below the outer surface, while retaining the advantage that the lateral separation between the distance optical zone and the near optical zone creates a substantially seamless and / or substantially jointless intersection.

[0287] FIG. 39 is a geometric diagram showing more details of the outer surfaces used to form the exemplary progressive addition spectacle lens (PAL) shown in FIG. 38. The diagram shows the optical center A of the lens, the hypothetical junction B of the upper and lower zones of the lens, and three progressive power areas C, D, and E. The upper area of ​​the lens in this example contains only distance power. Note that the lower area may contain a portion of the progressive power area and a near power area, with the remainder being a distance power area. The upper distance power area is represented by a spherical curvature, and the lower area is represented by a series of spherical curvatures to generate the three powers of the progressive power area, with the remainder being the same curvature representing the distance power. The values ​​are in millimeters, with the distance radius being 180 and the near radii being R93, R120, and R150. The lateral spacing of the progressive power zones can be expressed as the difference in distance between the optical center A of the lens and the progressive power zones.

[0288] FIG. 40 details the power maps of the PAL spectacle lens design shown in FIG. 39. Two power maps are shown covering the area of ​​the spectacle lens. A 35 mm x 35 mm mean spherical power map and a 35 mm x 60 mm cylindrical power map are shown for a PAL spectacle lens designed with laterally spaced distance and progressive power areas. The spherical power map shows that, in this example, the distance, progressive, and near power areas have large, wide, uniform power areas. The spherical and cylindrical power maps shown in FIG. 40 show a substantially uniform, substantially wider mean spherical power zone (compared to other PAL designs), with substantially no blending area and no total or surface cylindrical power, creating a substantially seamless and substantially joint-free surface. Thus, the design and construction of the ophthalmic lens maintains substantially the same tangential and sagittal surface curvature and power throughout the progressive zone. Conventional PAL designs compromise significant blend areas containing significant cylinder power above 0.5 DC, 1.0 DC, or even 2.0 DC to provide a progressive power band with a virtually joint-free surface.

[0289] The PAL eyeglass lens of the exemplary embodiment depicted in FIG. 39 is symmetrical about the vertical meridian. Additional embodiments of PAL eyeglass lenses may be designed for custom or individual parameters desired by a wearer or practitioner (e.g., dimensions or locations of distance and progressive areas, as desired). PAL lenses may be asymmetrical, for example, for the left and right eyes, to accommodate changes in eye convergence and the resulting change in interocular distance when viewing from distance to near, or for user preferences for offsetting the object of gaze to one side while using a portion of the progressive power area. PAL eyeglass lenses may be designed with an amount of lateral separation, which may be distributed as desired between areas of the lens, such as between the top and bottom of the lens, between the distance and progressive areas, and within the progressive areas. The lateral separation may be distributed as desired and appropriate between the outer and inner surfaces to meet the ophthalmic needs of the wearer, practitioner, manufacturer, and / or manufacturing process. The design may be wholly or partially contained on the outer surface of the ophthalmic lens or on the inner surface of the ophthalmic lens. The lateral spacing of the optical axis may be wholly or partially contained in the semi-finished lens blank, and the final desired lens design may be completed in a final manufacturing process at the same or a different location and time once the patient's complete prescription is determined and ordered. The new design may be applied to appropriate manufacturing processes for other ophthalmic lenses, such as spectacle lenses, contact lenses, and intraocular lenses. In the case of spectacle lenses, such as PAL lenses, the lens may be fully molded or partially manufactured into a semi-finished blank or single-vision blank that includes a PAL surface on its outer or inner surface, or the PAL may be surfaced on the inner surface of the blank through a surface cutting and polishing process. The ophthalmic lenses may be configured and applied to improve manufacturing and supply chain efficiencies by reducing the inventory of semi-finished blanks or base curve blanks, or to reduce the need for unique asymmetric designs due to the increased field of view of the vision correction area.

[0290] The final spherical and cylindrical dioptric power and astigmatic power axes desired for a patient's refractive error can be achieved in a finishing process from a stock of semi-finished or unfinished lens blanks in a laboratory or office. The final lateral separation of the optical axes can also be achieved to the desired level during the finishing process, along with the progressive power profile, fitting height, and interpupillary distance required for optimal function in presbyopia and myopia. For example, residual prismatic power that may be present in semi-finished or finished lens blanks can be removed during the final processing of the spectacle lens. For example, prismatic power may be desired to be 0.12D or less, 0.25D or less, 0.5D or less, 1.5D or less, 3D or less, or more.

[0291] Extended Depth of Focus (EDOF) In some embodiments, the ophthalmic lenses described herein may provide an extended depth of focus (EDOF). In some embodiments, light rays passing through an ophthalmic lens and converging to form one or more off-axis foci may continue beyond one or more off-axis foci to provide an EDOF in combination with on-axis light rays. In some embodiments, light rays passing through an ophthalmic lens and converging to form one or more off-axis foci may continue beyond one or more off-axis foci to provide an EDOF with good image quality in combination with on-axis light rays. In some embodiments, a desired amount of EDOF may be achieved by having a desired amount of lateral focal separation between one or more on-axis foci and one or more off-axis foci, where the lateral focal separation between the on-axis and off-axis foci is achieved by incorporating an optically perpendicular surface configuration in the ophthalmic lens. In some embodiments, a desirable amount of EDOF can be achieved with an ophthalmic lens incorporating first and second optical zones, wherein the power profile of the second optical zone incorporates a relatively more negative power (m component) and a relatively more positive power (p component) than the power of the first zone, such that "m=p<+ / - 20%." In some embodiments, the EDOF is located substantially anterior to the retinal image plane.

[0292] 41 is a schematic diagram illustrating an ophthalmic lens 4100 having a first optical zone 4101 having a first power and at least one second zone 4102 concentric with the first optical zone, the second zone 4102 configured with a curvature (i.e., a curvature) referred to as a geometric normal to the base surface. The geometric characteristics of the normal to the base (herein, base refers to the first optical zone) surface can be used to configure or achieve a desired amount of lateral separation of the off-axis focus formed by the second optical zone 4102 from the on-axis focus formed by the first optical zone 4101. As shown in FIG. 41 , the geometric normal to the surface curvature is where the center of the second optical zone 4102, the center of curvature / arc of 4102, and the center of curvature of the first optical zone of the ophthalmic lens 4100 can lie along a single line. In some embodiments, there may be a predetermined amount of lateral separation of the optical axes of the first and second optical zones of a lens designed with a geometric normal to the surface features. Configuring the second optical zone 4102 as a geometric normal to the surface may result in the second optical zone being discontinuous (not a smooth transition) with the peripheral zones (e.g., the first optical zone and the third annular optical zone 4103).

[0293] 42 is a schematic diagram of the on-axis power profiles of the optical zones of an ophthalmic lens configured with a first central optical zone 4201 and an annular second optical zone 4202 configured geometrically normal to the base (i.e., central optical zone). As shown, the first optical zone 4101 may have a first power 4201 having a positive power greater than the eye's distance refractive error, such that light passing through the first optical zone can result in one or more focal points at a surface other than the retina of the eye and a third optical zone 4203 powered to provide an on-axis focus that coincides with the central zone focus. The second annular optical zone 4102 may incorporate a power profile 4202 having a more positive (“p”, 4202a) and / or more negative (“m”, 4202b) component relative to the first power 4201, and a progressive power profile component 4202c that increases in positive power from 4202d to 4202e. The difference in absolute power between 4202d and 4202e is the on-axis focal depth in diopters. The "m" component arises from the geometric normal to the discontinuity between the first optical zone and the innermost part of the second optical zone, and the "p" component arises from the geometric normal to the discontinuity between the outermost part of the second optical zone and the innermost part of the third optical zone, which provides a coaxial focal point coincident with the central zone. The progressive power profile 4202c in the second annular optical zone, which joins 4202d and 4202e, may be a sloped (e.g., curved, curvilinear, linear, or other) power profile depending on the surface configuration of the second optical zone and the lateral separation of the optical axes of the first and second optical zones. In the embodiment of FIG. 41, the ophthalmic lens is configured with geometric normals to the surface features that create the lateral separation between the on-axis and off-axis foci, resulting in an on-axis power profile that satisfies "m=p<approximately ±20%." An ophthalmic lens is determined to satisfy the "condition of being optically perpendicular to the surface" when "m=p<approximately ±20%."In some embodiments, the geometric normal to the surface features of the base may not result in a lens that satisfies a condition such as, for example, "m=p<approximately ±20%." Therefore, an ophthalmic lens configured to be optically perpendicular to the surface features provides better image quality. A larger difference between m and p increases the interference between on-axis and off-axis rays, impairing image quality along the depth of focus. In some embodiments, the location and diameter of the First Optical Zone may affect the m:p ratio. For example, a smaller central optical zone (e.g., <approximately 2 mm) may result in "m:p ratio > 20%" because the rays passing through the innermost part of the Second Optical Zone tend to flatten (become more parallel, resulting in a relatively larger negative power for "m" compared to the "p" component), thereby reducing the angle between these rays and the optical axis. When the rays intersect the optical axis, the "m" component may have a relatively larger negative power than the "p" component, potentially increasing the interference between on-axis and off-axis rays at the image plane along the depth of focus. Furthermore, for wider second optical zones, e.g., >1.5 to 2.0 mm or greater, the geometric normal to the surface features may not maintain the geometric normal to the surface features. As the zone width increases, the p component increases at the outermost periphery of the second optical zone, which may result in increased interference between on-axis and off-axis rays at the image plane along the depth of focus.

[0294] Thus, in exemplary embodiments described herein, to achieve a depth of focus that does not substantially affect image quality, a desired amount of lateral separation between the focal points from one or more first optical zones and one or more second optical zones is obtained by considering and incorporating one or more optically perpendicular surface features, including: a) substantially similar discontinuous surfaces at both edges of the second optical zones; b) m and p components of the one or more second optical zones, where the m:p component is < about ±20%, 1-20%, 1-5%, 5-10%, 10-15%, or about 10-20%; c) the location and width of the one or more second optical zones on the ophthalmic lens; and d) the width of the central optical zone on the ophthalmic lens.

[0295] In some embodiments, an ophthalmic lens configured to be optically perpendicular to a surface feature may comprise at least one first optical zone having a first axis, the at least one first optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one first optical zone to one or more first foci on the first axis; and at least one second optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one second optical zone to one or more foci. The one or more foci from the at least one second optical zone may not be on the first axis, and the second zone may be configured such that light converging to form the one or more foci continues or extends beyond the one or more foci to provide an extended depth of focus in combination with light rays from the first optical zone.

[0296] In some embodiments, at least one first optical zone of the ophthalmic lens optically perpendicular to the surface feature may comprise a first portion having a substantially circular shape located at a center of the ophthalmic lens and a second optical zone having a substantially annular shape located between the first portion of the first optical zone and the second portion of the first optical zone. The at least one first optical zone and the at least one second optical zone may be concentric (e.g., substantially concentric and / or partially concentric). In some embodiments, the ophthalmic lens may comprise alternating first and second optical zones. In some embodiments, the second optical zone may comprise one or more zones that are conjugate and may have varying power.

[0297] In some embodiments, at least one Second Optical Zone of the Ophthalmic Lens optically perpendicular to the surface feature may be configured such that, in use on an eye, light passing through the at least one Second Optical Zone is refracted to multiple (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, or 16) focal points rather than on a first axis. In some embodiments, the multiple focal points resulting from light passing through the at least one Second Optical Zone may form rings of successive foci surrounding the first axis and spaced apart from the first axis (e.g., having a substantially large and / or infinite number of foci). In some embodiments, the multiple focal points resulting from light passing through the at least one Second Optical Zone may form rings of successive foci surrounding the first axis and spaced apart from the first axis.

[0298] In some embodiments, one or more features of one or more Second Optical Zones of the Ophthalmic Lens optically perpendicular to the surface features may be configured such that light passing through the one or more Second Optical Zones and focusing to form one or more focal points continues or extends beyond the one or more focal points to provide an extended depth of focus in combination with light passing through the First Optical Zone. In some embodiments, one or more features of the Second Optical Zones, such as width, circumferential extent (e.g., arc or annular), curvature, number of zones, focal power and focal length of one or more focal points associated with one or more sections of the zones, location on the Ophthalmic Lens, base power of the Ophthalmic Lens, and extent and / or means of lateral separation between the First and Second Optical Zones, may affect the extended depth of focus provided by the Ophthalmic Lens.

[0299] In some embodiments, the one or more second optical zones may be between about 0.05 mm and 3 mm. For example, in some embodiments, the optical zone width may be about 0.05 mm, 0.1 mm, 0.15 mm, 0.2 mm, 0.3 mm, 0.4 mm, 0.5 mm, 0.6 mm, 0.7 mm, 0.75 mm, 0.8 mm, 0.9 mm, 1 mm, 1.25 mm, 1.5 mm, 1.75 mm, 2 mm, 2.25 mm, 2.5 mm, 2.75 mm, or 3 mm. In some embodiments, the ring width may be between about 0.05 and 2.0 mm, between about 0.1 mm and 2.0 mm, between about 0.2 and 0.5 mm, 0.5 and 0.75 mm, 0.75 and 1 mm, 1 and 1.5 mm, 1.25 and 1.75 mm, 1.5 and 2 mm, 1.75 and 2.25 mm, 2 and 2.5 mm, 2.25 and 2.75 mm, and / or 2.5 and 3 mm.

[0300] In some embodiments, the absolute power of the curvature of one or more second optical zones may be between about -10 and +10 D. For example, in some embodiments, the ring curvature may be about -10 D, -9 D, -8 D, -7 D, -6 D, -5 D, -4 D, -3 D, -2 D, -1 D, +1 D, +2 D, +3 D, +4 D, +5 D, +6 D, +7 D, +8 D, +9 D, and / or +10 D. As used herein, the term "curvature" may refer to a geometric curvature (or line) or a curvature (or line) that mathematically best fits the area or cross-section (power profile) of a surface of the lens.

[0301] In some embodiments, the lateral separation of the focal point from the first optical zone and the second optical zone may be between 0.2 and 2 mm. For example, the lateral separation of the focal point from the one or more first optical zones and the one or more second optical zones at the image plane can be about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, about 0.6 mm, about 0.65 mm, about 0.7 mm, about 0.75 mm, about 0.8 mm, about 0.85 mm, about 0.9 mm, about 1 mm, about 1.1 mm, about 1.2 mm, about 1.25 mm, about 1.3 mm, about 1.35 mm, about 1.4 mm, about 1.45 mm, about 1.5 mm, about 1.55 mm, about 1.6 mm, about 1.65 mm, about 1.7 mm, about 1.75 mm, about 1.8 mm, about 1.85 mm, about 1.9 mm, or about 2 mm. In some embodiments, the lateral separation of the focal point from the first optical zone and the second optical zone at the image plane may be less than or equal to about 50 μm, 60 μm, 70 μm, 80 μm, 90 μm, 0.1 mm, 0.15 mm, 0.2 mm, 0.25 mm, 0.3 mm, 0.35 mm, 0.4 mm, 0.45 mm, 0.5 mm, 0.55 mm, 0.6 mm, 0.7 mm, 0.75 mm, 0.8 mm, 0.85 mm, 0.9 mm, 0.95 mm, and / or 1 mm. In some embodiments, the lateral separation of the focal point from the one or more first optical zones and the one or more second optical zones at the image plane may be about 50 μm, 60 μm, 70 μm, 80 μm, 90 μm, 0.1 mm, 0.15 mm, 0.2 mm, 0.25 mm, 0.3 mm, 0.35 mm, 0.4 mm, 0.45 mm, 0.5 mm, 0.55 mm, 0.6 mm, 0.7 mm, 0.75 mm, 0.8 mm, 0.85 mm, 0.9 mm, 0.95 mm, and / or 1 mm or more.

[0302] FIG. 43 is a schematic diagram illustrating an exemplary embodiment of an ophthalmic lens incorporating a central optical zone 4301 surrounded by an annular zone 4302, where light rays passing through the annular zone 4302 result in one or more off-axis foci that interact with on-axis light rays from the central optical zone 4301. However, instead of a second optical zone comprised of curved surfaces as in the embodiment of FIG. 41, the embodiment of FIG. 43 uses straight lines to form the annular zone on the inner surface of the ophthalmic lens (FIG. 43A). As shown, the central zone power 4301 is a positive power that is greater than the refractive error of the eye, thereby allowing light passing through the first optical zone to result in one or more foci at a surface other than the retina of the eye and a third optical zone 4303 that is powered to provide an on-axis focus that coincides with the central zone focus. The second annular optical zone 4302 (FIG. 43B) may incorporate a power profile 4202 having a more positive (“p”, 4302a) and / or more negative (“m”, 4302b) component relative to the first power 4301, and a progressive power profile component 4302c that increases in positive power from 4302d to 4302e. The “m” arises from the geometric normal to the discontinuity plane between the first optical zone and the innermost part of the second optical zone, and the “p” component arises from the geometric normal to the discontinuity plane between the outermost part of the second optical zone and the innermost part of the third optical zone, which provides a coaxial focus coincident with the central zone. The progressive power profile of the second annular optical zone 4302c, which joins 4302d and 4302e, is a linear power profile. By configuring the inner surface of the ophthalmic lens in this manner, the innermost portion of the second optical zone forms a less positive power than the first, central zone, resulting in a power profile that is more positive (p) at the innermost portion of the second optical zone and less negative (m) at the outermost portion of the second optical zone. Consistent with the embodiment described in FIG. 42, since "m=p<approximately ±20%," the second optical zone is optically perpendicular to the surface, and the use of a straight line to form the second optical zone results in a desirable lateral separation of the foci between the first and second optical zones.

[0303] Figure 44 is a schematic diagram illustrating an ophthalmic lens, according to certain embodiments, incorporating a central optical zone (first optical zone 4401) surrounded by an annular zone (second optical zone 4404) to form an off-axis focal plane 4404a and an extended depth of focus 4403. Specifically, the ophthalmic lens of Figure 44 (A and B) has a central optical zone 4401 that forms a coaxial (high intensity) focal point 1A along an optical axis 4402 in front of a retinal image plane 4405, and an annular zone 4404 that has a relatively more positive power than the central zone 4401 and forms a non-coaxial focal point 5 (in some embodiments, the non-axial point leads to a defocus ring evaluated in 3D) at the image plane 4404a. Light rays passing through the inner 7, outer 8 and central 9 parts of the annular zone 4404 intersect the optical axis 4402 to form coaxial foci 10, 11 and 12 in front of the retina (10), between the front of the retina and the retinal surface (11), and at the retinal surface (12), respectively.

[0304] In some embodiments, focal points 10, 11, and 12 may be of lower light intensity than focal point 1A formed by light rays passing through first optical zone 4401, while in other embodiments, they may be of higher light intensity than focal point 1A. In some embodiments, the light intensities of focal points 10, 11, and 12 may be different from one another. In some embodiments, focal points 10, 11, and 12 may be equally spaced from one another, while in other embodiments, they may not be spaced from one another. In the embodiment of FIG. 44(B), focal points 10, 11, and 12 are substantially unequal in light intensity. Focus point 1A from central optical zone 4401 coincides with focus point 11 formed by central-most light ray 9 of annular zone 4404. Additionally, light rays passing through central zone 4401 form higher light intensity areas 13 and 14 at image planes 10B (in front of the retina) and 12B (on the retina) that are equal in size and intensity. Light rays passing through the annular zone 4404 to form coaxial focal points 10, 11 and 12 and light intensity areas 10A, 11A and 12A at image planes 10B, 11B and 12B actively interfere with light rays from the central zone 4401 to form coaxial focal point 1A and light intensity areas 13, 14 at image planes 10B and 12B to form a depth of focus 4403 extending from image plane 10B to 12B.

[0305] 44A and B, light rays passing through the annular zone 4404 form a relatively myopic (in front of the retina) off-axis focal plane 4404a that is in front of the focal point 1A formed by the central optical zone, although in some other embodiments, the off-axis focal plane 4404a may be in front of, behind, or substantially in the same plane as the image plane for light rays passing through the central optical zone 11B. Also, light rays continue and extend beyond the off-axis focal plane, forming a depth of field behind and in front of the central focal point 1A. In some embodiments, the depth of field 4403 may be completely in front of the central focal plane 11B or completely behind it. In some embodiments, part of the depth of field 4403 may be in front of the central focal point at 11B and part behind it. In some embodiments, the ratio of focal depth in front of and behind the central focus may be approximately 100:0 (completely in front of the central focus), 90:10, 80:20, 75:25, 70:30, 60:40, 50:50 (equal in front of and behind the central focus), 40:60, 30:70, 25:75, 20:80, 10:90, and / or 0:100 (completely behind the central focus).

[0306] The example shown in Figure 44 (A and B) creates a continuous depth of focus, which in some embodiments can be used to improve image quality in front of the retina compared to behind the retina, and therefore inhibit / slow / reduce the progression of myopia.

[0307] In some embodiments, the focal point formed by the central or first optical zone may be located on (or substantially on) the retinal image plane, in front of the retinal image plane, and / or behind the retinal image plane.

[0308] In some embodiments, light rays from the central optical zone 4401 may have a higher light intensity compared to light rays from the annular optical zone. By placing the higher-intensity light rays at the midpoints (e.g., midpoints of the depth of focus) of the near (most anterior) and far (most posterior or retinal) image planes, the effect of these light rays on the light spot characteristics may be substantially uniformly distributed across the planes encompassing the depth of focus (DOF). In some embodiments, this configuration can result in improved vision at various DOF ​​planes. Additionally, as shown in FIG. 44B , the light rays from the annular zone have a lower light intensity, which reduces or reduces detrimental effects at the near, intermediate, and / or far planes, and therefore does not affect or interfere with vision even when the light is distributed over a wider area. As shown, in this embodiment, the interference from light rays formed by the annular zone 4404 on the area of ​​light intensity at the surface most anterior to the retina (near surface 10B) is less than the interference on the area of ​​light intensity formed posteriorly (far surface 12B), so the image at the near surface may be better than the image at the far surface.

[0309] FIG. 45 is a schematic diagram of an ophthalmic lens incorporating a central optical zone 4501 surrounded by an annular zone 4502, where light rays passing through the annular zone 4502 interact with on-axis light rays 4501a to one or more off-axis foci 4502a, resulting in depth of focus. In FIG. 45, the inner surface of the annular optical zone 4502 has a relatively more negative power (steeper curvature) than the inner surface of the central zone 4501, resulting in the formation of an off-axis focal plane 4502b behind the central zone on-axis focus 4501a and the retinal image plane 4501b. The annular zone 4502 may be configured to be optically normal to its surface (the annular zone 4502 power profile provides "m = p < approximately ±20%," resulting in a) lateral separation of several off-axis foci from the on-axis focus, and b) light rays from the very center of the annular zone 4503a approximately coincide with the central zone focus 4501a so that they intersect the optical axis. Similarly, light rays from the innermost 4503b and outermost 4503c portions of the annular zone 4502 form endpoints of the depth of focus at 4506 and 4507 when they intersect the optical axis equidistant from the central zone focus 4501a. In this configuration, the depth of focus may be entirely intraocular (i.e., anterior to the retinal plane). However, because the sharp curvature of the inner surface of the lens results in an off-axis focal plane 4502b being formed behind the retina, no off-axis focus (or defocus ring) is formed in front of the retinal image plane. This configuration is desirable in some embodiments because it can improve image quality at the retinal image plane. In this embodiment, the lens has a lower light intensity at the off-axis focal point 4502a, and because the off-axis focal point is located posterior to the on-axis image point 4502a, there is less interference of light at A, potentially improving image quality. This differs from the example of FIG. 44, in which there is less interference of light rays at the light intensity area of ​​the innermost image plane 10B than at the retinal image plane 12B.

[0310] According to an embodiment, FIG. 46 is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone 4601 surrounded by an annular zone 4602 to form an off-axis focal plane and depth of focus. As shown, light passing through the central zone 4601 forms an on-axis focal point 4601a in front of the retinal image plane, and the central zone 4601 is surrounded by the annular zone 4602 having a flatter inner surface curvature (having a positive power greater than the central optical zone 4601 power). In some embodiments, the use of a flatter inner surface curvature for the annular zone 4602 may provide a positive power relative to the central optical zone 4601 power, providing results similar to the embodiment of FIG. 44. Thus, the off-axis focal plane 4602b is located in front of the central focal point 4601a, and the depth of focus 4610 can be located both in front of and behind the central focal point 4601a. Thus, as described herein, the curvature of the annular zone 4602 relative to the central zone 4601 can affect the location and depth of focus of the off-axis focal plane relative to the central focus. The exemplary ophthalmic lens of FIG. 46 includes similar properties to those of FIGS. 44A and 44B. For example, the ophthalmic lens includes a central optical zone 4601 having an on-axis focus 4601 a that is not formed on the retinal plane, and an annular zone configured to be optically perpendicular to the surface (the annular zone power profile provides "m = p < approximately ±20%)," resulting in a) lateral separation of one or more off-axis foci from one or more on-axis foci, and b) light rays 4602 a from the very center of the annular zone 4602 approximately coincide with the central zone focus 4601 a so that they intersect the optical axis. Similarly, light rays from the innermost 4602d and outermost 4602c portions of the annular zone 4602 form depth of focus endpoints at 4612 and 4611 when they intersect the optical axis equidistant from the central zone focus 4601a. ​​In this configuration, the depth of focus may be located entirely intraocularly (i.e., anterior to the retinal plane). In some embodiments, the configuration of the ophthalmic lens of FIG. 46, where the inner surface of the annular zone 4602 has a flatter curvature 4603 than the curvature of the central optical zone 4601, may be desirable as it reduces the sag difference between the optical zones and the surface is not recessed into the lens.Such a configuration may be less noticeable, therefore cosmetically appealing, and may increase compliance with lens wear. Additionally, in some embodiments, the flatter inner surface curvature of the annular zone 4602 may be more suitable for manufacturing processes such as freeform lens manufacturing, thereby reducing costs and increasing flexibility in lens manufacturing.

[0311] According to an embodiment, FIG. 47 is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone 4701 surrounded by an annular zone 4702 to form an off-axis focal plane and depth of focus. As shown, light passing through the central optical zone 4701 forms a focal point 4701a at the retinal image plane, and the annular zone 4702 may include an angled curvature such that the depth of focus 4710 is located entirely within the eye. Thus, this embodiment may provide different results than the embodiment of FIG. 44. For example, the central optical zone 4701 incorporates power to correct distance refractive error, so that the central focal point 4701a is located substantially at the retinal image plane 4712. The off-axis focal plane 4702b is located in front of the central focal point 4701a, but if the annular zone 4702 is not configured optically perpendicular to the surface (the power profile of the annular zone is such that m=p>approximately ±20%), the depth of focus 4710 may also be located more anterior to the central focal point 4701a. Thus, the lateral spacing of the off-axis focus 4702b from the on-axis focus 4701a can result in rays from the innermost 4702d of the annular zone 4702 nearly coinciding with the central zone focus 4701a as they intersect the optical axis at the retinal image plane. Here, rays from the retinal plane 4701a and rays from the outermost 4702c of the annular zone form the endpoints of the depth of focus at 4712 and 4711. Rays from the centralmost 4702a of the annular zone now intersect the optical axis equidistant from the endpoints of the depth of focus. In this configuration, the depth of focus of the illustrated embodiment can be located entirely intraocularly (i.e., in front of the retinal plane), but unlike FIG. 44, the central zone focus 4701a of FIG. 47 is at the retinal plane and does not coincide with the centralmost rays of the annular zone 4702 as they intersect the optical axis. The change in the power profile of the annular zone results in an m:p ratio where p>m, shifting the depth of focus more anteriorly in front of the retina and avoiding a focal point posterior to the retina. However, in some embodiments, this can result in increased interference of high intensity rays at the near image plane 4711, degrading image quality at the near image plane and potentially adversely affecting image quality at the far image plane 4712 (e.g., compared to the example described in FIG. 44).

[0312] According to an embodiment, FIG. 48 is a schematic diagram illustrating an ophthalmic lens 4800 having a central optical zone 4801 and an annular zone 4802 for forming one or more off-axis focal planes and depths of focus. The annular zone 4802 has three substantially similar combined curvatures 4802a, 4802b, and 4802c (as opposed to a single curvature). The combined curves transition the innermost and outermost portions of the curve to the base curve (the curvature of the first optical zone). For simplicity, we will discuss light rays passing through the first two combined curvatures 4802a, 4802b. Light rays passing through the central zone 4801 form an on-axis focal point 4801a at 4813a, located in front of the retinal image plane 4812a. Light rays passing through the combined curvatures 4802a and 4802b of the annular zone 4802 can form off-axis focal planes 4805a and 4805b and focal depths 4806a and 4806b, respectively. The combined curvatures of the annular zone 4802 are on the outer surface and may have a steeper curvature than the curvature of the central optical zone 4801 (resulting in a power zone 4802 that is relatively more positive than the central optical zone power). In some embodiments, each combined curvature can provide similar performance compared to the single curvature of the annular optical zone in FIG. 44. The off-axis focal planes 4805a and 4805b may be located in front of the central focal point 4801a, and the combined curvature focal depths 4806a and 4806b may be located to the left and right of the central focal point 4801a (i.e., both in front and behind). In some embodiments, the combined curvatures may be on the outer or inner surface, or on both surfaces. Additionally, as described herein, the curvature of the annular zone 4802 relative to the central optical zone 4801 can affect the position and depth of focus of the off-axis focal plane relative to the central focal point.As configured, light rays passing through central optical zone 4801 form an on-axis focus 4801a in front of the retinal surface, annular zone 4802 is composed of coupling curvatures 4802a and 4802b optically perpendicular to the surface (the power profile of each coupling curve provides "m = p < approximately ±20%)," light passing through annular zone 4802 results in off-axis foci 4805a and 4805b, and the lateral spacing of off-axis foci 4805a and 4805b from on-axis focus 4801a can result in light rays from the very center 4807a and 4807b of each coupling curve of the annular zone approximately coinciding with central zone focus 4801a so that they intersect the optical axis. Similarly, light rays passing through the innermost 4808a and 4808b and outermost 4809a and 4809b annular zones form the endpoints of a depth of focus at 4812a and 4811a when they intersect the optical axis equidistant from the central zone focus 4801a. In this configuration, the depth of focus 4806a and 4806b, according to the illustrated embodiment, may be located entirely intraocularly (i.e., anterior to the retinal plane). A close-up of the light rays intersecting the three image planes that form the depth of focus is shown in FIG. 48. The central zone focus 4801a is located at the intermediate image plane 4813a and is approximately coincident with the light rays 4809a, 4809b formed by the centralmost portions of the combining curvatures 4802a and 4802b. The near and far image planes 4811a and 4812a, and thus the depth of focus 4806a, from the first coupling curvature 4802a may be slightly longer than the depth of focus 4806b formed by the second coupling curvature 4802b between image planes 4813b and 4812b. However, the optical interference at image planes 4811(a and b), 4812(a and b), and 4813a from rays emanating from the central zone 4801 and the first coupling curvature (approximately a 5 mm aperture) may be similar to the optical interference at the same three image planes from rays from the central zone and both coupling curvatures combined (approximately a 7 mm aperture). In some embodiments, the slight difference in the depth of focus formed by the coupling curvatures 4802a and 4802b may be due to the more peripheral location of the second coupling curvature relative to the center of the lens. In some embodiments, the off-axis optical power of the combined curvatures may decrease as each curvature is located farther from the central zone.From this figure, it can be seen that as the width of the annular zone is increased, the combined curvature may continue to provide good image quality and depth of focus. A desirable feature of combining multiple annular curves is that a large area of ​​the annular optical zone surrounding the central optical zone can be devoted to extending depth of focus. The ophthalmic lens of FIG. 44 , in some embodiments, can provide optimal image quality for a 5 mm pupil size when the central optical zone 4401 has a diameter of 3 mm and the annular zone 4404 has a width of 1.0 mm. However, at larger pupil sizes, i.e., approximately 6 mm or greater, light rays may pass through the third optical zone of the ophthalmic lens of FIG. 44 (which has similar optical power to the central optical zone) and contribute an additional high intensity focus, increasing interference with image quality at the critical image plane. Additionally, in some embodiments, the lenses described in FIGS. 44A and 44B may also have a second annular zone surrounding the first annular ring that forms a coaxial focus that coincides with the focus formed by the central zone. When the pupil size is large, the coaxial light rays forming an on-axis focus from the second annular ring may be located within the pupil, increasing the area of ​​light intensity formed at the image plane (e.g., the retinal image plane). Therefore, in some embodiments, it may be advantageous to provide a wider annular zone than that provided in FIG. 44 . However, using a single curvature to widen the annular zone, e.g., to 0.50 mm or more or 1.50 mm or more, may increase light interference at various image planes and degrade image quality because the optically normal to the surface condition (i.e., the power profile of the annular zone providing m = p < approximately ±20%) may not be maintained in the wider annular optical zone. Therefore, to maintain good image quality in a larger annular optical zone, multiple combined annular zones with individual widths that substantially maintain the optically normal to the surface condition (i.e., m = p < approximately ±20%) may provide improved image quality and depth of focus. Thus, the exemplary embodiment of FIG. 48 can provide improved depth of focus and improved and consistent image quality, particularly for eyes with larger pupils or where variations in pupil size are significant (such as when illumination changes).

[0313] In some embodiments, the multiple combined curvatures of the Ophthalmic Lens of FIG. 48 can increase the depth of focus beyond that of a single-curvature annular optical zone. For example, the depth of focus created by combined curvatures 4802a, 4802b, and 4802c may be further extended by using a higher dioptric power, e.g., +4.00D, in each curvature. Thus, in some embodiments, the combined zone design of FIG. 48 can be applied to myopia treatment by extending the area and light intensity onto an image plane located in front of the retinal image plane. Similarly, in some embodiments, the multiple combined curvature annular zone can be applied to presbyopia correction. For presbyopia, the depth of focus required for distance and near vision may depend on the severity of the presbyopia. In early presbyopia, less depth of focus is required because the eye has sufficient residual accommodation to focus at intermediate distances up to 50 or 60 cm, whereas in advanced presbyopia, where little residual accommodation remains, a longer depth of focus may be required. Thus, in some embodiments, an annular optical zone consisting of only two combined curvatures may be sufficient for early or intermediate presbyopia, but for high-power presbyopia, three or more combined curvatures may be required. Furthermore, for advanced presbyopia, a longer depth of focus, extending from distance to 30-40 centimeters, may be required. By incorporating multiple combined curvatures and increasing the dioptric power of each curvature, additional depth beyond a single annular optical zone can be achieved. In this way, increasing the amount of combined curvature power and the area of ​​the combined curvature depth of focus can be achieved while maintaining optimal image quality at intermediate and near distances.

[0314] In some embodiments, the annular zone may have 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 combined curvatures. In some embodiments, multiple single curvatures positioned adjacent to each other can be used to form combined curvatures. In some embodiments, the design can form multiple myopia treatment surfaces (e.g., multiple off-axis focal surfaces). In some embodiments, one or more myopia treatment surfaces may not be located off-axis. In some embodiments, multiple myopia treatment surfaces can be utilized to add greater depth of focus for use in treating presbyopia and / or hypermyopia.

[0315]

[0316] 49(A and B) are schematic diagrams of an ophthalmic lens 4900 having a central optical zone 4901 and an annular zone 4902 for forming one or more off-axis focal planes and depths of focus, according to an embodiment. The annular zone 4902 has multiple infusion curvatures 4902a, 4902b, 4902c, and 4902d (as opposed to a single curvature), each having the same curvature except for 4902d, which has a wider, steeper curvature. An infusion curvature refers to a partial or incomplete ring whose innermost and outermost portions do not match the base surface (central optical zone) curvature, as opposed to, for example, a combined curvature, where the ring is complete and the innermost and outermost portions of the ring generally match (and may be symmetrical to) the base curvature. In some embodiments, an annular zone consisting of multiple infusion curves may have a first infusion where the innermost part of the first (innermost) infusion curve matches the base surface curvature and the outermost part of the last (outermost) infusion curve of the annular zone matches the base surface (or the surface of the next optical zone), but the infusion curves in between may not have a portion that matches the base surface curvature. In some embodiments, the first curve infusion may not be geometrically or optically perpendicular to the surface because its innermost part may be at the base surface, but its outermost part may not be geometrically or optically perpendicular to the surface as it transitions to the next infusion curve.

[0317] For ease of explanation, rays from first curvature infusion 4902a, second curvature infusion 4902b, and final curvature infusion 4902d will be described. Central zone 4901 forms an on-axis focal point 4901a in front of retinal image plane 4912b. Curvature infusions 4902a, 4902b, and 4902d may create off-axis focal planes 4905a, 4905b, and 4905d and focal depths 4906a, 4906b, and 4906d, depending on the specific embodiment. In this example, the curvature infusions of annular zone 4902 are on the outer surface and may have a curvature that is steeper than that of central optical zone 4901 (e.g., a more positive power than the central optical zone power). The shape and sagittal depth of the curvature infusions can be seen in magnification in 49-1 and are similar except for 4902c, as previously described. The degree of infusion between each curvature is determined by the amount of overlap between the curvatures, e.g., spacings 4914, 4915, and 4916. The degree of infusion in the annular zone 4902 between the first infusion 4902a and the second infusion 4902b (4914), between the third infusion 4916 and the final infusion, and between the second infusion and the third infusion (4915) is similar. In some embodiments, the degree of overlap controls the diameter, symmetry, and contribution of light rays that provide depth of focus and interference to the image plane formed by the Ophthalmic Lens 4900 of each infusion.

[0318] In some embodiments, such as in FIG. 49A , the off-axis focal planes formed by curvature infusions 4902a, 4902b, and 4902d may be located in front of the central focal point 4901a, and the focal depths 4906a, 4906b, and 4906d of each curvature infusion may be located both in front of and behind the central focal point 4901a. In some embodiments, the annular zone 4902 may be located on the inner surface of the ophthalmic lens and may have multiple curvature infusions and still produce similar or substantially similar results. Additionally, as described herein, the curvature of the annular zone relative to the central zone may affect the location and focal depth of the off-axis focal planes relative to the central focal point. In some embodiments, the spherical structures described herein may be utilized to achieve the features described herein, while in some embodiments, other techniques may be utilized.

[0319] As configured, the exemplary ophthalmic lens of FIG. 49A includes a central optical zone 4901 having an on-axis focal point 4901a that is not formed on the retinal plane (e.g., in front of the retinal plane), and annular zones made up of infusion curvatures 4902a, 4902b, and 4902d (where the power profile of each curvature provides "m=p<approximately ±20%), with only 4902b (and 4902c) optically perpendicular to the surface. Thus, in some embodiments, e.g., FIG. 49A, the first infusion curvature 4902a may have a power profile where "m:p>20%" i.e., not optically perpendicular to the surface, and similarly, the final infusion 4902d may have a similar and opposite power profile where "m:p>20%" and not optically perpendicular to the surface, as depicted in FIG. 49B.

[0320] As shown in Figure 49A, due to the lateral spacing of off-axis foci 4905a, 4905b, and 4905d from on-axis focus 4901a, only rays from the centermost portion 4907b of the second curvature infusion (4902b) may intersect the optical axis, approximately coinciding with central zone focus 4901a, resulting in a depth of focus of 4906b. Because infusion curvatures 4902a and 4902d are not configured optically normal to the surface, rays passing through the centermost portion of the infusion curvature do not intersect the optical axis at 4901a, but rather at 4917a and 4917d. The depths of focus formed by infusion curvatures 4902a and 4902d are 4906a and 4906d. In this configuration, the depth of focus for each infusion curvature of the ophthalmic lens 4900 may be located entirely within the eye (i.e., in front of the retinal plane). A close-up of the rays intersecting the image plane forming the depth of focus is shown in FIG. 49-1A. Each infusion curvature may form a different depth of focus. For example, the depth of focus 4906b of the second infusion curve configured perpendicular to the surface is shorter than the depth of focus 4906a formed by the first infusion curvature and the depth of focus 4906d formed by the second infusion curvature. Furthermore, neither of these depths of focus 4906a, 4906d are equidistant around the on-axis focus of the central zone 4901a. The depth of focus 4906a is longer and shifted more anteriorly, while 4906d is shifted more posteriorly but shorter than 4906a due to the infusion curvature being located further away from the lens center. Compared to the depth of focus 4906e formed by the annular zone with a single curvature, all of the depth of focus formed by the infusion curvatures are less extended.

[0321] The width of the infusion curve may be narrower than either multiple combined curves or an annular zone containing a single curvature, thus providing a shorter depth of focus per infusion curve section. However, in an ophthalmic lens formed with multiple appropriately configured narrow infusion curves, the total depth of focus may maintain or exceed that achieved with either a single annular zone or multiple combined zones. Thus, an ophthalmic lens incorporating multiple infusion curves in an annular zone is advantageous, similar to the example of FIG. 48, and in some embodiments, may provide further improvements. In some embodiments, the lateral separation of the off-axis focus from the on-axis focus achieved with an ophthalmic lens having multiple infusion curves may be the same or different. In some embodiments, the infusion curvatures may be created with substantially the same curvature or substantially different curvatures, or may include "straight lines" adjacently or interspersed between the curvatures. In some embodiments, all infusion curvatures may be configured with an optical power profile as shown in FIG. 49B , where all but the first and last infusion curvatures may satisfy the condition of optical normality to the surface, m = p < approximately ±20%. In some embodiments, the infusion curvatures may be adjusted to provide power profiles within a range of m and p ratios. In this manner, the narrow dimensions of the infusion curvatures provide lens designers with flexibility to provide desired image quality and depth of focus. For example, by utilizing multiple infusion curves, annular zones may be configured to provide power profiles that satisfy the condition of optical normality to the surface, m = p < approximately 20%, even if they are not geometrically perpendicular to the surface, thereby providing optimal depth of focus and image quality at each image plane with minimal interference between light rays. The ophthalmic lens may provide more beneficial visual acuity, for example, by providing a sufficiently extended depth of focus for advanced presbyopia or a consistent image quality for presbyopia with large pupils and wide variations in pupil size across different lighting conditions.In some embodiments, utilizing multiple infusion curvatures to form the annular zone can allow for the formation of a continuous surface with the central zone, while providing a continuous power profile substantially free of discontinuities.

[0322] In some embodiments, the annular zone may have 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 curved infusions. In some embodiments, multiple curved infusions may reduce the depth of focus provided by the annular zone, but may provide a more pupil-independent design. Multiple curved infusions may also increase the overall width of the annular zone without affecting the depth of field. In some embodiments, multiple curved infusions may also create designs that are optically non-perpendicular to the surface. In some embodiments, multiple curved infusions may have similar or identical optical characteristics. As shown in FIG. 49B, multiple curved infusions may also have different optical characteristics. For example, based on the normalized base lens aberration profile, the curved infusions may have different m and / or p power values. As shown in FIG. 49B, the power profile of the first (closest to the center) infusion curve may have a negative m power (m) that is significantly greater than the positive pa power. Similarly, the power profile of the last (farthest from the center) infusion curve D may have a negative power m (md) significantly less than the positive power pd, while the power profiles of the two middle (second and third) infusion curves B and C may have negative power m (mb and mc) approximately equal to the positive power pb and pc, respectively. Thus, the power profiles of infusion curves B and C are optically perpendicular to the surface. Furthermore, the positive and negative power profiles of the first infusion curve A may be longer than the power profiles of the second, third, and so on, infusion curves, e.g., curves B, C, and D. This can be caused by asymmetry in the infusion curve. A curve infusion is asymmetric when its innermost portion is at a different sagittal height than its outermost portion. As previously mentioned, the first and last infusion curves in Figure 49A are asymmetric and provide power values ​​of "m = p > ±20%."

[0323] According to an embodiment, FIG. 50 is a schematic diagram illustrating an ophthalmic lens 5000 having a central optical zone 5001 and an annular second optical zone 5002 for forming an off-axis focal plane and depth of focus. In some embodiments, the annular second optical zone 5002 may be formed utilizing a zero or substantially zero curvature surface (referred to herein as a rectilinear curvature), creating an annular zone 5002 with a positive power greater than the central optical zone power 5001. In some embodiments, the rectilinear curvature is combined with an outer surface curvature, such that the ophthalmic lens functions as a plano-convex lens, creating a desired off-axis image plane 5001b located in front of or behind the central optical zone focus 5001a (but in front of the retinal image plane 5001c). In some embodiments, this design may create a relatively equal amount of depth of focus, but using a much smaller annular width (e.g., by about 5, 10, or 15 factors for contact lens designs). In some embodiments, this design may also be used in combination with the infusion and / or conjugation curvatures described herein. While straight lines can be applied to all ophthalmic lenses, when used in contact lenses, the curvature of the line can be very narrow, e.g., 50 μm wide, and can result in very high off-axis power, e.g., >50 D, or even about 100 D. Light rays emerging from such an off-axis focus of power can be highly divergent, potentially reducing contrast despite the extended depth of focus. When applied to spectacle lenses, a line of about 1 mm can potentially provide off-axis power of about 5.0 D while still maintaining depth of focus.

[0324] In some embodiments, the ophthalmic lens 5000 can provide results similar to the lens of FIG. 44 (A and B) by using a straight line (aspherical torus) on the inner surface of the lens. In other words, some form of an aspherical torus rotating around the surface of the ophthalmic lens, according to certain embodiments, can increase the positive power of the annular optical zone relative to the central optical zone power required to create the off-axis focal plane and depth of focus. In some embodiments, an aspherical torus, such as a straight line, or a concentric, or a conjunct or infusion curve, or a line, or a line and a curve interspersed with the annular zone, may be utilized to achieve the features described herein, and in some embodiments, other techniques may be utilized. Thus, the off-axis focal plane 5001b is located in front of the central focal point 5001a, and the depth of focus 5006 can be located both in front of and behind the central focal point 5001a. Additionally, as described herein, the curvature of the annular zone relative to the central zone can affect the location of the off-axis focal plane and the depth of focus relative to the central focal point.

[0325] The exemplary ophthalmic lens of FIG. 50 includes similar features to those of FIG. 44 (A and B). For example, the ophthalmic lens includes a central optical zone 5001 having an on-axis focus 5001a that is not formed on the retinal plane (e.g., anterior to the retinal plane), and an annular zone 5002 configured such that the lateral separation of the on-axis focus from the off-axis focus is a straight line optically perpendicular to the inner surface (where the annular zone power profile provides m=p, < approximately ±20%), such that light rays 5002a from the centralmost portion of the annular zone approximately coincide with the central zone focus 5001a as they intersect the optical axis. Similarly, light rays from the innermost 5002b and outermost 5002c portions of the annular zone form the endpoints of a depth of focus 5006 when they intersect the optical axis equidistant from the central zone focus 5001a. In this configuration, the depth of focus, according to the illustrated embodiment, may be located entirely within the eye (i.e., anterior to the retinal plane).

[0326] According to an embodiment, FIG. 51A is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to form an off-axis focal plane and depth of focus, according to certain embodiments. As shown in this example, both surfaces of the annular optical zone of the lens may be formed utilizing surfaces with zero or substantially zero curvature (referred to herein as linear curvature). In some embodiments, this configuration may form a depth of focus in an area of ​​minimal light intensity from low-intensity annular zone light rays, thereby potentially resulting in better image quality. In some embodiments, this design may also reduce or eliminate the presence of an off-axis focal plane along the optical axis.

[0327] 51A is a schematic diagram illustrating an ophthalmic lens comprising a central optical zone 5101 that provides an on-axis focal point 5101a in front of the retinal surface, and an annular zone 5102 that surrounds the central optical zone, the curvature of the annular optical zone 5102 being formed by straight lines 5102a (e.g., flat lines or flatter lines than the central zone) on its outer surface and straight lines 5102b (e.g., flat lines or steeper lines than the central zone) on its inner surface, wherein light rays passing through the annular zone 5102 have no off-axis focusing power, thus resulting in light rays 5104a, 5104b, and 5104c passing through the annular zone 5102 traveling in straight paths that are parallel to the image planes 5111, 5113, and 5112. The off-axis rays intersect the optical axis and interact with on-axis rays from the central optical zone, resulting in a depth of focus 5106. The lens of this embodiment may not form an off-axis focus at the image plane along the focal depth 5106 that may increase light interference, and may not have light rays converging or diverging beyond the off-axis focus.

[0328] Because the annular zone 5102 is composed of straight lines that do not form any off-axis power, the annular zone is optically normal to the surface (where the annular zone on-axis power profile provides "m = p < approximately ±20%"). Rays 5104b from the centermost portion of the annular zone approximately coincide with the central zone focus 5101a as they intersect the optical axis. Similarly, rays from the innermost 5104c and outermost 5104a portions of the annular zone form depth of focus endpoints at 5107 and 5108 as they intersect the optical axis equidistant from the central zone focus 5101a. In this configuration, the depth of focus 5106, according to the illustrated embodiment, may be located entirely intraocularly (i.e., anterior to the retinal plane). The absence of off-axis power means that no off-axis focus (or defocus ring) is formed in front of or behind the retinal image plane. This configuration may be desirable in some embodiments because it may improve image quality at the image plane 5106 along the depth of focus, as the interference of light rays along the depth of focus may be less than in many embodiments, e.g., the ophthalmic lenses of Figures 44A and 44B.

[0329] FIG. 51B illustrates an exemplary power profile for a lens having a central zone and three areas within the annular zone formed by straight lines on the outer and inner surfaces. The ophthalmic lens simulated in FIG. 51B incorporates a 2.0 mm diameter central optical zone 5121 with an on-axis focus not formed on (e.g., in front of) the retinal plane, surrounded by an annular zone 5122 formed by three connecting lines 5123a, 5123b, and 5123c on the outer surface and 5124a, 5124b, and 5124c configured on the inner surface, forming a 3 mm wide annular optical zone with a 3 x 1 mm wide concentric annular optical zone of zero off-axis power. As described in FIG. 51A, light rays passing through the annular zone with no off-axis focusing power simply pass intersecting the optical axis and interact with on-axis light rays from the central optical zone 5121, resulting in a depth of focus 5206 with reduced optical interference at the image plane along the depth of focus. FIG. 51B shows a simulation of the sagittal power profile across a 6 mm aperture of the lens described in FIG. 51B. The 6 mm aperture can capture rays from the center and two of the three annular line regions. The power profile shows the on-axis power of the central zone 5122 and the on-axis power profile of the two annular concentric regions (innermost 5123a, middle 5123b) formed by the outer and inner lines. As shown, the exemplary design provides a depth of focus 5129 of approximately 1.5D. For both annular regions, p=m, < approximately ±20%, consistent with an optically perpendicular configuration to the surface in each region.

[0330] A desirable feature of forming annular portions with straight lines on both sides of the lens is that they create annular zones with no off-axis focusing power, resulting in a very comfortable fit. The width of the zones can be similar to or even wider than annular zones created with a single curve or multiple combined or infused curves. The absence of off-axis power means that no off-axis focus (or defocus ring) is formed in front of or behind the retinal image plane, reducing the interference of light rays at the image plane because there are no rays emanating from the off-axis ring defocus.

[0331] FIG. 52 compares the calculated through-focus retinal image quality (RIQ) between a) a commercially available lens having a central distance zone surrounded by alternating annular zones of greater positive coaxial lens power and distance power, referred to herein as a "coaxial lens design (CLD)," and b) the ophthalmic lens designs shown in FIGS. 44 and 51. The key parameters of the three lens designs are detailed in FIG. 52. The contact lens of FIG. 44 (FIG. 44CL) has a 3 mm central optical zone with optical power that is hyperopic (positive) for the eye's distance refractive error, and a 1 mm wide annular zone with an add power of +3.5D. The contact lens of FIG. 51 (FIG. 51BCL) has a 2 mm diameter central optical zone with optical power that is hyperopic (positive) for the eye's distance refractive error, surrounded by a 2 x 1 mm connecting annular zone with "plano" off-axis power configured with "straight lines" on both its outer and inner surfaces. The CLD has a 3.0 mm central optical zone power for the eye's distance refractive error, surrounded by three 1 mm diameter annular optical zones with a +2.00 D relative to the central optical zone power, alternating with the central zone power. All CLD optical zones are aligned coaxially with the optical axis. RIQs were calculated across a 5 mm pupil size for through-focus from -1.75 D (behind the retina) to +2.25 D (in front of the retina) (Figure 52). As shown, the RIQ of the CLD is bimodal, centered on two coaxial zone powers: a distance power centered on the retinal plane (RIQ = 0.34) and a +2.00 D add power anterior to the retinal image plane (RIQ = 0.38). The RIQ is significantly lower between the two peaks. In contrast, the lenses of Figures 44 and 51B have peak RIQs of 0.46 and 0.44, which are superior to the RIQ of the CLD over a wide range of vergence, indicating a true extended depth of focus with good RIQ.

[0332] In some embodiments, the ophthalmic lens may have a central zone refractive power equal to the eye's distance refractive error plus about 1.00 D for both myopia and presbyopia. In other embodiments, the central zone refractive power is equal to the eye's distance refractive error plus about 0.75 D, 0.50 D, or 0.25 D, and may be between about 1.00 D and 0.50 D, 0.75 D and 0.25 D, or 0.50 D and 0.25 D. In some embodiments, one or more refractive zones of the ophthalmic lens contribute to restoring vision to the eye. In some embodiments, the multiple refractive zones of the ophthalmic lens may include, in addition to the central zone, one of alternating angular rings (zones), conjugated annular rings, infusion rings, annular zones with flat lines, etc.

[0333] In some embodiments, the tilt of the annular zone relative to the central optical zone can be configured to provide the desired functionality in terms of off-axis focal planes, extended depth of focus, and good image quality. In some embodiments, the annular zone can have zero tilt when the curvature of the annular zone / ring is normal to the surface.

[0334] In some embodiments, the depth of focus provided by the Ophthalmic Lens may range from about 0.25D to 5.0D. For example, the depth of focus may be about 0.25D, 0.5D, 0.75D, 1D, 1.25D, 1.5D, 1.75D, 2D, 2.25D, 2.5D, 2.75D, 3D, 3.25D, 3.5D, 3.75D, 4D, 4.25D, 4.5D, 4.75D, and / or 5D. In some embodiments, the depth of focus may be about 1D or more, or 1.5D or more, and / or 2D or more. As discussed above, the depth of focus may be balanced or unbalanced relative to the on-axis focus. In some embodiments, a lens set is considered balanced if the depth of focus exists on either side of the on-axis focus (i.e., the on-axis focus is approximately at the midpoint of the range of depth of focus), where depth of focus is the distance between the larger positive focal plane closest to the anterior eye and the smaller focal plane farthest from the anterior eye. In some embodiments, the magnitude and location of the depth of focus can be controlled by the ring and / or annular zone width, the annular zone / ring power, and the central optical zone size of a given annular zone. Some embodiments may have a constant depth of focus across the range of central zone powers of the lens set, while other embodiments may have a range of depth of focus depending on the central optical zone power. In some embodiments, the patient's A set of lenses may be provided with a range of depths of focus for the management of myopia (e.g., myopia control with short, average, and long depths of focus to slow / inhibit / reduce axial progression of the eye). Some embodiments may have a lens set with a range of depths of focus that provides one or more depths of focus for the management of a patient (e.g., presbyopia may have short, average, and long depths of focus for addition correction). In some embodiments (e.g., presbyopia correction), the prescribed depth of focus may not be similar for both eyes of an individual. For example, in some embodiments, the depth of focus may be 1.0D in one eye and 2.0D in the other eye, or may be equal but offset from each other.For example, the depth of focus is 2D for both eyes, but the depth of focus for the non-dominant eye is positioned relatively further in front of the retina than the dominant eye, thereby expanding the depth of focus and the range of clear vision for near and intermediate distances as a measure against presbyopia. In some embodiments, the offset may be at least about 0.25D or more, or 0.5D or more, or about 1.5D or more, or about 2.50D or less.

[0335] In some embodiments, the off-axis foci may result in a ring focus, while in other embodiments, the off-axis foci may result in an incomplete ring. For example, the incomplete focus ring may have only a finite number of foci (every 0.5 degree, i.e., 720 foci, or every 1.0 degree, i.e., 360 foci, or every 2 degrees, i.e., 180 foci), which may result from the construction of the annular optical zone (the treatment zone is not a complete ring (e.g., a 10-degree or 15-degree arc includes all of the foci and / or a 10-degree or 15-degree arc has no foci); and / or the relevant zone on the ophthalmic lens is configured as a spiral, polygon, or any predetermined direction that forms a spiral, linear, continuous off-axis focus shape when viewed from the top surface of the lens.

[0336] As described herein, a desired surface profile of the annular zone may be provided on the outer surface (e.g., a positive elevated surface profile) and / or the inner surface (e.g., a negative recessed surface height), or both. In some embodiments, the surface profile of the annular zone may or may not be a spherical torus. In some embodiments, the surface profile of the annular zone may be infused. In some embodiments, the annular zone may have a concentric spherical curvature as part of the annular zone incorporating an infused ring. In some embodiments, the surface profile of the annular zone may be a cone. In some embodiments, the torus may be on the inner surface and may be equal and opposite to the outer surface (e.g., in a lens, where a tilt applied on the inner surface will shift the focus in the opposite direction than applying the exact tilt on the same curve on the outer surface).

[0337] In some embodiments, the ophthalmic lenses described herein may provide improved visual acuity as determined by any combination of overall visual acuity score, retinal image quality (RIQ) value, and / or through-focus image quality (TFIQ) visual acuity score.

[0338] In some embodiments, the ophthalmic lens may be comprised of a bonded annulus surrounding a central zone. In some embodiments, the ophthalmic lens may be comprised of an infused annulus surrounding a central zone. In some embodiments, the ophthalmic lens may have a central zone with a radius ranging from 1 mm to 8 mm (e.g., 1 mm, 2 mm, 3 mm, 4 mm, 5 mm, 6 mm, 7 mm, and / or 8 mm). In some embodiments, the central zone is about 3 mm or less, or about 0.5 mm or more.

[0339] In some embodiments, an ophthalmic lens may have a central optical zone and an annular optical zone comprised of a plurality of annular bodies, each of which may have a width in the range of 0.05 mm to 2 mm (e.g., 0.05 mm, 0.1 mm, 0.15 mm, 0.2 mm, 0.25 mm, 0.3 mm, 0.35 mm, 0.4 mm, 0.45 mm, 0.5 mm, 0.55 mm, 0.6 mm, 0.65 mm, 0.7 mm, 0.75 mm, 0.8 mm, 0.85 mm, 0.9 mm, 0.95 mm, 1 mm, 1.1 mm, 1.2 mm, 1.3 mm, 1.4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8 mm, 1.9 mm, and / or 2 mm). In some embodiments, the width of the annular body may be about 0.05 mm, 0.1 mm, 0.15 mm, 0.2 mm, 0.25 mm, 0.3 mm, 0.35 mm, 0.4 mm, 0.45 mm, 0.5 mm, 0.55 mm, 0.6 mm, 0.65 mm, 0.7 mm, 0.75 mm, 0.8 mm, 0.85 mm, 0.9 mm, 0.95 mm, 1 mm, 1.1 mm, 1.2 mm, 1.3 mm, 1.4 mm, 1.5 mm, 1.6 mm, 1.7 mm, 1.8 mm, 1.9 mm, and / or 2 mm or less. In some embodiments, the width may vary within the annular body, or the width may vary across individual annular bodies. In some embodiments, the width of each annular body is 2 mm or less and / or 1.5 mm or less. In some embodiments, the annular zone may have a slope of about 0. In some embodiments, the retinal image quality (RIQ) may be 0.4 or greater for a +2.0D relative power annulus.

[0340] The lens design sets Lens 1 and Lens 2 in Table 1 are designed with annular zones normal to the surface structure. Both Lenses 1 and 2 have a central optical zone and annular optical zone, with the annular optical zone having a relatively more positive power (referred to as ADD) than the central zone. The central optical zone of Lens 1 incorporates power to correct the eye's distance refractive error, while the central zone of Lens 2 does not have power to correct the eye's distance refractive error. Lens 1 is configured such that the annular zone power provides a constant relative positive power regardless of the central zone power; for example, the ADD power is constant and does not change with changes in central zone power. In comparison, the annular zone of Lens 2 can be configured to provide different amounts of relative positive power or ADD power across a power range relative to the central optical zone. Lens 2 may be configured to have different additions for each central zone power while maintaining two important criteria: the annular optical zones are designed to have geometric normals to the surface to achieve the desired amount of lateral separation, and further, the refractive correction of the eye is not based on the central optical zone power to correct the eye's distance refractive error. [Table 1] Table 1. Design examples when the power of the peripheral part depends on the power of the central optical part (Example 1) and when it does not (Example 2)

[0341] As described herein, the image quality at an image plane can be directly related to the characteristics of the light spot formed by light rays from optical zones located on the ophthalmic lens at one or more image planes. Thus, the optical quality of an ophthalmic lens can be a result of the interaction between the image qualities of the light spot formed across the infinite image plane formed between the lens and the final image plane. The cross-section of the light spot has a dimension in microns called the spot size. The light spot will also have a light intensity distribution across its diameter in the form of a range of stronger and weaker peaks. The Strehl ratio is an index of the light intensity distribution across the entire light spot, and is calculated as the ratio of the peak light intensity at a defined diameter of the spot image divided by the peak light intensity of an image formed by a diffraction-limited lens. Perfect image quality results in a ratio of 1, while poor image quality results in a ratio close to 0. The light spot at the image plane can be composed of all light rays passing through the image plane from on-axis and off-axis optical elements located within the lens aperture that form the image at the image plane. Thus, the light spot may include rays that converge at the image plane, any rays that converge toward a focal point behind the image plane, and any rays that diverge away from the focal point formed in front of the image plane of interest. Thus, the size and intensity distribution of the light spot at the image plane, and therefore the image quality, reflect the interference of low-intensity rays emanating from the off-axis optical zone with high-intensity rays formed by the on-axis optical zone at the image plane. The relative importance of light spot characteristics may vary depending on the optical design and application. Light intensity distribution may be an important characteristic in terms of improving ophthalmic lenses that benefit from extended depth of focus, such as for myopia prevention, presbyopia, and other applications.

[0342] Therefore, the light intensity distribution of the light spot formed on the image plane is important for image quality and needs to be defined.

[0343] In some embodiments, to optimize the image quality of the Ophthalmic Lens, the optical simulation indicates that the light distribution and positions of spots formed at multiple image planes should be defined, where a first image plane may be located at the retinal image plane, a second image plane may be located anterior to the retinal image plane, and collectively form a boundary of a depth of focus of at least 0.50D or more, while a third image plane may be located at the midpoint of the distance between the other two image planes.

[0344] Unexpectedly, it has been found that optimal image quality is achieved when high-intensity light rays from the central zone are focused at a third image plane rather than at the retinal image plane. Thus, in some embodiments, it is desirable for the high-intensity light rays forming the central zone to form defocused spot sizes at the first and second image planes without strong peaks, resulting in a lower Strehl ratio at both sides compared to the third image plane. Because the third image plane is located at the midpoint of the distance between the first and second image planes, the light distributions of the high-intensity spot sizes formed at the first image plane (from light rays converging at the third image plane) and the second image plane (from light rays diverging from the third image plane) are approximately equal and have approximately similar Strehl ratios.

[0345] Clinical observations of eyes wearing prototype contact lenses with different central optical zone sizes and powers, annular optical zone widths and powers, and m:p ratios determined that for a 5mm lens diameter, the optimal light intensity distribution of the light spots formed at the first and second image planes, as measured by the Strehl ratio, was 0.15 or less (e.g., <0.10 or 0.07 or less). Similarly, the optimal Strehl ratio at the third image plane was higher than that at the first and second image planes, e.g., <0.15, <0.10, and / or 0.07 or less. The m:p ratio of the power profile formed at the annular ring, as illustrated in several examples in Figures 44-51, has been shown based on optical simulations to be a control parameter that affects optical quality, i.e., m, approximately equal to p. The third image plane is located at the midpoint between the first and second image planes, and the m:p ratio is also equal. Clinical observations confirmed that optimal image quality was achieved when the m:p ratio was approximately 20% or less.

[0346] In some embodiments, the ophthalmic lenses described herein can be implemented in many ways for a variety of purposes, including as contact lenses and / or spectacle lenses for correcting and / or slowing myopia; presbyopia contact lenses (high, intermediate, low); lenses or anti-fatigue lenses; as single vision lenses; contact lenses for astigmatism; toric multifocal contact lenses; intraocular lenses, implantable contact lenses; corneal inlays, and for keratoplasty in refractive surgery.

[0347] The lens designs disclosed herein can be manufactured using any suitable ophthalmic lens manufacturing method. For example, contact lenses can be fully molded, spin-cast, or semi-molded, with one surface molded and the second surface formed through additional processes such as lathing the lens surface. Ophthalmic lenses can also be intraocular lenses with bifocal, trifocal, or multifocal power areas for distance vision correction and intermediate / near vision correction. Spectacle lenses can be manufactured entirely from molds, or by grinding, or by digital freeform processes. Semi-finished blanks or blank stocks with different base curves and parameters, including formed outer or inner surfaces, can be manufactured into a patient's final prescription with one or more of the benefits of the improved ophthalmic lenses described in one or more additional processing steps. For example, semi-finished ophthalmic lens blanks can have dimensions of at least 40 mm. In some embodiments, the semi-finished ophthalmic lens blank may have a diameter dimension of at least 55 mm, 60 mm, 70 mm, 75 mm, or more, may have a thickness greater than that of a final spectacle lens, may have an inner surface that is not the final shape or curvature of a finished spectacle lens that may be used on a patient, and may be used as a predecessor to a final spectacle lens. The semi-finished lens blank may require further processing so that a final ophthalmic lens having a final lens surface and thickness that corrects the wearer's final prescription can be molded to fit an eyeglass lens frame. The semi-finished lens blank or final ophthalmic lens may also include desired lens markings to enable further manufacturing steps, such as lens fitting or frame fitting. The lens markings may be laser engraved or added at an appropriate point in the manufacturing process. The outer surface of the ophthalmic lens in this example may be the same as the outer surface of the semi-finished blank so that the final lens for the patient will have the outer surface shape of the final prescription, and therefore the semi-finished lens blank may or may not include, or may already include, the application of any lens coatings for anti-reflective, anti-scratch, light-altering or light-filtering treatments, or color-altering or tinting of the lens.In this example, the semi-finished lens blank may require machining of the blank's inner surface to complete the final ophthalmic lens, and the final inner surface shape works in conjunction with the lens refractive index, outer lens surface curvature, lens treatment, and lens thickness to provide an ophthalmic lens with a number of final prescriptions and shapes for the patient's desired ametropia, including, but not limited to, spherical, cylindrical, cylinder axis, distal, prismatic, progressive addition, or multifocal power permutations. Improved spectacle lens designs can provide improved optical performance, including improved image quality, reduced oblique astigmatism or other distortions or aberrations, including cylinder power, and a wider field of view, regardless of monocular pupillary distance, fitting height, progression length, tetrahedron angle, pantoscopic tilt, or vertex distance.

[0348] One or more embodiments of the ophthalmic lenses disclosed herein may also be incorporated into suitable systems or processes, additional steps, treatments, or procedures to enhance the efficiency of lens manufacturing. One or more embodiments of the ophthalmic lenses disclosed herein may also be incorporated into the lens supply chain, from material production to lens design, lens molding, the application or inclusion of lens coatings and special features, or lens fitting into eyeglass frames. One or more embodiments of the ophthalmic lenses disclosed herein may be suitable for use with spectacle lenses with multiple foci, or other optical designs that may be inherently distorted and require improved image quality and / or visual acuity. For example, wrap frames may require special lens shapes, frame shapes, and highly curved surfaces. Laterally spaced optical axes can be applied to aberration control, including surface distortion, oblique astigmatism, and / or aberrations. Improved designs may benefit from including superior, inferior, lateral, or nasal spacing of the optical axis in Cartesian or polar coordinate systems, or combinations thereof, and may be designed with substantially seamless and / or substantially joint-free surface curvatures to manipulate lens power for desired optical performance. The final shape of exemplary embodiments of the ophthalmic lenses disclosed herein can be manufactured by any suitable process, including grinding, digital diamond turning, or digital freeform processes. For example, from a standard single vision lens, lens blank, or semi-finished blank having a final outer surface shape, the final lens design features can be designed to incorporate a patient's prescription to correct one or more of refractive error, presbyopia, myopia control, and other optical features to support the patient's requirements as prescribed by the practitioner, customized by the user, or both. Exemplary design embodiments can be used with digital surfacing algorithms from the manufacturer, such as Digital Ray Path Tracing (IOT, Madrid, Spain), either on the same surface or on a single surface.

[0349] In some embodiments, the first optical zone may have a substantially circular shape. In some embodiments, the first optical zone may be located at the center of the ophthalmic lens. In some embodiments, the first optical zone may have a substantially circular shape located at the center of the ophthalmic lens, and the second optical zone may have a substantially annular shape surrounding the first optical zone. In some embodiments, the first optical zone and the second optical zone may be substantially concentric. In some embodiments, the first optical zone and the second optical zone may be substantially concentric but may not share a common axis. In some embodiments, the first optical zone and / or the second optical zone may be rotationally symmetric or asymmetric about the first axis.

[0350] In some embodiments, the ophthalmic lens may be configured to be used to slow, reduce, or stop the progression of myopia in the eye. In some embodiments, the ophthalmic lens may be configured to be used for the correction of myopia. In some embodiments, the ophthalmic lens may be configured to be used for the correction of presbyopia.

[0351] In some embodiments, the ophthalmic lens may be a simultaneous vision lens. In some embodiments, the ophthalmic lens may be a simultaneous vision bifocal lens. In some embodiments, the ophthalmic lens may be a distance-centered bifocal lens. In some embodiments, the ophthalmic lens may be a distance-centered bifocal contact lens. In some embodiments, the ophthalmic lens may be a simultaneous vision multifocal lens. In some embodiments, the ophthalmic lens may be a split vision lens.

[0352] In some embodiments, the Ophthalmic Lens may be configured to correct any combination of distance, intermediate, and near vision.

[0353] In some embodiments, the ophthalmic lens may be one or more of a spectacle lens, a contact lens, a corneal onlay, a corneal inlay, an intraocular lens, a sheet or film that may be applied or attached to a spectacle lens.

[0354] Further advantages of the claimed subject matter will become apparent from the following examples that describe specific embodiments of the claimed subject matter. In certain embodiments, one or more (e.g., including all) of the following additional embodiments may include each of the other embodiments or portions thereof.

[0355] Example A: A1. An ophthalmic lens comprising: a first optical zone defined at least in part by a spherical surface having a first radius and having a first axis, wherein the first optical zone is configured, in use on an eye, to refract light passing through the first optical zone to a first focal point on the first axis; and a second optical zone defined at least in part by a spherical surface having a second radius different from the first radius, wherein the second optical zone is configured, in use on an eye, to refract light passing through the second optical zone to a second focal point (e.g., on the second axis); wherein the second focal point is offset from the first axis by an amount substantially equal to a central zone diameter of the ophthalmic lens.

[0356] Example B: B1. An ophthalmic lens comprising a plurality of optical zones (e.g., 2, 3, 4, or 5 optical zones) configured such that, in use on an eye, light passing through the plurality of optical zones is refracted to a corresponding plurality of one or more focal points on a corresponding plurality of axes; and at least two of the plurality of optical zones do not share a common axis.

[0357] C example: C1. An ophthalmic lens comprising at least one first optical zone having a first axis, the at least one first optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one first optical zone to a first focal point on the first axis; and at least one second optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one second optical zone to one or more focal points; wherein the one or more focal points from the at least one second optical zone are not on the first axis.

[0358] C2. The Ophthalmic Lens of any of Examples A, B, or C, wherein the at least one First Optical Zone and the at least one Second Optical Zone define an Optical Zone of the Ophthalmic Lens.

[0359] C3. The Ophthalmic Lens of any of Examples A, B, or C, wherein the at least one First Optical Zone and the at least one Second Optical Zone occupy a substantial portion of the Optical Zone of the Ophthalmic Lens (e.g., at least 90%, 95%, 98%, or 99% of the surface area of ​​the Optical Zone of the Ophthalmic Lens).

[0360] C4. The Ophthalmic Lens of any of Examples A, B, or C, wherein the Ophthalmic Lens is configured such that, in use on an eye, out-of-focus light associated with at least one first optical zone does not substantially interfere with a focal point associated with at least one second optical zone.

[0361] C5. The Ophthalmic Lens of any of Examples A, B, or C, wherein the Ophthalmic Lens is configured such that, in use on an eye, defocused light associated with the at least one Second Optical Zone does not substantially interfere with focal point associated with the at least one First Optical Zone.

[0362] C6. An ophthalmic lens of any of Examples A, B, or C, wherein the ophthalmic lens is configured such that, in use on the eye, interference with the focused focal point due to out-of-focus light is reduced, substantially reduced, or eliminated.

[0363] C7. The ophthalmic lens of any of Examples A, B, or C, wherein at least one first optical zone has a first optical power and at least one second optical zone has a second optical power different from the first optical power.

[0364] C8. The ophthalmic lens of any of Examples A, B, or C, wherein at least one first optical zone has a first optical power and at least one second optical zone has a positive second optical power that is relatively greater than the first optical power.

[0365] C9. The ophthalmic lens of any of Examples A, B, or C, wherein at least one first optical zone has a first optical power and at least one second optical zone has a positive second optical power that is relatively less than the first optical power.

[0366] C10. The ophthalmic lens of any of Examples A, B, or C, wherein at least one first optical zone is configured to correct one or more of distance vision, intermediate vision, and near vision, and / or at least one second optical zone is configured to correct a different one of distance vision, intermediate vision, or near vision.

[0367] C11. The ophthalmic lens of any of Examples A, B, or C, wherein at least one first optical zone is configured to correct distance vision and at least one second optical zone is configured to correct near vision.

[0368] C12. The ophthalmic lens of any of Examples A, B, or C, wherein at least one first optical zone is configured to correct near vision and at least one second optical zone is configured to correct distance vision.

[0369] C13. The ophthalmic lens of any of Examples A, B, or C, wherein the first axis passes through the first optical zone.

[0370] C14. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone occupies an upper portion of the optical zone and the at least one second optical zone occupies a lower portion of the optical zone.

[0371] C15. The Ophthalmic Lens of any of Examples A, B, or C, wherein the first axis is an axis of symmetry about which the optical zone of the Ophthalmic Lens is rotationally symmetric.

[0372] C16. The ophthalmic lens of any of Examples A, B, or C, wherein the first axis is the optical axis of at least one first optical zone.

[0373] C17. The ophthalmic lens of any of Examples A, B, or C, wherein the first focal point is on a first axis at a first distance from the ophthalmic lens, and the second focal point is at a second distance from the ophthalmic lens, the second distance being different from the first distance and offset from the first axis.

[0374] C18. The ophthalmic lens of any of Examples A, B, or C, wherein the second optical zone has a second axis associated with the second optical zone, the second axis being offset from the first axis.

[0375] C19. The Ophthalmic Lens of any of Examples A, B, or C, wherein the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens is about 0.5 mm (e.g., about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, about 0.6 mm, about 0.65 mm, about 0.7 mm, about 0.75 mm, about 0.8 mm, about 0.85 mm, about 0.9 mm, or 1 mm), or in some embodiments, the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens may be about 0.25 mm, about 0.5 mm, or about 0.75 mm.

[0376] C20. The Ophthalmic Lens of any of Examples A, B, or C, wherein the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens is about 0.5 mm or less (e.g., about 50 μm, about 60 μm, about 70 μm, about 80 μm, about 90 μm, about 0.1 mm, about 0.15 mm, about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, 0.55 mm, or about 0.6 mm or less), or in some embodiments, the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens may be about 0.1 mm, about 0.25 mm, or about 0.5 mm or less.

[0377] C21. The Ophthalmic Lens of any of Examples A, B, or C, wherein the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens is about 0.5 mm or less (e.g., about 50 μm, about 60 μm, about 70 μm, about 80 μm, about 90 μm, about 0.1 mm, about 0.15 mm, about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, 0.55 mm, or about 0.6 mm or less), or in some embodiments, the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens may be about 0.1 mm, about 0.25 mm, or about 0.5 mm or less.

[0378] C22. The Ophthalmic Lens of any of Example A, B, or C, wherein the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens is about 50 μm or more (e.g., about 50 μm, about 60 μm, about 70 μm, about 80 μm, about 90 μm, about 0.1 mm, about 0.15 mm, about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, 0.55 mm, or about 0.6 mm or more), or in some embodiments, the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens may be about 0.1 mm, about 0.25 mm, or about 0.5 mm or more.

[0379] C23. The ophthalmic lens of any of Examples A, B, or C, wherein the second focal point is on a second axis associated with at least one second optical zone, the second axis being offset from the first axis.

[0380] C24. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one second optical zone is configured such that, in use on an eye, light passing through the at least one second optical zone is refracted to a plurality of second foci, the plurality of second foci being on a corresponding one or more of a plurality of second axes associated with the at least one second optical zone, and the plurality of second axes being offset from the first axis.

[0381] C25. The ophthalmic lens of any of Examples A, B, or C, wherein at least one first optical zone has a substantially circular shape.

[0382] C26. The ophthalmic lens of any of Examples A, B, or C, wherein at least one first optical zone is located in the center of the ophthalmic lens.

[0383] C27. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone has a substantially circular shape located in the center of the ophthalmic lens, and the at least one second optical zone has a substantially annular shape surrounding the at least one first optical zone.

[0384] C28. The Ophthalmic Lens of any of Examples A, B, or C, wherein at least a portion of the at least one First Optical Zone has a substantially circular shape located in the center of the Ophthalmic Lens, and at least a portion of the at least one Second Optical Zone has a substantially annular shape surrounding the at least one First Optical Zone.

[0385] C29. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone comprises a first portion having a substantially circular shape located in a center of the ophthalmic lens and a second portion having a substantially annular shape surrounding the first portion.

[0386] C30. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one second optical zone comprises a first portion having a substantially annular shape surrounding the first optical zone and a second portion having a substantially annular shape surrounding the first portion.

[0387] C31. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone and the at least one second optical zone are concentric (e.g., substantially concentric and / or partially concentric).

[0388] C32. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone and the at least one second optical zone are substantially concentric but do not share a common axis.

[0389] C33. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone and / or the at least one second optical zone are rotationally symmetric about a first axis.

[0390] C34. The ophthalmic lens of any preceding claim, wherein at least one first optical zone directly abuts at least one second optical zone.

[0391] C35. The ophthalmic lens of any of Examples A, B, or C, wherein a blend zone is disposed between the at least one first optical zone and the at least one second optical zone.

[0392] C36. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone occupies 50% or more (e.g., about 55%, 60%, 65%, 70%, or 75%) of the surface area of ​​the optical zone of the ophthalmic lens.

[0393] C37. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone occupies 50% or less (e.g., about 45%, 40%, 35%, 30%, or 25%) of the surface area of ​​the optical zone of the ophthalmic lens.

[0394] C38. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone occupies about 60% (e.g., about 55%, 56%, 57%, 58%, 59%, 60%, 61%, 62%, 63%, 64%, or 65%) of the surface area of ​​the optical zone of the ophthalmic lens.

[0395] C39. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone occupies about 40% (e.g., about 35%, 36%, 37%, 38%, 39%, 40%, 41%, 42%, 43%, 44%, or 45%) of the surface area of ​​the optical zone of the ophthalmic lens.

[0396] C40. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone occupies about 75% or less (e.g., about 55%, 60%, 65%, 70%, or 75%) of the surface area of ​​the optical zone of the ophthalmic lens.

[0397] C41. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone occupies about 25% or more (e.g., about 25%, 30%, 35%, 40%, or 45%) of the surface area of ​​the optical zone of the ophthalmic lens.

[0398] C42. The ophthalmic lens of any of Examples A, B, or C, wherein at least one first optical zone is defined, at least in part, by a spherical surface having a first radius and / or at least one second optical zone is defined, at least in part, by a spherical surface having a second radius different from the first radius.

[0399] C43. The ophthalmic lens of any of Examples A, B, or C, wherein at least one first optical zone is defined, at least in part, by a spherical surface having a first radius and / or at least one second optical zone is defined, at least in part, by a spherical surface having a second radius that is smaller than the first radius.

[0400] C44. The ophthalmic lens of any of Examples A, B, or C, wherein at least one first optical zone is defined, at least in part, by a spherical surface having a first radius and / or at least one second optical zone is defined, at least in part, by a spherical surface having a second radius greater than the first radius.

[0401] C45. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone may be substantially circular in shape and have a diameter of about 3 mm (e.g., in some embodiments, the diameter may be about 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 2-4 mm, 2-3 mm, 3-4 mm, 4 mm or less, 3.5 mm or less, and / or 3 mm or less).

[0402] C46. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one second optical zone is substantially annular in shape and has an inner diameter of about 3 mm (e.g., in some embodiments, the inner diameter may be about 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 2-4 mm, 2-3 mm, 3-4 mm, 4 mm or less, 3.5 mm or less, and / or 3 mm or less), and may have an outer diameter of about 7 mm (e.g., in some embodiments, the outer diameter may be about 5 mm, 5.5 mm, 6 mm, 6.5 mm, 7 mm, 7.5 mm, 8 mm, 5-8 mm, 6-7 mm, 6-8 mm, 8 mm or less, 7.5 mm or less, and / or 7 mm or less).

[0403] C47. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one first optical zone is substantially circular in shape, the at least one second optical zone is substantially annular in shape, and the inner diameter of the at least one second optical zone is substantially equal to the diameter of the at least one first optical zone.

[0404] C48. The ophthalmic lens of any of Examples A, B, or C, wherein the location of the second focal point is determined, at least in part, by reducing and / or eliminating the slope of the outer surface of the second optical zone relative to the radius of curvature of the first optical zone.

[0405] C49. The ophthalmic lens of any of Examples A, B, or C, wherein the at least one second optical zone is configured such that, in use on an eye, light passing through the at least one second optical zone is refracted to multiple (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, or 16) focal points rather than on a first axis.

[0406] C50. The ophthalmic lens of any of Examples A, B, or C, wherein the ophthalmic lens is configured for use in slowing, reducing, or arresting the progression of myopia in the eye.

[0407] C51. The ophthalmic lens of any of Examples A, B, or C, wherein the ophthalmic lens is configured to be used for the correction of myopia.

[0408] C52. The ophthalmic lens of any of examples A, B, or C, wherein the ophthalmic lens is configured to be used to correct presbyopia.

[0409] C53. An ophthalmic lens according to any of the examples A, B, or C, wherein the ophthalmic lens is a simultaneous vision lens.

[0410] C54. The ophthalmic lens of any of Examples A, B, or C, wherein the ophthalmic lens is a split vision lens and / or a progressive addition multifocal (PAL) lens.

[0411] C55. The ophthalmic lens of any of examples A, B, or C, wherein the ophthalmic lens is one or more of a spectacle lens, a contact lens, a corneal onlay, a corneal inlay, and an intraocular lens.

[0412] DExample: D1. An ophthalmic lens comprising: at least one first optical zone having a first axis, the at least one first optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one first optical zone to a first focal point on the first axis; and at least one second optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one second optical zone to one or more focal points; wherein the at least one second optical zone is configured to provide an extended depth of focus for light extending beyond the one or more focal points.

[0413] D2. An ophthalmic lens comprising: at least one first optical zone having a first axis, the at least one first optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one first optical zone to a first focal point on the first axis; and at least one second optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one second optical zone to one or more focal points; wherein the at least one first optical zone is configured such that the first focal point is located anterior to the retinal surface, and the at least one second optical zone is configured such that light refracted to the first focal point, as well as light extending beyond the one or more focal points, provides an extended depth of focus.

[0414] D3. An ophthalmic lens comprising: at least one first optical zone having a first axis, the at least one first optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one first optical zone to a first focal point on the first axis; and at least one second optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one second optical zone to one or more focal points; wherein the at least one first optical zone is configured such that the first focal point is located anterior to the retinal surface, and the at least one second optical zone is configured such that light refracted to the first focal point, together with light extending beyond the one or more foci, provides an extended depth of focus extending from the retinal image plane to an anterior surface located anterior to the first focal point, where the first focal point is substantially equidistant from the anterior surface and the retinal surface.

[0415] D4. An ophthalmic lens comprising: at least one first optical zone having a first axis, the at least one first optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one first optical zone to a first focal point on the first axis; and at least one second optical zone configured, in use on an eye, to refract at least a portion of light passing through the at least one second optical zone to one or more focal points; wherein the at least one first optical zone is configured such that the first focal point is located anterior to the retinal surface, and the at least one second optical zone is configured to provide an extended depth of focus, with light refracted to the first focal point and light extending beyond the one or more focal points being located entirely within the eye.

[0416] D5. The ophthalmic lens of any of the examples of D, wherein the at least one first optical zone has a substantially circular shape and is centrally located on the ophthalmic lens, and the at least one second optical zone has a substantially annular shape surrounding the at least one first optical zone.

[0417] D6. The ophthalmic lens of any of the examples of D, wherein the at least one first optical zone and the at least one second optical zone are concentric.

[0418] D7. The ophthalmic lens of any of the examples of D, wherein the one or more foci located off-axis relative to the first focus have a finite number of foci (e.g., 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 180, 360, or 720 foci).

[0419] D8. The ophthalmic lens of any of the examples of D, wherein one or more foci located off-axis relative to the first focus have an infinite number of foci.

[0420] D9. The ophthalmic lens of any of the examples of D, wherein one or more focal points located off-axis relative to the first focal point are located on at least two focal planes (e.g., at least two, three, four, or five focal planes).

[0421] D10. The ophthalmic lens of any of the examples of D, wherein the number and location of the one or more foci is determined, at least in part, based on any combination of one or more of the width of the at least one second optical zone, the curvature of the at least one second optical zone, the location of the at least one second optical zone, the base power of the at least one second optical zone, and / or the lateral separation value of the at least one second optical zone.

[0422] D11. The Ophthalmic Lens of any of the examples of D, wherein the depth of focus provided by the Ophthalmic Lens is determined, at least in part, based on a width of the at least one second optical zone, a curvature of the at least one second optical zone, a position of the at least one second optical zone, a base power of the at least one second optical zone, a lateral separation value of the at least one second optical zone, and / or any combination of one or more of the m and p components.

[0423] D12. The ophthalmic lens of any example of D, wherein the at least one second optical zone has a substantially annular shape with a width between about 0.2 and 3 mm (e.g., about 0.2 mm, 0.3 mm, 0.4 mm, 0.5 mm, 0.6 mm, 0.7 mm, 0.75 mm, 0.8 mm, 0.9 mm, 1 mm, 1.25 mm, 1.5 mm, 1.75 mm, 2 mm, 2.25 mm, 2.5 mm, 2.75 mm, 3 mm, 0.2-0.5 mm, 0.5-0.75 mm, 0.75-1 mm, 1-1.5 mm, 1.25-1.75 mm, 1.5-2 mm, 1.75-2.25 mm, 2-2.5 mm, 2.25-2.75 mm, and / or 2.5-3 mm).

[0424] D13. The ophthalmic lens of any example of D, wherein at least one second optical zone has a substantially toroidal shape with a curvature of about -10 to +10D (e.g., about -10D, -9D, -8D, -7D, -6D, -5D, -4D, -3D, -2D, -1D, +1D, +2D, +3D, +4D, +5D, +6D, +7D, +8D, +9D, and / or +10D).

[0425] D14. The ophthalmic lens of any of the examples of D, wherein the at least one second optical zone has a substantially annular shape with a base power of about -20 to +20D (-20D, -19D, -18D, -17D, -16D, -15D, -14D, -13D, -12D, -11D, -10D, -9D, -8D, -7D, -6D, -5D, -4D, -3D, -2D, -1D, +1D, +2D, +3D, +4D, +5D, +6D, +7D, +8D, +9D, +10D, +11D, +12D, +13D, +14D, +15D, +16D, +17D, +18D, +19D, and / or +20D).

[0426] D15. The ophthalmic lens of any of the examples of D, wherein the at least one second optical zone has a substantially annular shape with a lateral separation value on the surface of the lens of between 0.2 and 1 mm (e.g., the lateral separation on the surface of the lens may be about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, about 0.6 mm, about 0.65 mm, about 0.7 mm, about 0.75 mm, about 0.8 mm, about 0.85 mm, about 0.9 mm, or 1 mm).

[0427] D16. The ophthalmic lens of any example of D, wherein the at least one second optical zone has a substantially annular shape with a lateral separation value on the surface of the lens of between 0.2 and 1 mm (e.g., the lateral separation on the surface of the lens may be equal to or less than about 50 μm, 60 μm, 70 μm, 80 μm, 90 μm, 0.1 mm, 0.15 mm, 0.2 mm, 0.25 mm, 0.3 mm, 0.35 mm, 0.4 mm, 0.45 mm, 0.5 mm, 0.55 mm, and / or 0.6 mm).

[0428] D17. The ophthalmic lens of any example of D, wherein the at least one second optical zone has a substantially annular shape with a lateral separation value on the surface of the lens of between 0.2 and 1 mm (e.g., the lateral separation on the surface of the lens may be about 50 μm, 60 μm, 70 μm, 80 μm, 90 μm, 0.1 mm, 0.15 mm, 0.2 mm, 0.25 mm, 0.3 mm, 0.35 mm, 0.4 mm, 0.45 mm, 0.5 mm, 0.55 mm, and / or 0.6 mm or more).

[0429] D18. The ophthalmic lens of any of the examples of D, wherein at least one focal plane is in front of, behind, or substantially in the same plane as the first focal point.

[0430] D19. The ophthalmic lens of any of the examples of D, wherein light rays extending beyond at least one focal plane form depths of focus behind and in front of the first focal point.

[0431] D20. The ophthalmic lens of any of the examples of D, wherein the ratio of the amount of depth of focus in front of the first focus to the amount of depth of focus behind the first focus may be approximately 100:0 (completely in front of the first focus), 90:10, 80:20, 75:25, 70:30, 60:40, 50:50 (equal in front of and behind the first focus), 40:60, 30:70, 25:75, 20:80, 10:90, and / or 0:100 (completely behind the first focus).

[0432] D21. The Ophthalmic Lens of any of the examples of D, wherein a cross section of at least one Second Zone has a focal length that is two-dimensional and independent from the remainder of the Ophthalmic Lens.

[0433] D22. The Ophthalmic Lens of any of the examples of D, wherein the at least one Second Zone is formed by adjusting the curvature of the base lens on at least one of the outer surface of the Ophthalmic Lens and / or the inner surface of the Ophthalmic Lens.

[0434] D23. The Ophthalmic Lens of any of the examples of D, wherein the at least one Second Zone is formed by adjusting the curvature of a base lens at the outer surface of the Ophthalmic Lens to form one of a plus optic zone or a minus optic zone.

[0435] D24. The Ophthalmic Lens of any of the examples of D, wherein the at least one Second Zone is formed by adjusting the curvature of the base lens on the interior surface of the Ophthalmic Lens to form one of a plus optic zone or a minus optic zone.

[0436] D25. The ophthalmic lens of any of the examples of D, wherein at least one second optical zone has a substantially annular shape including an oblique curvature to affect (e.g., shift) depth of focus.

[0437] D26. The ophthalmic lens of any example of D, wherein the at least one second optical zone has a substantially annular shape with multi-curve infusions (e.g., 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 curve infusions) having the same or different optical properties.

[0438] D27. The ophthalmic lens of any example of D, wherein the at least one second optical zone has a substantially toroidal shape with multiple combined curvatures (e.g., 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 combined curvatures).

[0439] D28. The ophthalmic lens of any example of D, wherein at least one second optical zone has a substantially annular shape formed by replacing at least one (or both) surface curvatures of the lens with straight lines (e.g., a surface with no or substantially no curvature).

[0440] D29. The depth of focus provided by the Ophthalmic Lens and / or the annular zone may range from about 0.25D to 5D (e.g., about 0.25D, 0.5D, 0.75D, 1D, 1.25D, 1.5D, 1.75D, 2D, 2.25D, 2.5D, 2.75D, 3D, 3.25D, 3.5D, 3.75D, 4D, 4.25D, 4.5D, 4.75D, and / or 5D), of any example Ophthalmic Lens of D.

[0441] D30. The Ophthalmic Lens of any of the examples of D, wherein the at least one first optical zone and the at least one second optical zone define an optical zone of the Ophthalmic Lens.

[0442] D31. The ophthalmic lens of any of the examples of D, wherein the at least one first optical zone and the at least one second optical zone occupy substantially all of the optical zone of the ophthalmic lens.

[0443] D32. The Ophthalmic Lens of any of the examples of D, wherein the Ophthalmic Lens is configured such that, in use on an eye, out-of-focus light associated with the at least one Second Optical Zone does not interfere with the focal point associated with the at least one First Optical Zone (e.g., does not substantially interfere with the focal point associated with the at least one First Optical Zone).

[0444] D33. The Ophthalmic Lens of any of the examples of D, wherein the Ophthalmic Lens is configured such that, in use on an eye, out-of-focus light associated with at least one first optical zone does not interfere with a focal point associated with at least one second optical zone (e.g., does not substantially interfere with a focal point associated with at least one second optical zone).

[0445] D34. The ophthalmic lens of any example of D, wherein the ophthalmic lens is configured such that, in use on the eye, interference with the focused focus caused by out-of-focus light is suppressed, reduced, substantially reduced, and / or eliminated.

[0446] D35. The ophthalmic lens of any of the examples of D, wherein at least one first optical zone has a first optical power and at least one second optical zone has one or more second optical powers different from (e.g., relatively positive or negative) the first optical power.

[0447] D36. The ophthalmic lens of any of the examples of D, wherein at least one first optical zone is configured to correct one of distance vision, intermediate vision, or near vision, and / or at least one second optical zone is configured to correct a different one of distance vision, intermediate vision, or near vision.

[0448] D37. The ophthalmic lens of any of the examples of D, wherein one of the at least one first optical zone and the at least one second optical zone is configured to correct distance vision, and the other optical zone is configured to correct near vision.

[0449] D38. The ophthalmic lens of any of the examples of D, wherein the first axis passes through the first optical zone.

[0450] D39. The ophthalmic lens of any of the examples of D, wherein the first axis is an axis of symmetry about which the optical zone of the ophthalmic lens is rotationally symmetric.

[0451] D40. The ophthalmic lens of any of the examples of D, wherein the first axis is the optical axis of the first optical zone.

[0452] D41. The Ophthalmic Lens of any of the examples of D, wherein the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens is about 0.5 (e.g., about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, about 0.6 mm, about 0.65 mm, about 0.7 mm, about 0.75 mm, about 0.8 mm, about 0.85 mm, about 0.9 mm or 1 mm).

[0453] D42. The Ophthalmic Lens of any of the examples of D, wherein the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens is about 0.5 mm or less (e.g., about 50 μm, about 60 μm, about 70 μm, about 80 μm, about 90 μm, about 0.1 mm, about 0.15 mm, about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, or about 0.6 mm or less).

[0454] D43. The Ophthalmic Lens of any of the examples of D, wherein the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens is about 0.5 mm or less (e.g., about 50 μm, about 60 μm, about 70 μm, about 80 μm, about 90 μm, about 0.1 mm, about 0.15 mm, about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, or about 0.6 mm).

[0455] D44. The Ophthalmic Lens of any of the examples of D, wherein the lateral separation of the first axis and the second axis at the surface of the Ophthalmic Lens is about 50 μm or more (e.g., about 50 μm, about 60 μm, about 70 μm, about 80 μm, about 90 μm, about 0.1 mm, about 0.15 mm, about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, or about 0.6 mm or more).

[0456] D45. The ophthalmic lens of any of the examples of D, wherein the at least one first optical zone and / or the at least one second optical zone are rotationally symmetric about the first axis.

[0457] D46. The ophthalmic lens of any of the examples of D, wherein at least one first optical zone directly abuts at least one second optical zone.

[0458] D47. The ophthalmic lens of any example of D, wherein the at least one first optical zone occupies 50% or more (e.g., about 55%, about 60%, about 65%, about 70%, or about 75%) of the surface area of ​​the optical zones of the ophthalmic lens.

[0459] D48. The ophthalmic lens of any of the examples of D, wherein at least one first optical zone is defined, at least in part, by a spherical surface having a first radius and / or at least one second optical zone is defined, at least in part, by a spherical surface having a second radius that is different (e.g., smaller or larger) than the first radius.

[0460] D49. The ophthalmic lens of any example of D, wherein the at least one first optical zone may be substantially circular in shape and have a diameter of about 3 mm (e.g., in some embodiments, the diameter may be about 2 mm, about 2.5 mm, about 3 mm, about 3.5 mm, about 4 mm, about 2-4 mm, about 2-3 mm, about 3-4 mm, about 4 mm or less, about 3.5 mm or less, and / or about 3 mm or less).

[0461] D50. The ophthalmic lens of any of the examples of D, wherein the at least one second optical zone may be substantially annular in shape and have an inner diameter of about 3 mm (e.g., in some embodiments, the inner diameter may be about 2 mm, about 2.5 mm, about 3 mm, about 3.5 mm, about 4 mm, about 2-4 mm, about 2-3 mm, about 3-4 mm, about 4 mm or less, about 3.5 mm or less, and / or about 3 mm or less) and an outer diameter of about 7 mm (e.g., in some embodiments, the outer diameter may be about 5 mm, about 5.5 mm, about 6 mm, about 6.5 mm, about 7 mm, about 7.5 mm, about 8 mm, about 5-8 mm, about 6-7 mm, about 6-8 mm, about 8 mm or less, about 7.5 mm or less, and / or about 7 mm or less).

[0462] D51. The ophthalmic lens of any of the examples of D, wherein the at least one first optical zone is substantially circular in shape and the at least one second optical zone is substantially annular in shape, and the inner diameter of the at least one second optical zone is substantially equal to the diameter of the at least one first optical zone.

[0463] D52. The ophthalmic lens of any of the examples of D, wherein the ophthalmic lens is configured for use in slowing, reducing, or stopping the progression of myopia in the eye.

[0464] D53. The ophthalmic lens of any of the examples of D, wherein the ophthalmic lens is configured to be used for the correction of myopia.

[0465] D54. The ophthalmic lens of any of the examples of D, wherein the ophthalmic lens is configured to be used to correct presbyopia.

[0466] D55. The ophthalmic lens of any of the examples of D, wherein the ophthalmic lens is a simultaneous vision lens.

[0467] D56. The ophthalmic lens of any of the examples of D, wherein the ophthalmic lens is a split vision lens and / or a progressive addition multifocal (PAL) lens.

[0468] It will be understood that the embodiments disclosed and defined herein extend to all alternative combinations of two or more individual features described or apparent in the text and drawings, all of which different combinations constitute various alternative aspects of the present disclosure.

[0469] The foregoing outlines features of several embodiments so that those skilled in the art may better understand aspects of the present disclosure. Those skilled in the art should readily appreciate that this disclosure may be used as a basis for designing or modifying other processes and structures to carry out the same purposes and / or achieve the same advantages of the embodiments presented herein. Those skilled in the art should also appreciate that such equivalent structures do not depart from the spirit and scope of the present disclosure, and that various changes, substitutions, and alterations can be made thereto without departing from the spirit and scope of the present disclosure. The present application provides the following aspects of the invention. (Aspect 1) at least one first optical zone having a first axis, the at least one first optical zone configured such that, in use on an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focal point on the first axis; and at least one second optical zone configured, in use on the eye, to refract at least a portion of light passing through the at least one second optical zone to one or more foci located off-axis with respect to the first focal point and on at least one focal plane different from a focal plane corresponding to the first focal point; An ophthalmic lens, wherein the at least one second optical zone is configured to provide an extended depth of focus for light extending beyond the one or more focal points. (Aspect 2) at least one first optical zone having a first axis, the at least one first optical zone configured such that, in use on an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focal point on the first axis; and at least one second optical zone configured, in use on the eye, to refract at least a portion of light passing through the at least one second optical zone to one or more foci located off-axis with respect to the first focal point and on at least one focal plane different from a focal plane corresponding to the first focal point; the at least one first optical zone is configured such that the first focal point is located anterior to the retinal plane; and An ophthalmic lens, wherein the at least one second optical zone is configured to provide an extended depth of focus for light refracted to the first focal point as well as light extending beyond the one or more focal points. (Aspect 3) at least one first optical zone having a first axis, the at least one first optical zone configured such that, in use on an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focal point on the first axis; and at least one second optical zone configured, in use on the eye, to refract at least a portion of light passing through the at least one second optical zone to one or more foci located off-axis with respect to the first focal point and on at least one focal plane different from a focal plane corresponding to the first focal point; the at least one first optical zone is configured such that the first focal point is located anterior to the retinal surface; and An ophthalmic lens, wherein the at least one second optical zone is configured such that light refracted to the first focal point, together with light extending beyond the one or more foci, provides an extended depth of focus extending from the retinal image plane to a front plane located in front of the first focal point at a position where the first focal point is substantially equidistant from the front plane and the retinal plane. (Aspect 4) at least one first optical zone having a first axis, the at least one first optical zone configured such that, in use on an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focal point on the first axis; and at least one second optical zone configured, in use on the eye, to refract at least a portion of light passing through the at least one second optical zone to one or more foci located off-axis with respect to the first focal point and on at least one focal plane different from a focal plane corresponding to the first focal point; the at least one first optical zone is configured such that the first focal point is located anterior to the retinal surface; and An ophthalmic lens, wherein the at least one second optical zone is configured to provide an extended depth of focus in which light refracted to the first focus, along with light extending beyond the one or more foci, is located entirely within the eye. (Aspect 5) An ophthalmic lens according to any one of Aspects 1 to 4, wherein the at least one first optical zone has a substantially circular shape and is located in the center of the ophthalmic lens, and the at least one second optical zone has a substantially annular shape surrounding the at least one first optical zone. (Aspect 6) Aspect 6. The ophthalmic lens of any one of Aspects 1 to 5, wherein the at least one first optical zone and the at least one second optical zone are concentric. (Aspect 7) The ophthalmic lens of any one of aspects 1 to 6, wherein the one or more foci located off-axis relative to the first focus have a finite number of foci (e.g., 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 180, 360, or 720 foci). (Aspect 8) The ophthalmic lens according to any one of aspects 1 to 7, wherein the one or more focal points located off-axis relative to the first focal point include an infinite number of focal points. (Aspect 9) The ophthalmic lens of any one of aspects 1 to 8, wherein the one or more focal points located off-axis relative to the first focal point are located on at least two focal planes (e.g., at least two, three, four, or five focal planes). (Aspect 10) An ophthalmic lens according to any one of aspects 1 to 9, wherein the number and position of the one or more foci are determined, at least in part, based on any combination of one or more of the width of the at least one second optical zone, the curvature of the at least one second optical zone, the position of the at least one second optical zone, the base power of the at least one second optical zone, and / or the lateral separation value of the at least one second optical zone. (Aspect 11) 11. The ophthalmic lens of any one of Aspects 1 to 10, wherein the depth of focus provided by the ophthalmic lens is determined, at least in part, based on a width of the at least one second optical zone, a curvature of the at least one second optical zone, a position of the at least one second optical zone, a base power of the at least one second optical zone, a lateral separation value of the at least one second optical zone, and / or any combination of one or more of the m and p components. (Aspect 12) 12. The ophthalmic lens of any one of Aspects 1 to 11, wherein the at least one second optical zone has a substantially annular shape with a width of between about 0.2 and 3 mm (e.g., about 0.2 mm, 0.3 mm, 0.4 mm, 0.5 mm, 0.6 mm, 0.7 mm, 0.75 mm, 0.8 mm, 0.9 mm, 1 mm, 1.25 mm, 1.5 mm, 1.75 mm, 2 mm, 2.25 mm, 2.5 mm, 2.75 mm, 3 mm, 0.2 to 0.5 mm, 0.5 to 0.75 mm, 0.75 to 1 mm, 1 to 1.5 mm, 1.25 to 1.75 mm, 1.5 to 2 mm, 1.75 to 2.25 mm, 2 to 2.5 mm, 2.25 to 2.75 mm, and / or 2.5 to 3 mm). (Aspect 13) 13. The ophthalmic lens of any one of Aspects 1 to 12, wherein the at least one second optical zone has a substantially annular shape with a curvature of about −10 to +10D (e.g., about −10D, −9D, −8D, −7D, −6D, −5D, −4D, −3D, −2D, −1D, +1D, +2D, +3D, +4D, +5D, +6D, +7D, +8D, +9D, and / or +10D). (Aspect 14) 14. The ophthalmic lens of any one of Aspects 1 to 13, wherein the at least one second optical zone has a substantially annular shape with a base power of about −20D to +20D (−20D, −19D, −18D, −17D, −16D, −15D, −14D, −13D, −12D, −11D, −10D, −9D, −8D, −7D, −6D, −5D, −4D, −3D, −2D, −1D, +1D, +2D, +3D, +4D, +5D, +6D, +7D, +8D, +9D, +10D, +11D, +12D, +13D, +14D, +15D, +16D, +17D, +18D, +19D, and / or +20D). (Aspect 15) 15. The ophthalmic lens of any of Aspects 1-14, wherein the at least one second optical zone has a substantially annular shape with a lateral separation value on the surface of the lens of between 0.2 and 1 mm (e.g., the lateral separation on the surface of the lens may be about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, about 0.6 mm, about 0.65 mm, about 0.7 mm, about 0.75 mm, about 0.8 mm, about 0.85 mm, about 0.9 mm, or 1 mm). (Aspect 16) 16. The ophthalmic lens of any of Aspects 1-15, wherein the at least one second optical zone has a substantially annular shape with a lateral separation value on the surface of the lens of between 0.2 and 1 mm (e.g., the lateral separation on the surface of the lens may be less than or equal to about 50 μm, 60 μm, 70 μm, 80 μm, 90 μm, 0.1 mm, 0.15 mm, 0.2 mm, 0.25 mm, 0.3 mm, 0.35 mm, 0.4 mm, 0.45 mm, 0.5 mm, 0.55 mm, and / or 0.6 mm). (Aspect 17) 17. The ophthalmic lens of any of Aspects 1-16, wherein the at least one second optical zone has a substantially annular shape with a lateral separation value on the surface of the lens of between 0.2 and 1 mm (e.g., the lateral separation on the surface of the lens may be about 50 μm, 60 μm, 70 μm, 80 μm, 90 μm, 0.1 mm, 0.15 mm, 0.2 mm, 0.25 mm, 0.3 mm, 0.35 mm, 0.4 mm, 0.45 mm, 0.5 mm, 0.55 mm, and / or 0.6 mm or more). (Aspect 18) 18. The ophthalmic lens according to any one of aspects 1 to 17, wherein the at least one focal plane is in front of, behind, or substantially in the same plane as the first focal point. (Aspect 19) 19. The ophthalmic lens according to any one of aspects 1 to 18, wherein the light rays extending beyond the at least one focal plane form a depth of focus behind and in front of the first focal point. (Aspect 20) 20. The ophthalmic lens of any of Aspects 1-19, wherein the ratio of the amount of depth of focus in front of the first focus to the amount of depth of focus behind the first focus may be about 100:0 (completely in front of the first focus), 90:10, 80:20, 75:25, 70:30, 60:40, 50:50 (equal in front of and behind the first focus), 40:60, 30:70, 25:75, 20:80, 10:90, and / or 0:100 (completely behind the first focus). (Aspect 21) 21. The ophthalmic lens of any of aspects 1-20, wherein a cross section of the at least one second zone has a focal length that is independent in two dimensions from the remainder of the ophthalmic lens. (Aspect 22) The ophthalmic lens according to any one of aspects 1 to 21, wherein the at least one second zone is formed by adjusting the curvature of the base lens on at least one of the outer surface of the ophthalmic lens and / or the inner surface of the ophthalmic lens. (Aspect 23) 23. The ophthalmic lens of any one of aspects 1 to 22, wherein the at least one second zone is formed by adjusting the curvature of the base lens at the outer surface of the ophthalmic lens to form one of a plus optic zone or a minus optic zone. (Aspect 24) 24. The ophthalmic lens of any one of aspects 1 to 23, wherein the at least one second zone is formed by adjusting the curvature of the base lens on the inner surface of the ophthalmic lens to form one of a plus optic zone or a minus optic zone. (Aspect 25) 25. The ophthalmic lens of any one of aspects 1 to 24, wherein the at least one second optical zone has a substantially annular shape including an oblique curvature to affect (e.g., shift) the depth of focus. (Aspect 26) 26. The ophthalmic lens of any of Aspects 1-25, wherein the at least one second optical zone has a substantially annular shape with multi-curve infusions (e.g., 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 curve infusions) having the same or different optical properties. (Aspect 27) 27. The ophthalmic lens of any of Aspects 1-26, wherein the at least one second optical zone has a substantially annular shape with multiple bond curvatures (e.g., 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 bond curvatures). (Aspect 28) 28. The ophthalmic lens of any of Aspects 1-27, wherein the at least one second optical zone has a substantially annular shape formed by replacing at least one (or both) surface curvatures of the lens with straight lines (e.g., a surface with no or substantially no curvature). (Aspect 29) 29. The ophthalmic lens of any of aspects 1-28, wherein the depth of focus provided by the ophthalmic lens and / or the annular zone may be in the range of about 0.25D to 5D (e.g., about 0.25D, 0.5D, 0.75D, 1D, 1.25D, 1.5D, 1.75D, 2D, 2.25D, 2.5D, 2.75D, 3D, 3.25D, 3.5D, 3.75D, 4D, 4.25D, 4.5D, 4.75D, and / or 5D). (Aspect 30) Aspect 30. The ophthalmic lens of any of aspects 1-29, wherein the at least one first optical zone and the at least one second optical zone define an optical zone of the ophthalmic lens. (Aspect 31) The ophthalmic lens of any of aspects 1-30, wherein the at least one first optical zone and the at least one second optical zone occupy substantially all of the optical zones of the ophthalmic lens. (Aspect 32) The ophthalmic lens of any of aspects 1-31, wherein the ophthalmic lens is configured such that, when used on the eye, defocused light associated with the at least one second optical zone does not interfere with a focus associated with the at least one first optical zone (e.g., does not substantially interfere with a focus associated with the at least one first optical zone). (Aspect 33) The ophthalmic lens of any of aspects 1-32, wherein the ophthalmic lens is configured such that, when in use on the eye, defocused light associated with the at least one first optical zone does not interfere with a focus associated with the at least one second optical zone (e.g., does not substantially interfere with a focus associated with the at least one second optical zone). (Aspect 34) 34. The ophthalmic lens of any one of aspects 1 to 33, wherein the ophthalmic lens is configured such that, when in use on the eye, interference at the in-focus focal point due to the out-of-focus light is suppressed, reduced, substantially reduced, and / or eliminated. (Aspect 35) The ophthalmic lens of any one of aspects 1 to 34, wherein the at least one first optical zone has a first optical power and the at least one second optical zone has one or more second optical powers different from the first optical power (e.g., relatively positive or negative). (Aspect 36) An ophthalmic lens according to any one of aspects 1 to 35, wherein the at least one first optical zone is configured to correct one of distance vision, intermediate vision, or near vision, and / or the at least one second optical zone is configured to correct a different one of distance vision, intermediate vision, or near vision. (Aspect 37) An ophthalmic lens according to any one of aspects 1 to 36, wherein one of the at least one first optical zone and the at least one second optical zone is configured to correct distance vision, and the other optical zone is configured to correct near vision. (Aspect 38) The ophthalmic lens of any one of aspects 1 to 37, wherein the first axis passes through the first optical zone. (Aspect 39) The ophthalmic lens according to any one of aspects 1 to 38, wherein the first axis is an axis of symmetry about which the optical zone of the ophthalmic lens is rotationally symmetric. (Aspect 40) 39. The ophthalmic lens according to any one of aspects 1 to 39, wherein the first axis is the optical axis of the first optical zone. (Aspect 41) The ophthalmic lens according to any one of aspects 1 to 40, wherein the lateral separation between the first axis and the second axis on the surface of the ophthalmic lens is about 0.5 (e.g., about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, about 0.6 mm, about 0.65 mm, about 0.7 mm, about 0.75 mm, about 0.8 mm, about 0.85 mm, about 0.9 mm, or 1 mm). (Aspect 42) The ophthalmic lens according to any one of aspects 1 to 41, wherein the lateral separation between the first axis and the second axis on the surface of the ophthalmic lens is about 0.5 mm or less (e.g., about 50 μm, about 60 μm, about 70 μm, about 80 μm, about 90 μm, about 0.1 mm, about 0.15 mm, about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, or about 0.6 mm or less). (Aspect 43) An ophthalmic lens according to any one of aspects 1 to 42, wherein the lateral separation between the first axis and the second axis on the surface of the ophthalmic lens is about 0.5 mm or less (e.g., about 50 μm, about 60 μm, about 70 μm, about 80 μm, about 90 μm, about 0.1 mm, about 0.15 mm, about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, or about 0.6 mm). (Aspect 44) An ophthalmic lens according to any one of aspects 1 to 43, wherein the lateral separation between the first axis and the second axis on the surface of the ophthalmic lens is about 50 μm or more (e.g., about 50 μm, about 60 μm, about 70 μm, about 80 μm, about 90 μm, about 0.1 mm, about 0.15 mm, about 0.2 mm, about 0.25 mm, about 0.3 mm, about 0.35 mm, about 0.4 mm, about 0.45 mm, about 0.5 mm, about 0.55 mm, or about 0.6 mm or more). (Aspect 45) The ophthalmic lens of any of aspects 1 to 44, wherein the at least one first optical zone and / or the at least one second optical zone are rotationally symmetric about the first axis. (Aspect 46) The ophthalmic lens of any of embodiments 1-45, wherein the at least one first optical zone is directly adjacent to the at least one second optical zone. (Aspect 47) 47. The ophthalmic lens of any of aspects 1-46, wherein the at least one first optical zone occupies 50% or more (e.g., about 55%, about 60%, about 65%, about 70%, or about 75%) of the surface area of ​​the optical zone of the ophthalmic lens. (Aspect 48) An ophthalmic lens according to any of aspects 1 to 47, wherein the at least one first optical zone is defined, at least in part, by a spherical surface having the first radius, and / or the at least one second optical zone is defined, at least in part, by a spherical surface having a second radius that is different (e.g., smaller or larger) than the first radius. (Aspect 49) The ophthalmic lens of any of Aspects 1-48, wherein the at least one first optical zone can be substan...

Claims

1. An ophthalmic lens, at least one first optical zone having a first axis, the at least one first optical zone configured such that, in use on an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focal point on the first axis; and at least one second optical zone configured, in use on the eye, to refract at least a portion of light passing through the at least one second optical zone to one or more foci located off-axis with respect to the first focal point and on at least one focal plane different from a focal plane corresponding to the first focal point; the at least one second optical zone is configured to provide an extended depth of focus for light extending beyond the one or more focal points; The ophthalmic lens, wherein the at least one second optical zone has an annular shape formed by at least one linear curvature formed on the inner and / or outer surface of the at least one second optical zone.

2. 10. The ophthalmic lens of claim 1, wherein the at least one first optical zone has a circular shape and is located at the center of the ophthalmic lens, and the at least one second optical zone has an annular shape surrounding the at least one first optical zone.

3. 3. The ophthalmic lens of claim 1, wherein the at least one first optical zone and the at least one second optical zone are concentric.

4. The ophthalmic lens according to any one of claims 1 to 3, wherein the one or more focal points located off-axis relative to the first focal point have a finite number of focal points.

5. The ophthalmic lens according to any one of claims 1 to 4, wherein the one or more foci located off-axis relative to the first focus have an infinite number of foci.

6. The ophthalmic lens according to any one of claims 1 to 5, wherein the one or more focal points located off-axis relative to the first focal point are located on at least two focal planes.

7. The ophthalmic lens of any one of claims 1 to 6, wherein the at least one second optical zone has an annular shape with a width between 0.05 and 3 mm.

8. 8. The ophthalmic lens of claim 1, wherein the at least one second optical zone has an annular shape with a curvature of -10 to +10D absolute power.

9. The ophthalmic lens according to any one of claims 1 to 7, wherein the at least one second optical zone has an annular shape with a power of -20 to +20D.

10. The ophthalmic lens of any one of claims 1 to 9, wherein the at least one focal plane is in front of, behind, or in the same plane as the first focal point.

11. An ophthalmic lens according to any one of claims 1 to 10, wherein the light extending beyond the at least one focal plane also forms a depth of focus behind and in front of the first focal point.

12. 12. An ophthalmic lens according to any one of claims 1 to 11, wherein the ratio of the amount of depth of focus before the first focus to the amount of depth of focus after the first focus may be 100:0, 90:10, 80:20, 75:25, 70:30, 60:40, 50:50, 40:60, 30:70, 25:75, 20:80, 10:90 and / or 0:

100.

13. The ophthalmic lens of any one of claims 1 to 12, wherein a cross section of the at least one second optical zone has a focal length that is independent in two dimensions from the remainder of the ophthalmic lens.

14. 14. The ophthalmic lens according to claim 1, wherein the linear curvature is formed on at least one of an outer surface of the ophthalmic lens and / or an inner surface of the ophthalmic lens.

15. 15. The ophthalmic lens according to claim 1, wherein the linear curvature is formed on an outer surface of the ophthalmic lens and is a plus optical zone or a minus optical zone.

16. 16. The ophthalmic lens of any one of claims 1 to 15, wherein the linear curvature is formed on an inner surface of the ophthalmic lens and forms one of a plus optic zone or a minus optic zone.

17. 17. The ophthalmic lens of any one of claims 1 to 16, wherein the at least one second optical zone has an annular shape including an oblique curvature to influence the depth of focus.

18. 18. The ophthalmic lens of any one of claims 1 to 17, wherein the at least one second optical zone has an annular shape with multi-curve infusions with the same or different optical properties.

19. The ophthalmic lens of any one of claims 1 to 18, wherein the at least one second optical zone has an annular shape with multiple conjugate curvatures.

20. An ophthalmic lens according to any of the preceding claims, wherein the depth of focus provided by the ophthalmic lens and / or the annular zone may be in the range of 0.25D to 5D.

21. The ophthalmic lens of any of claims 1 to 20, wherein the at least one first optical zone and the at least one second optical zone define an optical zone of the ophthalmic lens.

22. 22. The ophthalmic lens of any of claims 1 to 21, wherein the at least one first optical zone and the at least one second optical zone occupy all of the optical zones of the ophthalmic lens.

23. 23. The ophthalmic lens of any one of claims 1 to 22, wherein the ophthalmic lens is configured such that, when used on the eye, out-of-focus light associated with the at least one second optical zone does not interfere with the focal point associated with the at least one first optical zone.

24. 24. The ophthalmic lens of any one of claims 1 to 23, wherein the ophthalmic lens is configured such that, when used on the eye, out-of-focus light associated with the at least one first optical zone does not interfere with a focal point associated with the at least one second optical zone.

25. 25. An ophthalmic lens according to any one of claims 1 to 24, wherein the ophthalmic lens is configured such that, when used on the eye, interference at the focused focal point caused by the out-of-focus light is suppressed, reduced and / or eliminated.

26. 26. The ophthalmic lens of any one of claims 1 to 25, wherein the at least one first optical zone has a first optical power and the at least one second optical zone has one or more second optical powers different from the first optical power.

27. 27. An ophthalmic lens according to any one of claims 1 to 26, wherein the at least one first optical zone is configured to correct one of distance vision, intermediate vision or near vision, and / or the at least one second optical zone is configured to correct a different one of distance vision, intermediate vision or near vision.

28. 28. The ophthalmic lens of any one of claims 1 to 27, wherein one of the at least one first optical zone and the at least one second optical zone is configured to correct distance vision, and the other optical zone is configured to correct near vision.

29. An ophthalmic lens according to any preceding claim, wherein the first axis passes through the first optical zone.

30. An ophthalmic lens according to any one of claims 1 to 29, wherein the first axis is an axis of symmetry about which the optical zone of the ophthalmic lens is rotationally symmetric.

31. An ophthalmic lens according to any preceding claim, wherein the first axis is the optical axis of the first optical zone.

32. An ophthalmic lens according to any one of claims 1 to 31, wherein the at least one first optical zone and / or the at least one second optical zone are rotationally symmetric about the first axis.

33. 33. The ophthalmic lens of any of claims 1 to 32, wherein the at least one first optical zone is directly adjacent to the at least one second optical zone.

34. 34. The ophthalmic lens of any of claims 1 to 33, wherein the at least one first optical zone occupies 50% or more of the surface area of ​​the optical zone of the ophthalmic lens.

35. 35. An ophthalmic lens according to any one of claims 1 to 34, wherein the at least one first optical zone is defined, at least in part, by a spherical surface having a first radius, and / or the at least one second optical zone is defined, at least in part, by one or more curvatures having a second radius different from the first radius.

36. 36. The ophthalmic lens of any of claims 1 to 35, wherein the at least one first optical zone is circular in shape and has a diameter of less than 4 mm.

37. 37. The ophthalmic lens of any of claims 1 to 36, wherein the at least one second optical zone is annular in shape and has an inner diameter of 2 to 4 mm and an outer diameter of 5 to 8 mm.

38. 38. The ophthalmic lens of any one of claims 1 to 37, wherein the at least one first optical zone is circular in shape, the at least one second optical zone is annular in shape, and an inner diameter of the at least one second optical zone is equal to a diameter of the at least one first optical zone.

39. 39. An ophthalmic lens according to any preceding claim, wherein the ophthalmic lens is configured for use in slowing, reducing or stopping the progression of myopia in an eye.

40. 40. An ophthalmic lens according to any preceding claim, wherein the ophthalmic lens is configured to be used for the correction of refractive errors.

41. An ophthalmic lens according to any preceding claim, wherein the ophthalmic lens is configured for use in correcting presbyopia.

42. The ophthalmic lens according to any one of claims 1 to 41, wherein the ophthalmic lens is a simultaneous vision lens.

43. An ophthalmic lens according to any one of claims 1 to 42, wherein the ophthalmic lens is a split vision lens and / or a progressive addition multifocal (PAL) lens.

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