Ophthalmic lens for reducing, minimizing and / or eliminating interference of out-of-focus light on focused images

Abstract

The present disclosure relates to ophthalmic lenses for reducing, minimizing and / or eliminating interference of out-of-focus light on focused images. An ophthalmic lens comprising: at least one first optical region having a first axis, the at least one first optical region configured such that, when used with an eye, at least a portion of light passing through the at least one first optical region is refracted to a first focal point on the first axis; and at least one second optical region configured such that, when used with the eye, at least a portion of light passing through the at least one second optical region is refracted to one or more focal points, the one or more focal points are positioned 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; wherein the at least one second optical region is configured such that light extending beyond the one or more focal points provides an extended depth of focus.

Description

[0001] This application is a divisional application of an application with a priority date of August 23, 2019, an application date of August 21, 2020, an application number of 202080072954.7, and an invention name of “Ophthalmic lens for reducing, minimizing and / or eliminating interference of out-of-focus light on focused images”.

[0002] CROSS-REFERENCE TO RELATED APPLICATIONS

[0003] This disclosure claims priority to U.S. Provisional Application No. 62 / 890,809, filed on August 23, 2019. The priority application is incorporated herein by reference in its entirety. This disclosure is also related to International Application No. PCT / AU2017 / 051173, filed on October 25, 2017, and International Application No. PCT / IB2020 / 056079, filed on June 26, 2020. Each of these related applications is incorporated herein by reference in its entirety. Technical Field

[0004] The present disclosure relates to ophthalmic lenses, and more particularly, to ophthalmic lenses for controlling, reducing, minimizing and / or eliminating interference of out-of-focus images with focused images to change (eg, improve) retinal image quality. Background Art

[0005] The optics of the eye determine whether an image is focused on the retina of the eye. Images that are focused on or near the retina of the eye are generally considered to have good or acceptable image quality. Images that are out of focus, substantially away from the retina of the eye (perhaps focused in front of or behind the retina) are generally considered to be blurry, having reduced image quality. Myopia, commonly referred to as shortsightedness, is an optical disorder of the eye and causes on-axis images to be focused in front of the retina. On-axis images are those that are substantially in line with the fovea or foveal area of ​​the retina (the area where highest visual acuity is achieved). Presbyopia is an optical disorder of the eye in which the accommodative ability of the lens is reduced, resulting in blurred vision at distances close to the eye.

[0006] Ophthalmic lenses may be designed to correct distance vision, intermediate vision, and / or near vision by providing one or more focal points from one or more optical zones. Ophthalmic lenses with multiple zones (e.g., synoptic lenses) may result in impaired vision because light passing through such lenses results in overlapping images due to the focal point from one optical zone being interfered with by the focal points from other optical zones, thus, resulting in a reduction in the quality and / or contrast of the retinal image.

[0007] Therefore, there is a need for an ophthalmic lens for controlling, reducing, minimizing, and / or eliminating interference of out-of-focus images with focused light (e.g., focused images) 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 have other advantages and / or improvements as discussed herein. The present disclosure is intended to address these and other issues disclosed herein. The present disclosure is also intended to point out one or more advantages of using the exemplary ophthalmic lenses described herein. Summary of the invention

[0008] The present disclosure is directed, at least in part, to overcoming and / or ameliorating one or more of the problems described herein.

[0009] The present disclosure relates, at least in part, to ophthalmic lenses for controlling the interference of out-of-focus light with a focused image to improve image quality.

[0010] The present disclosure relates, at least in part, to ophthalmic lenses for controlling the overlap of out-of-focus images with focused images to extend depth of focus.

[0011] The present disclosure relates, at least in part, to ophthalmic lenses for controlling the overlap of one or more focal points at a given image plane with the focal points of one or more out-of-focus images or rays by spacing or shifting the focal points associated with the image at the given image plane and the focal points associated with the one or more out-of-focus images or rays.

[0012] The present disclosure relates, at least in part, to ophthalmic lenses for controlling the overlap of one or more on-axis focal points with one or more off-axis light rays to improve image quality and / or extend depth of focus.

[0013] The present disclosure relates, at least in part, to an ophthalmic lens for controlling the overlap of one or more focal points of a focused image at a given image plane with one or more focal points of an out-of-focus image, wherein the control is performed by spacing and / or shifting one or more focal points associated with the focused image at the image plane and one or more focal points associated with the out-of-focus image using one or more optical spacing devices.

[0014] The present disclosure relates, at least in part, to an ophthalmic lens for controlling the overlap of one or more focal points of a focused image and one or more focal points associated with an out-of-focus image at a given image plane by spacing and / or shifting the one or more focal points associated with the focused image and the one or more out-of-focus images using one or more lateral spacing optical devices.

[0015] The present disclosure relates, at least in part, to an optical spacing device for spacing and / or shifting a focus associated with a focused image at a given image plane and a focus associated with one or more out-of-focus images or rays using one or more optical surfaces comprising two or more optical elements (e.g., spherical, elliptical, conical, aspherical, or other suitable elements, including aspherical toric elements, such as lines, conical surfaces), wherein the two or more optical elements are positioned, offset, rotated, tilted, or shifted relative to each other such that all or some of the two or more optical elements do not share a common optical axis.

[0016] The present disclosure relates, at least in part, to laterally spaced optical devices for spacing and / or shifting a focus associated with a focused image at a given image plane and a focus associated with one or more out-of-focus images or rays using one or more optical surfaces, wherein the optical surfaces comprise two or more optical elements (e.g., spherical, elliptical, conical, aspherical, or other suitable elements, including aspherical toric elements, such as lines, conical surfaces), wherein the two or more optical elements are positioned, offset, rotated, tilted, or shifted relative to each other such that all or some of the two or more optical elements do not share a common optical axis.

[0017] The present disclosure relates, at least in part, to an exemplary apparatus configured, when in use, to space and / or shift at least one focal point associated with a focused image at a given image plane and a focal point associated with one or more out-of-focus images or rays using one or more optical surfaces, wherein the optical surfaces comprise two or more optical elements (e.g., spherical, elliptical, conical, aspherical, or other suitable elements, including aspherical toric elements, such as lines, conical surfaces), wherein the two or more optical elements are positioned, offset, rotated, tilted, or shifted relative to each other such that all or some of the two or more optical elements do not share a common optical axis.

[0018] The present disclosure relates, at least in part, to ophthalmic lenses for improving image quality.

[0019] The present disclosure relates, at least in part, to ophthalmic lenses for improving image contrast.

[0020] The present disclosure relates, at least in part, to an ophthalmic lens for improving the quality of a focused image at a given image plane by controlling an overlap of a focus associated with the focused image at the given image plane and a focus associated with one of a plurality of out-of-focus images.

[0021] The present disclosure relates, at least in part, to an ophthalmic lens for improving the quality of a focused image at a given image plane by controlling an overlap of a focus associated with the focused image at the given image plane and a focus associated with one of a plurality of out-of-focus images, wherein the improvement may 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).

[0022] The present disclosure relates, at least in part, to ophthalmic lenses that include one or more optical zones that do not share a common optical axis.

[0023] The present disclosure relates, at least in part, to ophthalmic lenses that include multiple optical zones or segments, wherein the optical axes for the multiple optical zones or segments are independent of each other and do not share a common axis.

[0024] The present disclosure relates, at least in part, to ophthalmic lenses comprising multiple optical zones or segments, wherein shifting of the optical axes of the multiple optical zones or segments can create prismatic power.

[0025] The present disclosure relates, at least in part, to an ophthalmic lens comprising a plurality of optical zones or segments, wherein a shift of an optical axis of the plurality of optical zones or segments relative to one of the other optical axes of the plurality of optical zones or segments creates a shift of about 0.05Δ diopters to about 15 prismatic diopters (Δ) (e.g., about 0.025Δ, about 0.05Δ, about 0.075Δ, about 0.1Δ, about 0.125Δ, about 0.15Δ, about 0.175Δ, about 0.2Δ, The prism power is about 0.25Δ, about 0.3Δ, about 0.35Δ, about 0.4Δ, about 0.45Δ, about 0.5Δ, about 0.6Δ, about 0.7Δ, about 0.8Δ, about 0.9Δ, about 1Δ, about 2Δ, about 3Δ, about 4Δ, about 5Δ, about 6Δ, about 7Δ, about 8Δ, about 9Δ, about 10Δ, about 11Δ, about 12Δ, about 13Δ, about 14Δ, about 15Δ, about 16Δ, about 17Δ, or about 18Δ).

[0026] The present disclosure relates, at least in part, to an ophthalmic lens comprising: a first optical zone, the first optical zone being at least partially defined by a sphere having a first radius and having a first axis, the first optical zone being configured such that, when used with an eye, light passing through the first optical zone is refracted to a first focus on the first axis; and a second optical zone, the second optical zone being at least partially defined by a sphere having a second radius different from the first radius and being configured such that, when used with an eye, light passing through the second optical zone is refracted to a second focus (e.g., on a second axis); wherein the amount by which the second focus is displaced relative to the first axis is substantially equal to a central zone diameter of the ophthalmic lens.

[0027] The present disclosure relates, at least in part, to an ophthalmic lens comprising: a plurality of optical zones (e.g., 2, 3, 4, or 5 optical zones), the plurality of optical zones being configured such that, when used 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; wherein at least two of the plurality of optical zones do not share a common axis.

[0028] The present disclosure relates, 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 being configured such that, when used with an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focus on the first axis; and at least one second optical zone being configured such that, when used with 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 one or more focal points from the at least one second optical zone are not on the first axis.

[0029] In some embodiments, the first focal power may be uniform or may vary in different portions of the first optical zone. In some embodiments, an ophthalmic lens may include a third optical zone having a third focal power. In some embodiments, the third optical zone may be one or more concentric zones proximate 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 of the lens occupied by the first and second optical zones.

[0030] In some embodiments, at least one first optical zone and at least one second optical zone can define an optic zone of the ophthalmic lens.

[0031] In some embodiments, at least one first optical zone and at least one second optical zone may occupy a majority (eg, substantially all) of the optic zone of the ophthalmic lens.

[0032] 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 optic zone of the ophthalmic lens.

[0033] In some embodiments, an ophthalmic lens can be configured such that, when used with an eye, out-of-focus light associated with the at least one second optical zone does not substantially interfere with the focus associated with the at least one first optical zone.

[0034] In some embodiments, an ophthalmic lens can be configured such that, when used with an eye, out-of-focus light associated with at least one first optical zone does not substantially interfere with focus associated with at least one second optical zone.

[0035] In some embodiments, an ophthalmic lens can be configured such that, when used with an eye, interference from out-of-focus light at a focused focal point is controlled.

[0036] In some embodiments, at least one first optical zone can include a first optical power and at least one second optical zone can include one or more second optical powers different from the first optical power.

[0037] In some embodiments, at least one first optical zone can include a first optical power and at least one second optical zone can include a second optical power that is relatively more positive than the first optical power.

[0038] In some embodiments, at least one first optical zone can include a first optical power and at least one second optical zone can include a second optical power that is relatively less positive than the first optical power.

[0039] In some embodiments, at least one first optical zone can be 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.

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

[0041] In some embodiments, at least one first optical zone together with a second optical zone is configured to correct one or more of: distance vision, intermediate vision, and near vision.

[0042] In some embodiments, at least one first optical zone can be configured to correct near vision and at least one second optical zone can be configured to correct distance vision.

[0043] In some embodiments, at least one first optical zone can occupy an upper portion of the viewing zone and a second optical zone can occupy a lower portion of the viewing zone.

[0044] In some embodiments, the first axis may be an axis of symmetry about which the optic zone of the ophthalmic lens is rotationally symmetric.

[0045] In some embodiments, the first axis can be an optical axis of the at least one first optical zone.

[0046] In some embodiments, the first focal point may be at a first distance from the ophthalmic lens on the first axis and the second focal point may be at a second distance from the ophthalmic lens, the second distance different from the first distance and displaced relative to the first axis.

[0047] In some embodiments, the second optical zone can have a second axis associated with the second optical zone that is displaced relative to the first axis.

[0048] In some embodiments, the lateral spacing of the first axis and the second axis on the surface of the ophthalmic lens can 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 about 1 mm). In some embodiments, the lateral spacing of the first axis and the second axis on the surface of the ophthalmic lens can be about 0.25 mm, about 0.5 mm, or about 0.75 mm. In some embodiments, the lateral spacing of the first axis and the second axis on the surface of the ophthalmic lens can 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.

[0049] In some embodiments, the lateral separation of the first axis and the second axis on the surface of the ophthalmic lens can be less than about 0.5 mm (e.g., less than about 50 um, about 60 um, about 70 um, about 80 um, about 90 um, 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). In some embodiments, the lateral separation of the first axis and the second axis on the surface of the ophthalmic lens can be less than about 0.1 mm, about 0.25 mm, or about 0.5 mm.

[0050] In some embodiments, the lateral separation of the first axis and the second axis on the surface of the ophthalmic lens may be greater than about 50 um (e.g., greater than about 50 um, about 60 um, about 70 um, about 80 um, about 90 um, 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). In some embodiments, the lateral separation of the first axis and the second axis on the surface of the ophthalmic lens may be greater than about 0.1 mm, about 0.25 mm, or about 0.5 mm.

[0051] In some embodiments, at least one first optical zone can have a substantially circular shape.

[0052] In some embodiments, at least one first optical zone is located at the center of the ophthalmic lens.

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

[0054] In some embodiments, at least a portion of at least one first optical zone may have a substantially circular shape located at the center of the ophthalmic lens, and at least a portion of at least one second optical zone has a substantially annular shape surrounding the at least one first optical zone.

[0055] In some embodiments, at least one first optical zone may include a first portion having a substantially circular shape located at the center of the ophthalmic lens; and a second portion having a substantially annular shape surrounding the first portion.

[0056] In some embodiments, the at least one second optical zone can include 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.

[0057] In some embodiments, at least one first optical zone and at least one second optical zone can be concentric (eg, substantially concentric, and / or partially concentric).

[0058] In some embodiments, at least one first optical zone and at least one second optical zone can be substantially concentric but not share a common axis.

[0059] In some embodiments, at least one first optical zone and / or at least one second optical zone can be rotationally symmetric about a first axis.

[0060] In some embodiments, at least one first optical zone can directly contact at least one second optical zone.

[0061] In some embodiments, a hybrid zone can be located between at least one first optical zone and at least one second optical zone.

[0062] In some embodiments, at least one first optical zone may occupy greater than 50% (eg, approximately 55%, 60%, 65%, 70%, or 75%) of the surface area of ​​the optic zone of the ophthalmic lens.

[0063] In some embodiments, the at least one first optical zone may occupy less than 50% (eg, approximately 45%, 40%, 35%, 30%, or 25%) of the surface area of ​​the optic zone of the ophthalmic lens.

[0064] In some embodiments, at least one first optical zone can occupy approximately 60% (e.g., approximately 55%, 56%, 57%, 58%, 59%, 60%, 61%, 62%, 63%, 64%, or 65%) of the surface area of ​​the optic zone of the ophthalmic lens.

[0065] In some embodiments, at least one first optical zone can occupy approximately 40% (e.g., approximately 35%, 36%, 37%, 38%, 39%, 40%, 41%, 42%, 43%, 44%, or 45%) of the surface area of ​​the optic zone of the ophthalmic lens.

[0066] In some embodiments, at least one first optical zone may occupy less than about 75% (eg, about 55%, 60%, 65%, 70%, or 75%) of the surface area of ​​the optic zone of the ophthalmic lens.

[0067] In some embodiments, at least one first optical zone may occupy greater than about 25% (eg, about 25%, 30%, 35%, 40%, or 45%) of the surface area of ​​the optic zone of the ophthalmic lens.

[0068] In some embodiments, at least one first optical zone can be at least partially defined by a sphere having a first radius and / or at least one second optical zone can be at least partially defined by a sphere having a second radius different than the first radius.

[0069] In some embodiments, at least one first optical zone can be at least partially defined by a sphere having a first radius and / or at least one second optical zone can be at least partially defined by a sphere having a second radius that is smaller than the first radius.

[0070] In some embodiments, at least one first optical zone can be at least partially defined by a sphere having a first radius and / or at least one second optical zone can be at least partially defined by a sphere having a second radius greater than the first radius.

[0071] In some embodiments, at least one first optical zone can be substantially circular in shape and have a diameter of about 3 mm (e.g., in some embodiments, the diameter can be about 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 2-4 mm, 2-3 mm, 3-4 mm, less than 4 mm, less than 3.5 mm, and / or less than 3 mm).

[0072] In some embodiments, at least one second optical zone can be substantially annular in shape and have an inner diameter of about 2 mm (e.g., in some embodiments, the inner diameter can be about 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 2-4 mm, 2-3 mm, 3-4 mm, less than 4 mm, less than 3.5 mm, and / or less than 3 mm) and an outer diameter of about 7 mm (e.g., in some embodiments, the outer diameter can 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, less than 8 mm, less than 7.5 mm, and / or less than 7 mm).

[0073] In some embodiments, the at least one first optical zone can be 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.

[0074] In some embodiments, the position of the second focal point can be determined at least in part by reducing and / or eliminating a tilt of an anterior surface of the second optical zone relative to a radius of curvature of the first optical zone.

[0075] In some embodiments, the second optical zones can be configured such that, when used with 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 that are not on the first axis.

[0076] The present disclosure relates, at least in part, to ophthalmic lenses having extended depth of focus.

[0077] The present disclosure relates, 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 being configured such that, when used with an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focus on the first axis; and at least one second optical zone being configured such that, when used with 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, the one or more focal points being positioned off-axis relative to the first focal point and on at least one focal plane different from the focal plane corresponding to the first focus; wherein the at least one second optical zone is configured such that light extending beyond the one or more focal points provides an extended depth of focus.

[0078] The present disclosure relates, 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 being configured such that, when used with an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focus on the first axis; and at least one second optical zone being configured such that, when used with 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, the one or more focal points being positioned off-axis relative to the first focus and on at least one focal plane different from the focal plane corresponding to the first focus; wherein the at least one first optical zone is configured such that the first focus is positioned anterior to a retinal plane; and wherein the at least one second optical zone is configured such that light extending beyond the one or more focal points together with light refracted to the first focus provides an extended depth of focus.

[0079] The present disclosure relates, 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 being configured such that, when used with an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focus on the first axis; and at least one second optical zone being configured such that, when used with 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 positioned off-axis relative to the first focus and on at least one focal plane different from the focal plane corresponding to the first focus; wherein the at least one first optical zone is configured such that the first focus is positioned in front of a retinal plane; and wherein the at least one second optical zone is configured such that light extending beyond the one or more focal points together with light refracted into the first focus provides an extended depth of focus extending from a retinal image plane to an anterior plane positioned in front of the first focus at a position that causes the first focus to be substantially equidistant from the anterior plane and the retinal plane.

[0080] The present disclosure relates, 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 being configured such that, when used with an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focus on the first axis; and at least one second optical zone being configured such that, when used with 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 positioned off-axis relative to the first focus and on at least one focal plane different from the focal plane corresponding to the first focus; wherein the at least one first optical zone is configured such that the first focus is positioned anterior to a retinal plane; and wherein the at least one second optical zone is configured such that light extending beyond the one or more focal points, together with light refracted to the first focus, provides an extended depth of focus that is completely within the eye.

[0081] In some embodiments, at least one first optical zone has a substantially circular shape and is located at the center of the ophthalmic lens, and at least one second optical zone may have a substantially annular shape surrounding the at least one first optical zone.

[0082] In some embodiments, the at least one first optical zone and the at least one second optical zone can be concentric.

[0083] In some embodiments, the one or more focal points positioned off-axis relative to the first focal point can include a limited number of focal points (e.g., 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 180, 360, or 720 focal points).

[0084] In some embodiments, the one or more focal points positioned off-axis relative to the first focal point include an infinite number of focal points.

[0085] In some embodiments, one or more focal points positioned off-axis relative to the first focal point can be positioned on at least 2 focal planes (eg, at least 2, 3, 4, or 5 focal planes).

[0086] In some embodiments, the number and position of one or more focal points can be determined at least in part based on any combination of one or more of the following: a width of at least one second optical zone, a curvature of at least one second optical zone, a position of at least one second optical zone, a base power of at least one second optical zone, and / or a lateral separation value of at least one second optical zone.

[0087] In some embodiments, the depth of focus provided by the ophthalmic lens can be determined at least in part based on any combination of one or more of the following: a width of at least one second optical zone, a curvature of at least one second optical zone, a position of at least one second optical zone, a base power of at least one second optical zone, a lateral separation value of at least one second optical zone, and / or m and p components.

[0088] In some embodiments, at least one second optical zone can have a substantially annular shape, wherein the lateral spacing value on the surface of the lens is between 0.2 and 1 mm (for example, the lateral spacing value on the surface of the lens 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 or about 1 mm).

[0089] In some embodiments, at least one second optical zone can have a substantially annular shape, wherein the lateral spacing value on the surface of the lens is between 0.2 and 1 mm (e.g., the lateral spacing value on the surface of the lens can be less than about 50um, 60um, 70um, 80um, 90um, 0.1mm, 0.15mm, 0.2mm, 0.25mm, 0.3mm, 0.35mm, 0.4mm, 0.45mm, 0.5mm, 0.55mm, and / or 0.6mm).

[0090] In some embodiments, at least one second optical zone can have a substantially annular shape, wherein the lateral spacing value on the surface of the lens is between 0.2 and 1 mm (e.g., the lateral spacing value on the surface of the lens can be greater than about 50um, 60um, 70um, 80um, 90um, 0.1mm, 0.15mm, 0.2mm, 0.25mm, 0.3mm, 0.35mm, 0.4mm, 0.45mm, 0.5mm, 0.55mm, and / or 0.6mm).

[0091] In some embodiments, at least one focal plane can be in front of, behind, or in substantially the same plane as the first focal point.

[0092] In some embodiments, rays extending beyond at least one focal plane may also form a depth of focus behind and in front of the first focal point.

[0093] 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 can be approximately 100:0 (completely in front of the first focus), 90:10, 80:20, 75:25, 70:30, 60:40, 50:50 (equally 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).

[0094] In some embodiments, at least one second region cross-section may have a focal length in two dimensions that is independent of the rest of the ophthalmic lens.

[0095] In some embodiments, the at least one second region may be created by adjusting the curvature of the base lens on at least one of the anterior surface of the ophthalmic lens and / or the posterior surface of the ophthalmic lens.

[0096] In some embodiments, the at least one second zone may be created by adjusting the curvature of the base lens on the front surface of the ophthalmic lens to create one of a positive optical zone or a negative optical zone.

[0097] In some embodiments, the at least one second zone may be created by adjusting the curvature of the base lens on the posterior surface of the ophthalmic lens to create one of a positive optical zone or a negative optical zone.

[0098] In some embodiments, at least one second optical zone can have a substantially annular shape that includes an oblique curvature to affect (eg, shift) depth of focus.

[0099] In some embodiments, at least one second optical zone can have a substantially annular shape comprising multiple curvilinear injections (e.g., 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 curvilinear injections) having the same optical properties or different optical properties.

[0100] In some embodiments, at least one second optical zone can have a substantially annular shape comprising a plurality of combined curvatures (eg, 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 combined curvatures).

[0101] In some embodiments, at least one second optical zone can have a substantially annular shape created by replacing at least one (or both) surface curvatures of the lens with a line (eg, a surface with no or substantially no curvature).

[0102] In some embodiments, the depth of focus provided by the ophthalmic lens and / or the annular region can range from approximately 0.25D to 5D (e.g., approximately 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).

[0103] In some embodiments, an ophthalmic lens may be configured to slow, reduce, or prevent myopia progression in an eye.

[0104] In some embodiments, an ophthalmic lens may be configured for correction of myopia.

[0105] In some embodiments, an ophthalmic lens may be configured to correct presbyopia.

[0106] In some embodiments, the ophthalmic lens may be a paropia lens.

[0107] In some embodiments, the ophthalmic lens may be a segmented vision lens and / or a progressive addition (PAL) lens.

[0108] In some embodiments, the ophthalmic lens can be one or more of the following: a spectacle lens, a contact lens, a corneal onlay, a corneal inlay, and an anterior chamber or posterior chamber intraocular lens.

[0109] Other features and advantages of the subject matter described herein will be apparent from the description and drawings, and from the claims. BRIEF DESCRIPTION OF THE DRAWINGS

[0110] Aspects of the implementations described herein can be understood from the following detailed description when read in conjunction with the accompanying figures.

[0111] Figure 1A and 1B is a schematic diagram showing a plan view of a bifocal ophthalmic lens incorporating a central vision correction zone surrounded by one (or more) zones whose power is used to create myopic defocus for myopia control.

[0112] Figure 2A and 2B It is shown by Figure 1A and 1B Schematic illustration of ray tracing of a distant object imaged by an ophthalmic lens.

[0113] Figure 3A and 3B It is shown by Figure 1A and 1BSchematic diagram of a point diagram of the focus DF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0114] Figure 4A and 4B is a schematic diagram illustrating a plan view of an ophthalmic lens (eg, a contact lens) incorporating a central vision correction region surrounded by a region whose power is used to create myopic defocus for myopia control in accordance with certain embodiments.

[0115] Figure 5A and 5B It is shown that according to some embodiments Figure 4A and 4B Schematic illustration of ray tracing of a distant object imaged by an ophthalmic lens.

[0116] Fig. 6A and 6B is a diagram showing that according to some embodiments Figure 4A and 4B Schematic diagram of the point diagram and RMS value of the focus DF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0117] Fig. 7A and 7B is a schematic diagram illustrating a plan view of an ophthalmic lens (e.g., a spectacle lens) configured for myopia control and incorporating a central vision correction zone and multiple annular zones that alternate between powers to create myopic defocus, according to certain embodiments.

[0118] Fig. 8A and 8B It is shown that according to some embodiments Fig. 7A and 7B Schematic illustration of ray tracing of a distant object imaged by an ophthalmic lens.

[0119] Fig. 9A and 9B is a diagram showing that according to some embodiments Fig. 7A and 7B Schematic diagram of the point diagram and RMS value of the focus DF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0120] Fig. 10A and 10B is a schematic diagram showing a plan view of an ophthalmic lens (eg, a bifocal soft contact lens for presbyopia) that combines a central vision correction zone and one (or more) zones whose power is used to correct near vision for presbyopia.

[0121] Fig.11A and 11B It is shown by Fig. 10A and 10B Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens.

[0122] Fig. 12A , 12B , 12C and 12D are shown by Fig. 10A and 10B Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0123] Fig.13 is a schematic diagram illustrating a plan view of an ophthalmic lens (eg, a soft bifocal contact lens) comprising laterally spaced optics for distance and near optical zones according to certain embodiments.

[0124] Fig.14 It is shown that according to some embodiments Fig.13 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens.

[0125] Fig.15A and 15B is a diagram showing that according to some embodiments Fig.13 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0126] Fig.16 is a schematic diagram illustrating an exemplary design of an ophthalmic lens using spherical geometry in accordance with certain embodiments.

[0127] Fig.17 is a schematic diagram illustrating a plan view of an ophthalmic lens (eg, a soft bifocal contact lens) comprising laterally spaced optics for distance and near optical zones according to certain embodiments.

[0128] Fig.18 It is shown that according to some embodiments Fig.17 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens.

[0129] Fig.19A and 19B is a diagram showing that according to some embodiments Fig.17 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0130] Fig. 20is a schematic diagram illustrating a plan view of an ophthalmic lens (eg, a soft bifocal contact lens) comprising laterally spaced optics for distance and near optical zones according to certain embodiments.

[0131] Fig.21 It is shown that according to some embodiments Fig. 20 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens.

[0132] Fig.22A and 22B is a diagram showing that according to some embodiments Fig. 20 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0133] Fig.23 is a schematic diagram illustrating a plan view of an ophthalmic lens (eg, a soft bifocal contact lens) comprising laterally spaced optics for distance and near optical zones according to certain embodiments.

[0134] Fig.24 It is shown that according to some embodiments Fig.23 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens.

[0135] Fig.25A and 25B is a diagram showing that according to some embodiments Fig.23 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0136] Fig.26 is a schematic diagram illustrating a plan view of an ophthalmic lens (eg, a bifocal spectacle lens) comprising laterally spaced optics for distance and near optical zones according to certain embodiments.

[0137] Fig. 27 It is shown that according to some embodiments Fig.26 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens.

[0138] Fig.28A and 28B is a diagram showing that according to some embodiments Fig.26 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0139] Fig.29A is a schematic diagram showing a plan view of a bifocal spectacle lens.

[0140] Fig.29B is a schematic diagram illustrating a plan view of an ophthalmic lens (eg, a bifocal spectacle lens) comprising laterally spaced optics for distance and near optical zones according to certain embodiments.

[0141] Fig.30 It is shown that according to some embodiments Fig.29B Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens.

[0142] Fig.31A and 31B is a diagram showing that according to some embodiments Fig.29B Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0143] Fig.32 is a schematic diagram illustrating a plan view of an ophthalmic lens (eg, a bifocal spectacle lens) comprising laterally spaced optics for distance and near optical zones according to certain embodiments.

[0144] Fig.33 It is shown that according to some embodiments Fig.32 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens.

[0145] Fig.34A and 34B is a diagram showing that according to some embodiments Fig.32 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0146] Fig.35 is a schematic diagram illustrating a plan view of an ophthalmic lens (eg, a progressive spectacle lens) comprising laterally spaced optics for distance and near optical zones according to certain embodiments.

[0147] Fig.36 It is shown that according to some embodiments Fig.35 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens.

[0148] Fig.37A and 37B is a diagram showing that according to some embodiments Fig.35 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0149] Fig.38is a schematic diagram of a progressive addition (PAL) eyeglass lens, according to certain embodiments.

[0150] Fig.39 is a diagram showing a method for forming a Fig.38 A more detailed geometrical view of the front surface of an exemplary progressive addition spectacle lens (PAL) is shown.

[0151] Fig.40 Described in detail according to certain embodiments Fig.39 Power diagram of the PAL eyeglass lens design shown.

[0152] Fig.41 is a schematic diagram of an ophthalmic lens according to certain embodiments, illustrating an exemplary embodiment of an optical zone that is geometrically perpendicular to a surface.

[0153] Fig.42 is a schematic diagram illustrating an exemplary embodiment of the curvature of an optic zone of an ophthalmic lens normal to a surface according to certain embodiments.

[0154] Fig.43A and 43B is a schematic diagram illustrating an exemplary embodiment of an ophthalmic lens having a line curvature of an optic zone that is geometrically perpendicular to the surface according to certain embodiments.

[0155] Fig.44A and 44B is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to create an off-axis focal plane and depth of focus according to certain embodiments.

[0156] Fig.45 is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to create an off-axis focal plane and depth of focus according to certain embodiments.

[0157] Fig.46 is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to create an off-axis focal plane and depth of focus according to certain embodiments.

[0158] Fig.47 is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to create an off-axis focal plane and depth of focus according to certain embodiments.

[0159] Fig.48is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to create an off-axis focal plane and depth of focus according to certain embodiments.

[0160] Fig.49A and 49B is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to create an off-axis focal plane and depth of focus according to certain embodiments.

[0161] Fig.50 is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to create an off-axis focal plane and depth of focus according to certain embodiments.

[0162] Fig.51A and 51B is a schematic diagram illustrating an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to create an off-axis focal plane and depth of focus according to certain embodiments.

[0163] Fig.52 It shows the existing lens design and Fig.44A , 44B , 51B, and a comparison of retinal image quality (RIQ) between a lens design having a coaxial annular design. DETAILED DESCRIPTION

[0164] The following disclosure provides many different embodiments or examples for realizing different features of the subject matter provided. Specific examples of components and arrangements are described below to simplify the disclosure. Of course, these are merely examples and are not restrictive. In addition, the disclosure may repeat reference numbers and / or letters in various examples. This repetition is for the purpose of simplicity and clarity and does not itself specify the relationship between the various embodiments and / or configurations discussed.

[0165] The subject headings used in the detailed description are included for the convenience of the reader's reference and should not be used to limit the subject matter found in the entire disclosure or claims. The subject headings should not be used to interpret the scope of the claims or the limitations of the claims.

[0166] The term "about" as used in this disclosure should be understood as interchangeable with the terms approximately or roughly.

[0167] As used in this specification, the term “comprise” and its derivatives (eg, includes, containing) should be construed as including the features it refers to, and are not intended to exclude the existence of additional features unless otherwise stated or implied.

[0168] The term "shifted" or "spaced" or "transversely spaced" as used in the present disclosure with respect to two or more optical axes means that the two or more optical axes or optical rays associated with the optical axes do not substantially coincide and / or are not substantially located on a common axis, but may be parallel, skewed, tilted, or a combination thereof relative to each other. In addition, the term "shifted" or "spaced" or "transversely spaced" as used in the present disclosure also means that the focus from one or more optical zones may be spaced a distance from the focus from other one or more optical zones or the optical axis of one or more other optical zones, the distance being at least one of transverse, vertical, superior, inferior, other angled directions, or a combination thereof relative to each other.

[0169] The term "controlled" or "control" as used in this disclosure means changing or modifying or reducing the overlap of one or more focal points of a focused image and one or more out-of-focus images at the retina.

[0170] As used in this disclosure with respect to light and / or images, the term "interfere" or "interference" in verb or noun form means that at least a portion of light from different optical zones, at least a portion of light rays, one or more of the focal points interfere with each other, overlap, obscure, conflict, occur simultaneously, cover, or a combination thereof.

[0171] The term "light quality" or "image quality" as used in this disclosure refers to the performance of an ophthalmic lens as can be determined, for example, by reduction in root mean square (RMS) spot size, contrast, subjective visual performance measurements such as halos, ghosting, and / or combinations thereof. Other suitable means may also be used to determine the performance of an ophthalmic lens.

[0172] The terms "depth of focus" or "extended depth of focus" as used in this disclosure refer to the distance or range in front of and / or behind the image plane within which one or more images can be placed / positioned / focused without significantly degrading the image quality of the system (e.g., a living eye or a model eye).

[0173] 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 for reshaping the cornea, and a clip-on feature configured to be attached to a spectacle lens.

[0174] The term "eyeglass lens" as used in this disclosure is intended to include a lens blank, a finished or a substantially finished eyeglass lens.

[0175] The term "out-of-focus" image or light as used in this disclosure is intended to mean an image that appears blurry to a particular user and has a focus that lies substantially at a plane other than the retina.

[0176] As used in this disclosure, the term "focused" image is intended to mean an image that appears sharp, substantially sharp, or reasonably sharp to a particular user.

[0177] The term "optical axis" as used in this disclosure means the optical axis of one or more of: an optic, an optical zone, and an optical zone segment.

[0178] As discussed in more detail below with respect to various examples, an ophthalmic lens (e.g., a synoptic lens) is configured to correct a combination of one or more of: distance vision, intermediate vision, and near vision. In the case of a synoptic ophthalmic lens, the design provides multiple focal points corresponding to multiple optical zones that share a common axis. In such a design, light passing through the ophthalmic lens may be shared between multiple optical zones, and as a result, the focal point from one optical zone may overlap with the defocused image from other optical zones—resulting in a focused image being disturbed by the out-of-focus image. This may result in a reduction in the image quality (e.g., contrast, sharpness) of the focused image.

[0179] An example of a homopic ophthalmic lens is a distance central bifocal lens (e.g., a contact lens for presbyopia). Most commonly, for such a lens, the lens design may have a central optic zone with power to correct for distance refractive error of presbyopia and may be surrounded by one or more annular or concentric zones with alternating zones with power to correct for near refractive error. In some other designs, the bifocal lens may be a central near lens, wherein the design may have a central optic zone with power to correct for near refractive error and may be surrounded by one or more annular or concentric zones with alternating concentric zones with power to correct for distance refractive error. Typically, the optical zones are configured to be concentric and coaxial so that the focal points from multiple optical zones may fall on a common axis of symmetry of the ophthalmic lens.

[0180] Considering the example of a distance-centered bifocal lens, when viewing a distant object, the ophthalmic lens may provide a focused image caused by light rays refracted by the distance power optical zone, while simultaneously producing one or more defocused images caused by rays refracted by one or more concentric near power optical zones. This may cause the defocused image to interfere with the focused image and reduce the image quality (e.g., the contrast and / or sharpness of the image). Similarly, when viewing a near object, the ophthalmic lens may provide a focused image caused by rays refracted by one or more near power optical zones, while simultaneously or substantially simultaneously producing a defocused image caused by light rays refracted by one or more distance power optical zones that interfere with the focused image, thereby reducing the image quality (e.g., the contrast and / or sharpness of the image).

[0181] Figure 1A and 1B is a schematic diagram showing a plan view of a bifocal ophthalmic lens incorporating a central vision correction zone 101 surrounded by one (or more) zones 102 whose power is used to create myopic defocus for myopia control. Figure 1A and 1B The bifocal soft contact lens in incorporates a central vision correction zone 101 surrounded by a zone whose power is used to create myopic defocus for myopia control. Figure 1A a single ring containing myopic defocus 102 power (e.g., relatively more correct power than the central vision correction area 101), and Figure 1B Contains two rings (annulus) of myopic defocus power (102) separated by a zone for distance ametropia correction 101. In both lenses, the vision correction zone is coaxial with the myopic defocus zone, and a myopic defocus of, for example, +2.5D is incorporated in one (or more) of the annular zones.

[0182] Figure 2A and 2B It is shown by Figure 1A and 1B Schematic diagram of ray tracing of a distant object imaged by an ophthalmic lens of FIG. As shown, light rays travel through the lens and the eye, and an image of the distant object is formed at the retinal plane. Light rays passing through the respective regions are represented as either a focus at the image plane for light rays traveling through the vision correction region 101, or an out-of-focus blur circle at the image plane for light rays passing through the myopic defocus region 102. Figure 2A and 2B In the example of , the distant object has been further defined by three points: the central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned approximately 0.5 degrees on either side of OP1.

[0183] In the higher magnification panels of the ray traces formed at and near the image plane, the foci of OP1, OP2, and OP3 are illustrated as DF1, DF2, and DF3 at the image plane. Figure 2A and 2B The degree of interaction between out-of-focus light rays of object points OP1, OP2 and OP3 from the near defocus region and the focused images of OP1, OP2 and OP3 produced by one (or more) distance power regions in these coaxial-based optical designs is shown.

[0184] Figure 3A and 3B Is Figure 1A and 1B Schematic diagram of a spot diagram of a focus DF1 of an object point OP1 formed at an image plane by an ophthalmic lens configured with coaxial optics. The spot diagram represents the focus size at the image plane. In some embodiments, the focus size can be expressed as the root mean square (RMS) of the spot radius in microns. A smaller spot size can indicate a more obvious focus (e.g., good image quality of focus). Conversely, a larger spot radius can indicate poor image quality of a less sharp and / or dispersed image focus, for example due to overlap and interference of out-of-focus light from other optical areas in focus.

[0185] In this example, DF1 has an RMS size of 0.52um and 0.4um at the image plane for the single-ring and dual-ring optical designs, respectively. These values ​​may be similar to the expected values ​​for the focal point produced by a single-vision optical design. However, the image quality of DF1 may be affected by the interaction of light rays from neighboring points on distant objects (e.g., OP2 and OP3). When considering the light rays from Figure 2A When the defocused light rays of OP2 and OP3 of the myopic defocus annular area of ​​the lens described in , the RMS spot size of DF1 at the image plane increased significantly from 0.52um to 145.2um (overall average 118.55um) for OP2 and OP3, respectively. Figure 2B The RMS spot size of DF1 also increases significantly from 0.4um to 147.05um (overall average 120.06um) at the image plane in the defocused light rays of OP2 and OP3 formed by the myopic defocus annular region of the lens described in . Therefore, the small focus DF1 of OP1 considered in isolation becomes blurred and increases in size due to the influence of the light rays of the neighboring object points OP2 and OP3 overlapping with the out-of-focus light formed by the myopic defocus region. In some embodiments, this may indicate that the image formed by OP1 is degraded (e.g., substantially degraded) due to the out-of-focus light rays of the neighboring object points generated by the on-axis myopic defocus region.

[0186] In some embodiments, interference of one or more defocused images with a focused image can be controlled; and / or the visual performance, contrast and / or sharpness of an image or the range of an extended depth of focus can be improved by designing one or more optical zones of an ophthalmic device to include optical devices that are laterally spaced or shifted relative to at least one other optical zone.

[0187] Some embodiments may be directed to an ophthalmic lens design that controls the overlap of one or more focal points of an image with out-of-focus light. In some embodiments, the overlap of one or more focal points of an image with out-of-focus light may be at least partially, or completely reduced. In other embodiments, the overlap of one or more focal points of an image with one or more out-of-focus images may 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%.

[0188] In some embodiments, the overlap of the focus associated with an image and the focus associated with one or more out-of-focus images can be at least partially or completely controlled by spacing or shifting the one or more focus associated with the image and the one or more focus associated with the out-of-focus image, for example, 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, the overlap of the focused image and one (or more) out-of-focus image can be controlled by spacing or shifting the one or more focus associated with the focused image and the one or more focus associated with the one or more out-of-focus images, for example, 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, about 0.1 to about 2.5 mm. In some embodiments, the spacing 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.

[0189] Some embodiments described herein may be directed to an ophthalmic lens design that improves the quality of an image by controlling the overlap of a focal point at a given image plane and a focal point associated with one of a plurality of out-of-focus images or lights, wherein the RMS spot size at the image plane is reduced by 1 μm or more. In some embodiments, the reduction in the RMS spot size radius achieved by controlling the overlap of a focal point at a given image plane and one or more focal points associated with one or more out-of-focus images may be about 1 μm or more. In some embodiments, the reduction in the RMS spot size radius at an image plane by controlling the overlap of the focus at a given image plane and the focus associated with one or more out-of-focus images 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, the reduction in the RMS spot size radius by controlling the overlap of the focus at a given image plane and the focus associated with one or more out-of-focus images can be about 1 μm, about 10 μm, about 25 μm, or about 50 μm.

[0190] 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 different from the first distance and displaced relative to the first axis.

[0191] In some embodiments, the overlap of the focus associated with an image at a given image plane and the focus associated with an out-of-focus image can be substantially controlled by designing an ophthalmic lens having multiple optical zones or segments, wherein the optical axes for the multiple optical zones or segments are different from each other 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 fall on a common axis. In some embodiments, some optical axes of the multiple optical zones or segments may fall on a common axis. In some embodiments, the optical axes of the multiple optical zones associated with a first focal length may fall on a first optical axis, and the optical axes of the multiple optical zones or segments associated with a second focal length may fall on a second optical axis. In some embodiments, the optical axes of the multiple optical zones associated with a first focal length may fall on a first optical axis, and the optical axes of the multiple optical zones or segments associated with a second focal length may fall on a corresponding multiple axes different from the first axis (e.g., a second optical axis, a third optical axis, a fourth optical axis, a fifth optical axis, etc.).

[0192] In some embodiments, the optical axes of multiple optical zones associated with a first focal length may fall on the first optical axis, and the optical axes of multiple optical zones or segments associated with a second focal length may fall on the second optical axis, and the optical axes of multiple optical zones or segments associated with a third focal length may fall on the third optical axis, and so on.

[0193] In some embodiments, the overlap of the focus associated with an image at a given image plane and the focus or rays associated with an out-of-focus image can be controlled by configuring an ophthalmic lens to have multiple optical zones or segments. One or more optical zones or segments may have an optical axis, and one or more optical zones or segments may not share a common axis (e.g., may have different optical axes). Therefore, the focus caused by one or more optical zones or segments can be shifted relative to the optical axis and focus from other optical zones or segments of the ophthalmic lens. In some embodiments, the shift of the focus caused by light directed through one or more optical zones or segments relative to the focus caused by light directed through other optical zones or segments of the ophthalmic lens can result in a modification or change in the defocused or out-of-focus light of the image at a given image plane, so that the quality of the retinal image (e.g., contrast and / or sharpness) can be improved and / or can result in an extended depth of focus.

[0194] In some embodiments, the shift of the focus caused by light directed through one or more optical zones or segments relative to the focus caused by light directed through other optical zones and / or segments on an ophthalmic lens can be addressed by one or more of the optical spacing devices (e.g., lateral spacing optics). In some embodiments, the optical spacing devices (e.g., lateral spacing optics) for shifting the focus caused by light directed through one or more optical zones or segments relative to the focus caused by light directed through other optical zones and / or segments on an ophthalmic lens can include utilizing one or more optical surfaces comprising two or more optical elements (e.g., spherical, elliptical, conical, aspherical, or other suitable elements, including aspherical toric elements, such as lines, conical surfaces), wherein the two or more optical elements are positioned, offset, rotated, tilted, or shifted relative to each other such that at least a majority or at least a portion of the two or more optical elements do not share a common optical axis. In some embodiments, an optical spacing device (e.g., lateral spacing optics) for shifting the focus caused by light directed through one or more optical zones or segments relative to the focus caused by light directed through other optical zones and / or segments on an ophthalmic lens can include utilizing an optical surface comprising two or more optical elements (e.g., spherical, elliptical, conical, aspherical, or other suitable elements, including aspherical toric elements, such as wires, conical surfaces), wherein the two or more optical elements can have different radii. The optical surface of the ophthalmic lens can be the front surface, the back surface, or both surfaces of the lens.

[0195] In some embodiments, the optical zone with a first focal power may be at the center of the lens, or substantially at the center of the lens, and the optical zone with a second focal power may be a concentric zone or a substantially concentric zone surrounding the central optical zone. In some embodiments, the optical zone with a first focal power may occupy a segment, meridian, or portion of the lens, and the optical zone with a second focal power may occupy the remaining segments, meridians, or remaining portions of the lens (e.g., a segmented ophthalmic lens). In some embodiments, the optical zone with a first focal power may occupy multiple portions of the lens and alternate between optical zones with a second focal power (e.g., multiple rings). In some embodiments, the first focal power may be uniform or may vary in different portions of the first optical zone. In some embodiments, the ophthalmic lens may include a third optical zone with a third focal power. In some embodiments, the third optical zone may be one or more concentric zones near (e.g., surrounding) the central optical zone. In some embodiments, the third optical zone may be a segment, meridian, or portion of the lens other than the segments, meridians, or portions of the lens occupied by the first optical zone and the second optical zone.

[0196] In some embodiments, for example, for a segmented ophthalmic lens, the optical element having a first power may be a first optical zone and the first axis may be an optical axis of the first optical zone. In some embodiments, the optical element having a second power may be a second optical zone. The second optical zone may have a second axis that is displaced relative to or laterally spaced from the first axis. In some embodiments, the spacing of the centers of the two optical elements relative to the center of the ophthalmic lens may range from 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, about 0.75 mm, about 0.80 mm, about 0.90 mm, about 100 mm, about 150 mm, about 100 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm, about 150 mm 7mm, about 0.75mm, about 0.8mm, about 0.85mm, about 0.9mm, about 0.95mm, about 1mm, about 1.25mm, about 1.5mm, about 1.75mm, about 2mm, about 2.25mm, about 2.5mm, about 2.75mm, about 3mm, about 3.25mm, about 3.5mm, about 3.75mm, about 4mm, about 4.25mm, about 4.5mm, about 4.75mm, about 5mm, about 5.25mm, about 5.5mm, about 5.75mm, about 6mm, about 6.25mm, about 6.5mm, about 6.75mm, about 7mm, about 7. 25mm, about 7.5mm, about 7.75mm, about 8mm, about 8.25mm, about 8.5mm, about 8.75mm, about 9mm, about 9.25mm, about 9.5mm, about 9.75mm, about 10mm, about 10.25mm, about 10.5mm, about 10.75mm, about 11mm, about 11.25mm, about 11.5mm, about 11.75mm, about 12mm, about 12.25mm, about 12.5mm, about 12.75mm, about 13mm, about 13.25mm, about 13.5mm, about 13.75mm, about 14mm, about 14.25mm , about 14.5mm, about 14.75mm, about 15mm, about 15.25mm, about 15.5mm, about 15.75mm, about 16mm, about 16.25mm, about 16.5mm, about 16.75mm, about 17mm, about 17.25mm, about 17.5mm, about 17.75mm, about 18mm, about 18.25mm, about 18.5mm, about 18.75mm, about 19mm, about 19.25mm, about 19.5mm, about 19.75mm, about 20mm, about 20.25mm, about 20.5mm, about 20.75mm, or about 21mm).In some embodiments, for spectacle lenses, the spacing can be about 10 mm and for contact lenses, the spacing can be about 2 mm. In some embodiments, for spectacle lenses, the spacing can 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. In some embodiments, for contact lenses, the spacing can be 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.

[0197] In some embodiments, the use of optical spacing devices (e.g., lateral spacing optics) to shift the focus caused by light directed through one or more optical zones or segments relative to the focus caused by light directed through other optical zones and / or segments on the ophthalmic lens can result in prismatic power and can cause the wearer of the ophthalmic lens to perceive objects as being shifted during use. In some embodiments, it may be desirable to reduce but still maintain the spacing of images (e.g., focal points), which can result in a trade-off in vision in the lens between lower prismatic power (reduced image spacing) and higher image quality (increased image spacing).

[0198] In some embodiments, the optical zone having a first power can be a first optical zone and the first axis can be an 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 that is displaced or laterally spaced relative to the first axis.

[0199] In some embodiments, the second optical zone can be configured so that, when used with the eye, light passing through the second optical zone is refracted to a plurality of second focal points, the plurality of second focal points being on corresponding one or more of a plurality of second axes associated with the one or more second optical zones, the plurality of second axes being displaced relative to the first axis. In some embodiments, the second optical zone can have a plurality of focal points. In some embodiments, the second optical zone can be configured so that, when used with the eye, light passing through the second optical zone is refracted to a plurality of (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, or 16) focal points that are not on the first axis. In some embodiments, light passing through the second optical zone can be refracted to 3, 3, 4, or 5 focal points that are not on the first axis. In some embodiments, this configuration can be used for an ophthalmic lens used to address myopia.

[0200] In some embodiments, an ophthalmic lens may include a first optical zone having a first power, a second optical zone having a uniform (or varying) power, a third optical zone having a uniform (or varying) power, and the like.

[0201] In some embodiments, the displacement of the first axis relative to the second axis can create a prismatic power on the ophthalmic lens. In some embodiments, the prismatic power created by the displacement of the first axis relative to the second axis can be 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 0.45Δ, about 0.5Δ, about 0.6Δ, about 0.7Δ, about 0.8Δ, about 0.9Δ, about 1Δ, about 1.25Δ, about 1.5Δ, about 1.75Δ, about 2Δ, about 2.25Δ, about 2.5Δ, about 2.75Δ, about 3Δ, about 3.25Δ, about 3.5Δ, about 3.75Δ, about 4Δ, about 4.25Δ, about 4.5Δ, about 4.75Δ, about 5Δ, about 5.25Δ, about 5.5Δ, about 5.75Δ, about 6Δ, about 6.25Δ, about 6.5Δ, about 6.75Δ, about 7Δ, about 7.25Δ, about 7.5Δ, about 7.75Δ, about 8Δ, about 8.1Δ, about 8.2Δ, about 8.3Δ, about 8.4Δ, about 8.5Δ, about 8.6Δ, about 8.7Δ, about 8.8Δ, about 8.9Δ, about 9Δ, about 9.1Δ, about 9.2Δ, about 9.3Δ, about 9.4Δ, about 9.5Δ, about 9.6Δ, about 9.7Δ, about 9.8Δ, about 9.9Δ, about 10Δ, about 10.1Δ, about 10.2Δ, about In some embodiments, the prismatic power created by the shift of the first axis relative to the second axis can be about 1Δ, about 2Δ, about 3Δ, about 4Δ, about 5Δ, about 6Δ, about 7Δ, about 8Δ, or about 9Δ.

[0202] In some embodiments, one or more optical zones having a first focal power may occupy greater than 50% (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 optic zone of the ophthalmic lens (e.g., the anterior or posterior surface area of ​​the lens). In some embodiments, one or more optical zones having a first focal power may occupy less than 50% (e.g., about 45%, about 40%, about 35%, about 30%, about 25%, or about 20%) of the surface area of ​​the optic zone of the ophthalmic lens (e.g., the anterior or posterior surface area of ​​the lens). In some embodiments, one or more optical zones having a first focal 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 optic zone of the ophthalmic lens (e.g., the anterior or posterior surface area of ​​the lens). In some embodiments, one or more optical zones having a first focal 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 optic zone of the ophthalmic lens (e.g., the front or back surface area of ​​the lens). In some embodiments, one or more optical zones having a first focal power may occupy less than about 75% (e.g., about 55%, about 60%, about 65%, about 70%, or about 75%) of the surface area of ​​the optic zone of the ophthalmic lens (e.g., the front or back surface area of ​​the lens). In some embodiments, one or more optical zones having a first focal power may occupy greater than about 10% (e.g., about 15%, about 20%, about 25%, about 30%, about 35%, about 40%, or about 45%) of the surface area of ​​the optic zone of the ophthalmic lens (e.g., the front or back surface area of ​​the lens).

[0203] In some embodiments, an optical zone having a first focal power may be at least partially defined by a sphere having a first radius and / or an optical zone having a second focal power may be at least partially defined by a sphere having a second radius different from the first radius. In some embodiments, an optical zone having a first focal power may be at least partially defined by a sphere having a first radius and / or an optical zone having a second focal power may be at least partially defined by a sphere having a second radius less than the first radius. In some embodiments, an optical zone having a first focal power may be at least partially defined by a sphere having a first radius and / or an optical zone having a second focal power may be at least partially defined by a sphere having a second radius greater than the first radius.

[0204] In some embodiments, one or more optical zones having a second power can comprise one or more spheres having one or more radii that are different than one or more optical zones having a first power and a first radius.

[0205] In some embodiments (e.g., for contact lenses), the first optical zone can be substantially circular in shape and have a diameter of about 3 mm (e.g., in some embodiments, the diameter can 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, less than about 4 mm, less than about 3.5 mm, and / or less than about 3 mm). In some embodiments, the second optical zone can be substantially annular in shape and have an inner diameter of about 3 mm (e.g., in some embodiments, the inner diameter can 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, less than about 4 mm, less than about 3.5 mm, and / or less than about 3 mm) and an outer diameter of about 7 mm (e.g., in some embodiments, the outer diameter can 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, less than about 8 mm, less than about 7.5 mm, and / or less than about 7 mm). In some embodiments, the first optical zone can be substantially circular in shape and the second optical zone can be substantially annular in shape and the inner diameter of the second optical zone can be substantially equal to the diameter of the first optical zone.

[0206] In some embodiments (e.g., for eyeglass lenses), the first optical zone can be substantially circular in shape and have a diameter of about 10 mm (e.g., in some embodiments, the 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 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 8-10 mm, about 10-12 mm, about 9-11 mm, about 12-14 mm, less than about 10 mm, less than about 12.65 mm, and / or less than about 15 mm). 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, less than about 10 mm, less than about 11 mm, and / or less than about 12 mm) and about 15 mm. In some embodiments, the first optical zone can be substantially circular in shape and the second optical zone can be substantially annular in shape and the inner diameter of the second optical zone can be substantially equal to the diameter of the first optical zone.

[0207] 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 the following: 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 a spectacle lens) may be configured such that the ophthalmic lens has one or more optical zones having a first focal power to correct one of distance vision, intermediate vision, or near vision; and one or more optical zones having a second focal power that is more positive than the first focal power. In some embodiments, the optical zones may be configured such that when an object is viewed, the focus caused by the light rays (or at least a portion of the light rays) refracted from one or more optical zones having the second focal power is shifted relative to the focus caused by the light rays (or at least a portion of the light rays) refracted from one or more optical zones having the first focal power, so that the image quality associated with the first image can be improved (e.g., there may be a reduced amount of overlapping light rays from one or more optical zones having the second focal power) and / or an extended depth of focus is provided. In some embodiments, when viewing an object at a distance, light directed through one or more optical zones having a first focal power can be focused at a first focal point that is displaced relative to light directed through one or more optical zones having a second focal power, such that the focal point resulting from light directed through the optical zones having the first focal power can be minimally interfered with (e.g., there is little, substantially little, and / or no interference with) the focal point resulting from light directed through the optical zones having the second focal power. In some embodiments, one or more optical zones having a first focal power and one or more optical zones having a second focal power have separate optical axes that are displaced relative to each other, wherein the resulting images have partial or reduced overlap. In some embodiments, interference of an out-of-focus image from one or more optical zones having a second focal power with an image from one or more optical zones having a first focal power during long distance and / or near viewing can be controlled by using an optical surface comprising two or more optical elements (e.g., spherical, elliptical, conical, aspherical, or other suitable elements, including aspherical toric elements, such as lines, conical surfaces), wherein two or more optical elements are positioned, offset, tilted, rotated, or shifted relative to each other so that they do not share a common optical axis.

[0208] Figure 4A and 4Bis a schematic diagram showing a plan view of an ophthalmic lens (e.g., a contact lens) in accordance with certain embodiments that incorporates a central zone 401 having a first power surrounded by a zone 402 having a power to create a myopic defocus relative to the zone 401 for myopia control. As shown, the central zone 401 and the surrounding myopic defocus power zone 402 are configured to be non-coaxial such that the focal points created by the myopic defocus zones are laterally spaced from each other and also from an axis on which a distance focus is created. Figure 4A A single ring with myopic defocus power and Figure 4B 2 annuli with myopic defocus power separated by a zone with a first power. Both lenses contain an on-axis zone with a first power, and the focal points of the myopic defocus zones are arranged to be laterally spaced, e.g. Figure 4A 0.5mm in the middle or Figure 4B In the example shown, both lens types incorporate +2.5D of myopic defocus in an annular arrangement. Figure 4A and 4B A continuous surrounding region is illustrated, however, it is also contemplated that the surrounding region may be discontinuous or a combination of continuous and discontinuous. Figure 4A and 4B Concentric circular regions are illustrated, however, other shapes are contemplated, such as spheres, ellipses, cones, aspherical surfaces, or other suitable elements, including non-spherical toroidal elements, such as lines, conical surfaces. Figure 4A and 4B Concentric regions are illustrated, however, substantially concentric and / or partially concentric regions are also contemplated.

[0209] Figure 5A and 5B It is shown that according to some embodiments Figure 4A and 4B Schematic diagram of ray tracing of a distant object imaged by an ophthalmic lens of FIG. Light rays passing through the respective regions are represented as either focal points at the image plane for light rays traveling through the region having a first focal power, or out-of-focus blur circles at the image plane for light rays passing through the myopic defocused region. Figure 5A and 5B , a distant object has been further defined by three points: the central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned 0.5 degrees on either side of OP1.

[0210] Figure 5A and 5BAlso illustrated are higher 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. In addition, the out-of-focus rays of OP1, OP2, and OP3 that pass through the myopic defocus region constitute the remaining light rays that fall at the image plane. Figure 5A and 5B Both illustrate the extent of interaction between out-of-focus light rays from object points OP1, OP2 and OP3 of the near defocus zone and the images of one (or more) distance power zones OP1, OP2 and OP3 in these lenses configured with laterally spaced focal points.

[0211] Fig. 6A and 6B is an illustration of an optical design based on creating lateral spacing of focal points according to certain embodiments by Figure 4A and 4B Schematic diagram of the point diagram and RMS value of the focus DF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane. For the single ring and double ring optical designs, DF1 has RMS values ​​of 0.46um and 0.41um, respectively. These values ​​may be similar to the expected values ​​of the focus of the single vision optical design. However, compared with, for example Figure 2A and 2B Unlike the example of an ophthalmic lens configured with coaxial optics in , there may be no interaction of defocused light rays from object points OP2 and OP3 formed by the myopic defocus area (e.g., RMS value = 0). Focus DF1 may not overlap and increase the RMS spot size of defocused light rays from neighboring object points, and the overall average RMS value remains relatively small at 0.46um and 0.41um because the lens design includes laterally spaced focal points. Likewise, DF2 and DF3 are also not affected by defocused light from neighboring object points. Therefore, the laterally spaced optics described in this example show a better performance than Figure 2A and 2B The coaxial-based design improves sharpness and higher image quality.

[0212] Fig. 7A and 7B is a schematic diagram showing a plan view of an ophthalmic lens (e.g., a spectacle lens) according to certain embodiments that is configured for myopia control and incorporates a central region having a first focal power 701 surrounded by a plurality of annular regions 702 that alternate between focal powers to create myopic defocus. Fig. 7A The lens shown in is configured so that the zone 701 having a first power and the myopic defocus zone may be coaxial and incorporate a myopic defocus of +2.5D in the myopic defocus annular zone. Figure 7BThe lens shown in is configured so that the zone having a first power 701 and the myopic defocus zone 702 may contain laterally spaced optics and incorporate a myopic defocus of +2.5D in the myopic defocus annular zone. Fig. 7A and 7B A continuous surrounding region is illustrated, however, it is also contemplated that the surrounding region may be discontinuous or a combination of continuous and discontinuous. Fig. 7A and 7B Concentric circular regions are illustrated, however, other shapes are contemplated, such as spheres, ellipses, cones, aspherical surfaces, or other suitable elements, including non-spherical toroidal elements, such as lines, conical surfaces. Fig. 7A and 7B Concentric regions are illustrated, however, substantially concentric and / or partially concentric regions are also contemplated.

[0213] Fig. 8A and 8B It is shown that according to some embodiments Fig. 7A and 7B Schematic diagram of ray tracing of a distant object imaged by an ophthalmic lens of FIG. Light rays passing through the respective regions are represented as either a focus at the retina for light rays traveling through the distance power region, or an out-of-focus blur circle at the image plane for light rays passing through the near defocus region. The distant object has been further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned 0.45 degrees on either side of OP1.

[0214] Fig. 8A and 8B Also included are higher 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 as DF1, DF2, and DF3 at the image plane. In addition, out-of-focus rays that pass through the myopic defocus regions OP1, OP2, and OP3 make up the remaining light rays that fall at the image plane. Fig. 8A and 8B Both illustrate that these are configured with a coaxial optical design ( Fig. 8A ) or optical design of laterally spaced focal points ( Figure 8B ) in a lens having a first focal power.

[0215] Fig. 9A and 9B is a diagram showing that according to some embodiments Fig. 7A and 7BSchematic diagram of the point diagram and RMS value of the focus DF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane. Fig. 9A The diagram shows the coaxial optical design. Fig. 8A Point diagram and RMS value of the focus F1 of the object point OP1 formed at the retinal plane by the myopia control lens of FIG. DF1 has an RMS value of 0.38um, which is comparable to the expected value of the focus of the single-vision optical design. However, the image quality of DF1 can be affected by the interaction of light rays from neighboring points on distant objects (such as OP2 and OP3). When considering the light rays from the Fig. 8A When the effect of the defocused light rays of OP2 and OP3 of the myopic defocus annular zones of the lens described in FIG. 1 on F1 is analyzed, the RMS point size of DF1 increases significantly from 0.38um to 126.39um (overall average 103.19um) for OP2 and OP3, respectively. Therefore, the defined focus F1 of OP1 considered in isolation has now become blurred and increased in size due to the effect of the myopic defocused light rays of the neighboring object points OP2 and OP3 formed by the myopic defocus zones. This shows that the image formed by OP1 is degraded by the out-of-focus light rays of the neighboring object points generated by the on-axis myopic defocus zones.

[0216] Fig. 9B Diagram showing the optical design based on creating lateral spacing of focal points Figure 8B The point diagram and RMS value of the focus DF1 of the object point OP1 formed by the myopia control lens at the retinal plane. DF1 has an RMS value of 0.36um, and the value is as follows Fig. 9A The focal point is similar to that expected for single vision designs. However, compared to lenses configured with coaxial optics (e.g., in 2A and Fig. 8A Unlike the case of contact lenses and glasses with coaxial optical designs, there seems to be no interaction of defocused light rays from object points OP2 and OP3 formed by the myopic defocus area (RMS value = 0.0). Fig. 9B In the example of FIG. 1 , the focal point DF1 does not overlap and increase the RMS spot size of the defocused light rays from the adjacent object points, so the overall average RMS value remains slightly at 0.36um for this eyeglass lens configured with the laterally spaced focal points. Likewise, F2 and F3 are similarly unaffected by the defocused light from the adjacent object points. Therefore, the laterally spaced optics described in this exemplary embodiment show improved sharpness and / or higher image quality compared to coaxial-based designs.

[0217] Fig. 10A and 10Bis a schematic diagram showing a plan view of an ophthalmic lens (e.g., a bifocal soft contact lens for presbyopia) that incorporates a central vision correction zone surrounded by one (or more) zones whose power is used to correct near vision for presbyopia. Fig. 10A Illustrated is a plan view of a bifocal soft contact lens for presbyopia that incorporates a central distance vision correction zone 1001 surrounded by a single zone 1002 whose power is used to correct near vision for presbyopia. The distance and near correction zones may be configured coaxially and incorporate a +2.5D near addition in the surrounding annular zone.

[0218] Fig. 10B A plan view of a soft bifocal contact lens is illustrated that incorporates a central distance vision correction zone 1011 surrounded by a zone 1012 whose power is used to correct near vision for presbyopia. The distance zone and surrounding near power zone can be configured to include laterally spaced optics such that the focal points created by the zones are laterally spaced from each other and also spaced from an axis on which the distance focus is created. Fig. 10B The lens may be configured so that the focus from the distance zone is formed on axis, but the focus formed by the near vision zone is spaced 0.5 mm laterally 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 focus ring around the optical axis where the distance focus is located and spaced from the optical axis. Thus, the near focus ring is spaced 0.5 mm laterally from the optical axis. The bifocal lens in this example incorporates a +2.50D near add. Fig. 10B A continuous surrounding region is illustrated, however, it is also contemplated that the surrounding region may be discontinuous or a combination of continuous and discontinuous. Fig. 10A and 10B Concentric circular regions are illustrated, however, other shapes are contemplated, such as spheres, ellipses, cones, aspherical surfaces, or other suitable elements, including non-spherical toroidal elements, such as lines, conical surfaces. Fig. 10A and 10B Concentric regions are illustrated, however, substantially concentric and / or partially concentric regions are also contemplated.

[0219] Fig.11A and 11B It is shown by Fig. 10A and 10B Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens.

[0220] Fig.11A Shown by Fig. 10ARay tracing of a distant object imaged by a contact lens. Light rays pass through the lens and the eye, and an image of the distant object is formed at the retinal plane. Light rays passing through the respective regions are represented as focal points at the image plane for light rays traveling through the distance focal power region, or out-of-focus blur circles at the image plane for light rays passing through the near addition region. The distant object has been further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned 0.5 degrees on either side of OP1 for distant objects and 0.15 degrees on either side of OP1 for near objects.

[0221] Fig.11A Also illustrated are higher magnification panels of ray traces formed when distant objects are in focus (Distant) and near images are in focus (Near) at the retinal plane. Fig.11A The focal points of distant objects OP1, OP2 and OP3 are shown as DF1, DF2 and DF3 at the image plane, and the out-of-focus rays passing through the near additional regions OP1, OP2 and OP3 constitute the remaining light rays falling at the image plane. Fig.11A The focal points of the near objects OP1, OP2 and OP3 are further illustrated as NF1, NF2 and NF3 at the image plane. The out-of-focus rays that pass through the distance vision region OP1, OP2, OP3 constitute the remaining light rays that fall at the image plane. Fig.11A The diagram illustrates the extent of interaction between out-of-focus light rays of object points OP1, OP2, and OP3 and the images of OP1, OP2, and OP3 produced by one (or more) far or near power zones in these coaxial-based optical designs.

[0222] Fig. 11B Shown by Fig. 10B A cross section of a ray trace of a distant object imaged by a contact lens. Light rays pass through the lens and the eye, and an image of the distant object is formed at the retinal plane. Light rays passing through the respective regions are represented as focal points at the image plane for light rays traveling through the distance focal power region, or out-of-focus blur circles at the image plane for light rays passing through the near addition region. The distant object has been further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned 0.5 degrees on either side of OP1 for distant objects and 0.15 degrees on either side of OP1 for near objects.

[0223] Fig. 11B Also provided are higher magnification panels of ray traces formed when distant objects are in focus (Distant) and near images are in focus (Near) at the retinal plane. Fig. 11BThe focal points of distant objects OP1, OP2 and OP3 are shown as DF1, DF2 and DF3 at the image plane, and the out-of-focus rays passing through the near additional area OP1, OP2 and OP3 constitute the remaining light rays falling at the image plane. This example further illustrates the focal points of near objects OP1, OP2 and OP3 as NF1, NF2 and NF3 at the image plane, and further, the out-of-focus rays passing through the far vision area OP1, OP2, OP3 constitute the remaining light rays falling at the image plane. Fig. 11B The degree of interaction between out-of-focus light rays of object points OP1, OP2 and OP3 and the focused images of OP1, OP2 and OP3 produced by one (or more) far or near power zones in these laterally spaced optical designs is illustrated.

[0224] Fig. 12A , 12B , 12C and 12D are shown by Fig. 10A and 10B Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0225] Fig. 12A The diagram shows Fig.11A Spot diagram and RMS values ​​of the focus DF1 of a distant object point OP1 formed at the retinal plane by a bifocal contact lens of FIG. 1. DF1 has an RMS size of 0.71 um. These values ​​are roughly similar to the focus produced by a single-vision optical design for this aperture size. However, the image quality of DF1 can be affected by the interaction of light rays from neighboring points on the distant object (e.g., OP2 and OP3). When considering the light rays from Fig. 10A When comparing the effect of defocused light rays of the near power annular zones OP2 and OP3 of the lens on D-F1 as described in , the RMS point size of DF1 increases significantly from 0.71um to 110.99um (overall average 90.62um) for OP2 and OP3, respectively. Therefore, the focus DF1 of OP1 considered in isolation has now become blurred and increased in size due to the actual effect of the defocused light rays of the neighboring object points OP2 and OP3 formed by the near power zones. In some embodiments, this indicates that the image formed by OP1 is degraded by the out-of-focus light rays of the neighboring object points generated by the on-axis near power zones.

[0226] Fig. 12B The diagram shows Fig.11ASpot diagram and RMS values ​​of the focal point NF1 of a near object point OP1 formed at the retinal plane by a bifocal contact lens of FIG. 1. N-F1 has an RMS size of 0.2 um. These values ​​are roughly similar to the expected values ​​of the focal point produced by a single-vision optical design for this aperture size. However, the image quality of NF1 can be affected by the interaction of light rays from neighboring points on the near object (e.g., OP2 and OP3). When considering the interaction of light rays from neighboring points on the near object (e.g., OP2 and OP3), the image quality of NF1 can be affected by the interaction of light rays from neighboring points on the near object (e.g., OP2 and OP3). Fig. 10A When comparing the effect of defocused light rays of the distance power center regions OP2 and OP3 of the lens on N-F1 as described in , the RMS spot size of N-F1 increases significantly from 0.2um to 44.15um (overall average 36.05um) for OP2 and OP3, respectively. Therefore, the focal point N-F1 of OP1 considered in isolation has now become blurred and increased in size due to the effect of defocused light rays of the adjacent object points OP2 and OP3 formed by the distance power regions. In some embodiments, this shows that the near image formed by OP1 is degraded by the out-of-focus light rays of the adjacent object points generated by the on-axis distance power region.

[0227] Fig. 12C Illustration of a device having laterally spaced optics for distance and near optical zones. Fig. 11B Spot diagram and RMS values ​​of the focus DF1 of a distant object point OP1 formed at the retinal plane by a bifocal contact lens of . DF1 has an RMS size of 0.7 um. These values ​​are roughly similar to the expected values ​​of the focus produced by a single-vision optical design. However, compared with, for example, Fig. 10A Unlike the case of the lens configured with coaxial optics in FIG. 1 , there is no interaction of defocused light rays from object points OP2 and OP3 formed by the near region (RMS value = 0.0). Focus DF1 does not overlap and increase the RMS spot size with defocused light rays from neighboring object points, so the overall average RMS value remains slightly lower at 0.7um for the lens configured with laterally spaced focal points. Likewise, DF2 and DF3 are similarly unaffected by defocused light from neighboring object points. Therefore, the laterally separated optics described herein exhibit a better than Fig. 10A The coaxial based design provides improved sharpness and / or higher image quality.

[0228] Fig.12D The diagram shows Fig. 11B Spot diagram and RMS value of the near focus N-F1 of the near object point OP1 formed at the retinal plane by the bifocal contact lens of FIG. NF1 has an RMS size of 0.05 um. However, compared with, for example Fig. 10AUnlike the case of the lens configured with coaxial optics in FIG. 1 , there may be no interaction (RMS value = 0.0) of defocused light rays from the near object points OP2 and OP3 formed by the distance zone. Focus point NF1 does not overlap and increase the RMS spot size of defocused light rays from the neighboring object points, so the overall average RMS value remains slightly lower at 0.05um for the lens configured with the laterally spaced near focus rings. Likewise, NF2 and NF3 are similarly unaffected by defocused light from the neighboring object points. Therefore, the laterally spaced optics described herein show a better performance than the conventional lens. Fig. 10A The coaxial based design provides improved sharpness and / or higher image quality.

[0229] Fig.13 is a schematic diagram illustrating a plan view of an ophthalmic lens (eg, a soft bifocal contact lens) comprising laterally spaced optics for distance and near optical zones according to certain embodiments. Fig.13 A plan view of a soft bifocal contact lens having laterally spaced optics for distance and near optical zones is illustrated. In this example, both the distance power zone 1301 and the near power zone 1302 are configured with a single focus, with their optical axes configured to be laterally spaced 0.5 mm apart. This example differs from Fig. 12B An example of a method in which the lateral spacing of the near optical axis is configured to form a near focus ring spaced from and surrounding the distance optical axis. The near zone has a focal power of +2.5D. Fig.13 The lens has also been configured so that the near focus has been laterally spaced or shifted downward relative to the distance focus. The plan view shows the optical zone divided into two hemispheres: an upper zone and a lower zone.

[0230] Fig.14 It is shown that according to some embodiments Fig.13 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens. Fig.14 Also illustrated are higher magnification subplots of ray traces formed when a distant object is focused at the retinal plane (distant focus) and when a near object is focused at the image plane (near focus). In each illustration, light rays passing through the respective out-of-focus regions are represented as out-of-focus blur circles at the image plane. Fig.14 The distant objects in have been further defined by three points: the central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned 0.5 degrees to either side of OP1. Fig.14 The near objects in have been further defined by three points: the 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.

[0231] As shown in the distance focus diagram, the focal points of the distant objects OP1, OP2 and OP3 are DF1, DF2 and DF3 at the image plane and the out-of-focus rays passing through the near additional area OP1, OP2 and OP3 constitute the remaining light rays falling at the image plane (below the point of focus of the distant objects). The near focus diagram illustrates the focal points of the near objects OP1, OP2 and OP3 as NF1, NF2 and NF3 at the image plane and the out-of-focus rays passing through the distance vision area OP1, OP2 and OP3 constitute the remaining light rays falling above the near focal point at the image plane. Fig.14 The ray tracing diagram in illustrates that there is no interaction between the out-of-focus light rays of object points OP1, OP2 and OP3 and the focused images of OP1, OP2 and OP3 produced by one (or more) distance and / or near focal power regions in this example of the laterally spaced ring bifocal contact lens design.

[0232] Fig.15A and 15B is a diagram showing that according to some embodiments Fig.13 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0233] Fig.15A Illustration of a device having laterally spaced optics for distance and near optical zones. Fig.13 Spot diagram and RMS values ​​of the focal point DF1 of a distant object point OP1 formed at the retinal plane by a bifocal contact lens of FIG. 1. In this example, DF1 has an RMS size of 2.16 um. These values ​​are roughly similar to the expected values ​​of the focal point produced by a single-vision optical design. However, compared with, for example, Fig. 10A Unlike the case of the lens configured with coaxial optics in FIG. 1 , there may be no interaction (RMS value = 0) of defocused light rays from object points OP2 and OP3 formed by the near region. Focus DF1 does not overlap and increase the RMS spot size of defocused light rays from neighboring object points, so the overall average RMS value remains slightly at 2.16um for the exemplary lens configured with laterally spaced focal points. Likewise, DF2 and DF3 may also be similarly unaffected by defocused light from neighboring object points.

[0234] Fig. 15B The diagram shows Fig.13 Spot diagram and RMS values ​​of the near focus NF1 of the near object point OP1 formed at the retinal plane by a bifocal contact lens of FIG. 1. In this example, NF1 has an RMS size of 1.80 um. These values ​​are similar to the expected values ​​of the focus produced by the single vision optical design. However, compared with, for example, Fig. 10AUnlike the case of the lens configured with coaxial optics in FIG. 1 , there may be no interaction (RMS value = 0) of defocused light rays from near object points OP2 and OP3 formed by the distance zone. Focus NF1 may not overlap and increase the RMS spot size with defocused light rays from neighboring object points, so the overall average RMS value remains slightly at 1.8um for the lens configured with laterally spaced near focal points. Likewise, NF2 and NF3 may also be similarly unaffected by defocused light from neighboring object points.

[0235] Therefore, the configuration of the laterally spaced optical device described herein Fig.15A and 15B (For example, Figure 13-15B ) lenses show improved sharpness and higher image quality at both distance and near.

[0236] Fig.16 is a schematic diagram illustrating an exemplary design of an ophthalmic lens using a spherical geometry according to certain embodiments. In some embodiments, in order to reduce the discontinuity between two optical zones (e.g. Fig.13In some embodiments, the ophthalmic lens 700 may be created using two spheres 702, 704. The spheres 702, 704 have varying diameters (where the diameter of the sphere 702 is greater than the diameter of the sphere 704) and may intersect at a boundary 706. A visual zone 708 is defined and includes a first optical zone 710 and a second optical zone 712. The properties of the first optical zone 710 are defined by the sphere 702, and the properties of the second optical zone 712 are defined by the sphere 704. Since the spheres intersect at the junction 706, there may be reduced discontinuities and the need for blending (e.g., blending zones) may be reduced. In some embodiments, there may be no blending zones. Several parameters may be used to characterize the resulting lens 700. In some embodiments, the first optical zone 710 includes a first optical power and the second optical zone 712 includes a second optical power that is different from the first optical power. In some embodiments, the first optical zone includes a first optical power and the second optical zone includes a second optical power that is relatively more positive than the first optical power. In some embodiments, the first optical zone comprises a first optical power and the second optical zone comprises a second optical power that is relatively more corrected than the first optical power by approximately +0.25D to approximately +3D. In some embodiments, the second optical zone comprises a second optical power that is relatively more corrected than the first optical power by approximately +0.25D to +2.5D, approximately +0.25D to +2D, approximately +0.25D to +1.5D, approximately +0.25D to +1D, and approximately +0.25D to +0.5D. In some embodiments, the first optical zone comprises a first optical power and the second optical zone comprises a second optical power that is relatively more corrected than the first optical power by approximately +3D or more. In some embodiments, the first optical zone comprises a first optical power and the second optical zone comprises a second optical power that is relatively less correct than the first optical power. In some embodiments, the first optical zone comprises a first optical power and the second optical zone comprises a second optical power that is relatively more corrected than the first optical power by approximately -0.25D to approximately -3D. In some embodiments, the first optical zone may occupy an upper portion of an ophthalmic lens. In some embodiments, the second optical zone may occupy a lower portion of an ophthalmic lens. In some embodiments, the first optical zone may be configured to correct one of far vision, intermediate vision, or near vision; and / or the second optical zone may be configured to correct a different one of far vision, intermediate vision, or near vision. In some embodiments, the first optical zone may be configured to correct far 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 far vision.By utilizing two spheres 702 and 704 and the radii of the first and second optical zones that do not intersect along the lens surface, the images are optically spaced (eg, laterally shifted) and, therefore, the resulting RMS spot size of the retinal image can be reduced.

[0237] Fig.17 is a schematic diagram illustrating a plan view of an ophthalmic lens (eg, a soft bifocal contact lens) comprising laterally spaced optics for distance and near optical zones according to certain embodiments. Fig.17 A plan view of a soft bifocal contact lens configured with laterally spaced optics for distance and near optical zones is shown. In this example, both the distance power zone 1701 and the near power zone 1702 have been configured with a single focus with their optical axes configured to be laterally spaced 0.5 mm apart. The near add has a power of +2.5D. This exemplary lens is configured so that the near focus is laterally spaced inferiorly. The plan view shows that the optical zones are divided into two hemispheres: an upper zone and a lower zone. This example differs from Fig.13 An example in which the lateral spacing of the near optical axis is configured without modifying the lateral spacing of the junction between the distance and near optical zones. Fig.17 The intersection of these two zones in the lens is curved and has been configured so that the junction between the distance and near zones is substantially seamless and / or substantially junction less. An improved junction has been achieved by using the spherical surface curvature discussed in the present disclosure. In some embodiments, a spherical surface curvature can be utilized without utilizing a substantially seamless and / or substantially junction less configuration (e.g., a hybrid zone or step can still be utilized).

[0238] Fig.18 It is shown that according to some embodiments Fig.17 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens. Fig.18 Also provided are higher magnification panels of ray traces formed when a distant object is focused at the retinal plane (distant focus) and when a near object is focused at the retinal plane (near focus). In each panel, defocused light rays passing through unfocused areas are represented as out-of-focus blur circles at the image plane. The distant object has been 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 apart on either side of OP1. Likewise, Fig.18 The near objects in have been further defined by three points: the central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned 0.15 degrees apart on either side of OP1.

[0239] Fig.18 The distance focus diagram in illustrates the focal points of distant objects OP1, OP2 and OP3 as DF1, DF2 and DF3 at the image plane and the out-of-focus rays passing through the near additional area OP1, OP2 and OP3 constitute the remaining light rays falling at the image plane (below the focus distant object point). The near focus diagram illustrates the focal points of near objects OP1, OP2 and OP3 as NF1, NF2 and NF3 at the image plane and the out-of-focus rays passing through the distance vision area OP1, OP2 and OP3 constitute the remaining light rays falling above the near focal point at the image plane. Fig.18 The illustration shows that in these laterally spaced bifocal contact lens designs there is no interaction between out-of-focus light rays of object points OP1, OP2 and OP3 and the focused images of OP1, OP2 and OP3 produced by one (or more) distance or near power zones.

[0240] Fig.19A and 19B is a diagram showing that according to some embodiments Fig.17 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0241] Fig.19A Illustration of a device having laterally spaced optics for distance and near optical zones. Fig.17 Spot diagram and RMS values ​​of the focus DF1 of a distant object point OP1 formed at the retinal plane by a bifocal contact lens of . In this example, DF1 has an RMS size of 2.32 um. These values ​​are roughly similar to those of the focus produced by a single-vision optical design. However, compared to, for example Fig. 10A Unlike the case of the lens configured with coaxial optics in FIG. 1 , there is no interaction of defocused light rays from object points OP2 and OP3 formed by the near region (RMS value = 0). Focus DF1 does not overlap and increase the RMS spot size with defocused light rays from neighboring object points, so the overall average RMS value remains slightly at 2.32um for the lens configured with laterally spaced focal points. Likewise, DF2 and DF3 can also be similarly unaffected by defocused light from neighboring object points.

[0242] Fig.19B The diagram shows Fig.17 Spot diagram and RMS values ​​of the near focus NF1 of the near object point OP1 formed at the retinal plane by a bifocal contact lens of . In this example, NF1 has an RMS size of 1.98um. These values ​​are similar to those of the focus produced by a single vision optical design. However, compared to, for example Fig. 10AUnlike the case of the lens configured with coaxial optics in FIG. 1 , there is no interaction (RMS value = 0) of defocused light rays from the near object points OP2 and OP3 formed by the distance zone. Focus NF1 does not overlap and increase the RMS spot size of defocused light rays from the neighboring object points, so the overall average RMS value remains slightly at 1.98um for the lens configured with laterally spaced near focal points. Likewise, NF2 and NF3 can also be similarly unaffected by defocused light from the neighboring object points.

[0243] Therefore, the configuration of the laterally spaced optical device Fig.17 The lens shows Fig. 10A Improved sharpness and higher distance and near image quality of the coaxial-based design. Other examples of introducing lateral spacing optical geometries into contact or spectacle lenses can include: (1) designing for partial overlap of object images, (2) independently introducing lateral spacing into both the distance and near optical portions in equal or unequal amounts and in the same or opposite directions or other relative directions or amounts. In addition, varying the lateral spacing can affect the shape of the junction between the two optical zones, wherein a relatively smaller spacing results in a relatively more curved junction and a relatively larger spacing results in a relatively less curved junction.

[0244] Fig. 20 is a schematic diagram showing a plan view of an ophthalmic lens (e.g., a soft bifocal contact lens) according to certain embodiments, the ophthalmic lens including laterally spaced optics for distance and near optical zones. In this example, both the distance power zone 2001 and the near power zone 2002 are configured with a single focus with their optical axes configured to be laterally spaced 0.25 mm apart. The near add has a power of +2.5D. This exemplary lens is configured such that the near focus is laterally spaced inferiorly. The plan view shows that the optical zones are divided into two hemispheres: an upper zone and a lower zone. This example differs from Fig.13 An example where the lateral spacing of the near optical axis is configured with a jointless connection between the laterally spaced distal and near optical zones. Fig. 20 The intersection of these two zones in the lens of is curved and has been configured so that the junction between the distance and near zones is substantially seamless and / or substantially free of junction. An improved junction has been achieved by using a spherical surface curvature.

[0245] Fig.21 It is shown that according to some embodiments Fig. 20 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens. Fig.21Also provided are higher magnification subplots of ray traces formed when a distant object is focused at the retinal plane (distant focus) and when a near object is focused at the retinal plane (near focus). In each plot, defocused light rays passing through unfocused areas are represented as out-of-focus blur circles at the image plane. The distant objects in the distant focus plot have been further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned 0.5 degrees apart on either side of OP1. Similarly, the near objects in the near focus plot have been further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned 0.15 degrees apart on either side of OP1.

[0246] The distance focus diagram illustrates the focal points of distant objects OP1, OP2 and OP3 as DF1, DF2 and DF3 at the image plane and the out-of-focus rays passing through the near additional area OP1, OP2 and OP3 constitute the remaining light rays falling at the image plane (below the point of focus of distant objects). The near focus diagram illustrates the focal points of near objects OP1, OP2 and OP3 as NF1, NF2 and NF3 at the image plane and the out-of-focus rays passing through the distance vision area OP1, OP2 and OP3 constitute the remaining light rays falling above the near focal point at the image plane. Fig.21 The diagram illustrates the interaction between out-of-focus light rays for a distant object point through the near zone on DF-1 and DF-2 but not on DF-3, while the near focus diagram shows the interaction between out-of-focus light rays for a near object point through the distance zone (by the distance power zone) on NF-3 in these laterally spaced bifocal contact lens designs.

[0247] Fig.22A and 22B is a diagram showing that according to some embodiments Fig. 20 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0248] Fig.22A Illustration of a device having laterally spaced optics for distance and near optical zones. Fig. 20 Spot diagram and RMS values ​​of the focal point DF1 of a distant object point OP1 formed at the retinal plane by a bifocal contact lens of FIG. 1. In this example, DF1 has an RMS size of 1.93 um. These values ​​are roughly similar to those of the focal point produced by a single-vision optical design. However, unlike Fig.17Unlike the case of the lens configured with larger laterally spaced focal points, there is some interaction of defocused light rays from object point OP3 formed on DF-1 by the near region (RMS value = 162.6 um) but no interaction of defocused light rays from OP2 formed on DF-1 (RMS value = 0 um). Therefore, for this lens configured with laterally spaced focal points, the overall blur of focus D-F1 may still be affected by defocused light rays from neighboring object points that overlap and increase the RMS spot size (overall average RMS value 93.88 um). Ray tracing also indicates that D-F2 is also similarly affected by defocused light from neighboring object points, while DF-3 is not.

[0249] Fig. 22B The diagram shows Fig. 20 Spot diagram and RMS values ​​of the near focus NF1 of the near object point OP1 formed at the retinal plane by the bifocal contact lens of FIG. NF1 has an RMS size of 1.84 um. These values ​​are similar to those of the focus produced by the single vision optical design. However, compared with Fig.22A Unlike when focusing on a distant object, there may be no interaction (RMS value = 0) of defocused light rays from near object points OP2 and OP3 formed by the distant region. Focus NF1 does not overlap and increase the RMS spot size with defocused light rays from neighboring object points, so the overall average RMS value remains slightly at 1.84um for lenses configured with laterally spaced near focal points.

[0250] therefore, Fig. 20 The lens of illustrates that the lenses configured with laterally spaced optics described herein can manipulate image quality differentially between distance and near focus.

[0251] Fig.23 is a schematic diagram showing a plan view of an ophthalmic lens (e.g., a soft bifocal contact lens) according to certain embodiments, the ophthalmic lens including laterally spaced optics for distance and near optical zones. In this example, both the distance power zone 2301 and the near power zone 2302 are configured with a single focus, wherein their distance and near optical axes are configured to be laterally spaced 0.25 mm inferiorly and 0.50 mm superiorly relative to the optical center of the contact lens. The near add has a power of +2.5D. This exemplary lens is configured so that the near focus is located inferiorly. The plan view shows that the optical zone is divided into two hemispheres: an upper zone and a lower zone. This example differs from Fig.13 An example in which the lateral spacing of the near optical axis is configured without modifying the lateral spacing of the junction between the distance and near optical zones. Fig.26The intersection of these two zones in the lens of is curved and has been configured so that the junction between the distance and near zones is substantially seamless and / or substantially free of junction. An improved junction has been achieved by using a spherical surface curvature.

[0252] Fig.24 It is shown by Fig.23 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens. Fig.24 Also provided are higher magnification insets of ray traces formed when a distant object is focused at the retinal plane (distant focus) and when a near object is focused at the retinal plane (near focus). In each figure, defocused light rays passing through unfocused areas are represented as out-of-focus blur circles at the image plane. The distant objects in the distant focus figures have been further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned 0.5 degrees apart on either side of OP1. Likewise, Fig.24 The near objects in have been further defined by three points: the central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned 0.15 degrees apart on either side of OP1.

[0253] The distance focus diagram illustrates the focal points of distant objects OP1, OP2 and OP3 as DF1, DF2 and DF3 at the image plane, and the out-of-focus rays passing through the near additional area OP1, OP2 and OP3 constitute the remaining light rays falling at the image plane (below the point of focus of the distant objects). The near focus diagram illustrates the focal points of near objects OP1, OP2 and OP3 as NF1, NF2 and NF3 at the image plane, and the out-of-focus rays passing through the distance vision area OP1, OP2 and OP3 constitute the remaining light rays falling above the near focal point at the image plane. Fig.24 The illustration shows that in these laterally spaced bifocal contact lens designs there is no interaction between out-of-focus light rays of object points OP1, OP2 and OP3 and the focused images of OP1, OP2 and OP3 produced by one (or more) distance or near power zones.

[0254] Fig.25A and 25B is a diagram showing that according to some embodiments Fig.23 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0255] Fig.25A Illustration of a device having laterally spaced optics for distance and near optical zones. Fig.17Spot diagram and RMS values ​​of the focal point D-F1 of a distant object point OP1 formed at the retinal plane by a bifocal contact lens of FIG. 1. In this example, DF1 has an RMS size of 5.71 um. These values ​​are roughly similar to the expected values ​​of the focal point produced by a single-vision optical design. However, compared with, for example, Fig. 10A Unlike the case of the lens configured with coaxial optics in FIG. 1 , there is no interaction of defocused light rays from object points OP2 and OP3 formed by the near region (RMS value = 0). Focus DF1 does not overlap and increase the RMS spot size with defocused light rays from neighboring object points, so the overall average RMS value remains slightly at 5.71 um for the lens configured with laterally spaced focal points. Similarly, D-F2 and D-F3 can also be similarly unaffected by defocused light from neighboring object points.

[0256] Fig.25B The diagram shows Fig.23 Spot diagram and RMS values ​​of the near focus N-F1 of the near object point OP1 formed at the retinal plane by a bifocal contact lens of FIG. 1. In this example, NF1 has an RMS size of 2.01 um. These values ​​are similar to those of the focus produced by a single vision optical design. However, compared to, for example, Fig. 10A Unlike the case of the lens configured with coaxial optics in FIG. 1 , there is no interaction (RMS value = 0) of defocused light rays from the near object points OP2 and OP3 formed by the distance zone. Focus NF1 does not overlap and increase the RMS spot size of defocused light rays from the neighboring object points, so the overall average RMS value remains slightly at 2.01um for the lens configured with laterally spaced near focal points. Likewise, NF2 and NF3 can also be similarly unaffected by defocused light from the neighboring object points.

[0257] Therefore, the configuration has long-distance and near focal points with different amounts of lateral separation. Fig.23 The lens can still maintain the ratio of Fig. 10A The coaxial-based design improves sharpness and higher image quality at both long and near distances.

[0258] Fig.26 is a schematic diagram showing a plan view of an ophthalmic lens (e.g., a bifocal spectacle lens) according to certain embodiments, the ophthalmic lens including laterally spaced optics for distance and near optical zones. In this example, both the distance power zone 2601 and the near power zone 2602 are configured with a single focus, wherein their optical axes are configured to be laterally spaced 0.5 mm apart. The near add has a power of +2.5D. Fig.26 The lens has also been configured so that the near focus has been laterally spaced or shifted downward. The plan view shows that the optical zone is divided into two zones: an upper zone and a lower zone. Fig.23The contact lens described in the embodiment of the present invention, this example of a spectacle lens is configured such that the junction between the distance and near zones is substantially seamless and / or substantially free of junction. An improved junction has been achieved by using a spherical front surface curvature, and in this example, the junction may be non-linear due to the lateral and downward spacing from the near focus being selected to be 0.5 mm.

[0259] Fig. 27 It is shown that according to some embodiments Fig.26 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens. Fig. 27 Also provided are higher magnification sub-graphs of ray traces formed when a distant object is focused at the retinal plane (distant focus) and when a near object is focused at the retinal plane (near focus). In each of the graphs, light rays passing through the respective out-of-focus regions are represented as out-of-focus blur circles at the image plane. The distant objects in the distant focus graph have been further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned 0.50 degrees apart on either side of OP1. Similarly, the near objects in the near focus graph have been further defined by three points: a central object point 1 (OP1) on the axis, and points 2 and 3 (OP2 and OP3) positioned 0.15 degrees apart on either side of OP1.

[0260] The distance focus diagram illustrates the focal points of distant objects OP1, OP2 and OP3 as DF1, DF2 and DF3 at the image plane and the out-of-focus rays passing through the near additional area OP1, OP2 and OP3 constitute the remaining light rays falling at the image plane (below the point of focus of distant objects). The near focus diagram illustrates the focal points of near objects OP1, OP2 and OP3 as NF1, NF2 and NF3 at the image plane and the out-of-focus rays passing through the distance vision area OP1, OP2 and OP3 constitute the remaining light rays falling above the near focal point at the image plane. Fig. 27 The illustration shows that there is no interaction between out-of-focus light rays of object points OP1, OP2 and OP3 and the images of OP1, OP2 and OP3 produced by one (or more) distance or near power zones in these laterally spaced ring spectacle lens designs.

[0261] Fig.28A and 28B is a diagram showing that according to some embodiments Fig.26 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0262] Fig.28A The diagram shows Fig.26Spot diagram and RMS values ​​of focus DF1 of a distant object point OP1 formed at the retinal plane by a spectacle lens having laterally spaced optics for sampling the distance and near optical zones over a 5 mm aperture at the spectacle lens plane. In this example, DF1 has an RMS size of 0.49 um. These values ​​are similar to those of the focus produced by a single vision optical design of similar aperture size. However, in contrast to e.g. Fig. 10A Unlike the case of the lens configured with coaxial optics in FIG. 1 , there is no interaction (RMS value = 0) of defocused light rays from object points OP2 and OP3 formed by the near area. Focus DF1 does not overlap and increase the RMS spot size of defocused light rays from neighboring object points, so the overall average RMS value remains slightly at 0.49um for the lens configured with laterally spaced focal points. Likewise, DF2 and DF3 can also be similarly unaffected by defocused light from neighboring object points.

[0263] Fig.28B The diagram shows Fig.26 Spot diagram and RMS value of near focus NF1 of near object point OP1 formed by a spectacle lens at the retinal plane. In this example, NF1 has an RMS size of 0.42um. These values ​​are similar to the expected values ​​of the focus produced by the single-vision optical design due to the lack of interaction of defocused light rays from near object points OP2 and OP3 formed by the distance zone (RMS value = 0). Focus NF1 does not overlap and increase the RMS spot size of defocused light rays from neighboring object points, so the overall average RMS value remains slightly at 0.42um for the lens configured with laterally spaced near focus points. Likewise, NF2 and NF3 can also be similarly unaffected by defocused light from neighboring object points.

[0264] Therefore, the configuration of the laterally spaced optical device described herein Fig.26 The spectacle lenses show a difference of Fig. 10A The coaxial-based design improves sharpness and higher image quality at both long and near distances.

[0265] Fig.29A is a schematic diagram showing a plan view of a bifocal spectacle lens. Fig.29A As shown, the bifocal spectacle lens includes a discontinuous junction between a distance zone 2901 and a near zone 2902 .

[0266] Fig.29Bis a schematic diagram showing a plan view of an ophthalmic lens (e.g., a bifocal spectacle lens) according to certain embodiments, the ophthalmic lens including laterally spaced optics for a distance optical zone 2911 and a near optical zone 2912. In this example, both the distance and near power zones are configured with a single focus, with their optical axes configured to be laterally spaced 1 mm apart. The near add has a power of +2.5D. Fig.29B The lens has also been configured so that the near focus is laterally spaced or shifted downward. The plan view shows that the optical zone is divided into two zones: an upper zone and a lower zone. Fig.26 Spectacle lenses described in, Fig.29B This example of a spectacle lens of is also configured such that the junction between the distance and near zones is substantially seamless and / or substantially free of junction. An improved junction can be achieved by using a spherical front surface curvature, and in this example, the junction can be non-linear because the lateral and downward spacing of the near focus is selected to be 1 mm. However, unlike Fig.26 Compared with the example shown in (where the lateral spacing value is 0.5 mm), the example shown in (where the lateral spacing value is 1 mm) Fig.29B The lenses of have made the junction between the distance and near zones less curved and widened the near zone of the eyeglass lens to increase the field of view through the near zone.

[0267] Fig.30 It is shown that according to some embodiments Fig.29B Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens. Fig.30 Also provided are higher magnification sub-graphs of ray traces formed when a distant object is focused at the retinal plane (distant focus) and when a near object is focused at the retinal plane (near focus). In each of the graphs, light rays passing through the respective out-of-focus regions are represented as out-of-focus blur circles at the image plane. The distant objects in the distant focus sub-graph have been further defined by three points: a central object point 1 (OP1) on the axis and points 2 and 3 (OP2 and OP3) positioned 0.50 degrees apart on either side of OP1. Similarly, the near objects in the near focus sub-graph have been further defined by three points: a central object point 1 (OP1) on the axis and points 2 and 3 (OP2 and OP3) positioned 0.15 degrees apart on either side of OP1.

[0268] The distance focus diagram illustrates the focal points of distant objects OP1, OP2 and OP3 as DF1, DF2 and DF3 at the image plane and the out-of-focus rays passing through the near additional area OP1, OP2 and OP3 constitute the remaining light rays falling at the image plane (below the point of focus of distant objects). The near focus diagram illustrates the focal points of near objects OP1, OP2 and OP3 as NF1, NF2 and NF3 at the image plane and the out-of-focus rays passing through the distance vision area OP1, OP2 and OP3 constitute the remaining light rays falling above the near focal point at the image plane. Fig.30 The diagram illustrates the larger separation between focused and out-of-focus light at the image plane, and the absence of interaction between the out-of-focus light rays at object points OP1, OP2 and OP3 and the images of OP1, OP2 and OP3 produced by one (or more) distance or near power zones in these laterally spaced annular spectacle lens designs.

[0269] Fig.31A and 31B is a diagram showing that according to some embodiments Fig.29B Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0270] Fig.31A The diagram shows Fig.29B Spot diagram and RMS values ​​of focus DF1 of a distant object point OP1 formed at the retinal plane by a spectacle lens having laterally spaced optics for sampling the distance and near optical zones over a 5 mm aperture at the spectacle lens plane. In this example, DF1 has an RMS size of 0.72 um. These values ​​are similar to those of the focus produced by a single vision optical design of similar aperture size. However, in contrast to e.g. Fig. 10A Unlike the case of the lens configured with coaxial optics in FIG. 1 , there is no interaction (RMS value = 0) of defocused light rays from object points OP2 and OP3 formed by the near area. Focus DF1 does not overlap and increase the RMS spot size with defocused light rays from neighboring object points, so the overall average RMS value remains slightly at 0.72um for the lens configured with laterally spaced focal points. Likewise, DF2 and DF3 can also be similarly unaffected by defocused light from neighboring object points.

[0271] Fig.31B The diagram shows Fig.29BSpot diagram and RMS value of near focus NF1 of near object point OP1 formed by a spectacle lens at the retinal plane. In this example, NF1 has an RMS size of 0.8um. ​​These values ​​are similar to the expected values ​​of the focus produced by the single-vision optical design due to the lack of interaction (RMS value = 0) of defocused light rays from near object points OP2 and OP3 formed by the distance zone. Focus NF1 does not overlap and increase the RMS spot size of defocused light rays from neighboring object points, so the overall average RMS value remains slightly at 0.8um for the lens configured with laterally spaced near focus points. Likewise, NF2 and NF3 can also be similarly unaffected by defocused light from neighboring object points.

[0272] Therefore, the configuration of the laterally spaced optical device described herein Fig.29B The spectacle lenses can show more Fig. 10A The coaxial-based design improves sharpness and higher image quality at long and near distances. In addition, with e.g. Fig.26 The increased lateral spacing of the focal points can widen the near zone and the field of view through the near zone compared to lenses configured with smaller focal spacing as described in .

[0273] Fig.32 is a schematic diagram showing a plan view of an ophthalmic lens (e.g., a bifocal spectacle lens) according to certain embodiments, the ophthalmic lens including laterally spaced optics for a distance optical zone 3201 and a near optical zone 3202. In this example, both the distance and near power zones are configured with a single focus, with their optical axes configured to be laterally spaced 0.5 mm apart. The near add has a power of +2.5D. However, unlike Fig.29B lenses in which only the near focus is laterally spaced or shifted downward, Fig.32 The lens in has been configured so that the distance focus has been displaced 0.25 mm in the upper portion, while the near focus has been displaced downward by an equal and opposite amount of 0.25 mm, for a total net lateral spacing of 0.5 mm between the focal points. The plan view shows that the optical zone is divided into two zones: an upper zone and a lower zone. As Fig.29B The spectacle lens described in , this spectacle lens example is configured so that the junction between the distance and near zones is substantially seamless and / or substantially free of junction. An improved junction can be achieved by using a spherical front surface curvature.

[0274] Fig.33 It is shown that according to some embodiments Fig.32 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens. Fig.33Also provided are higher magnification sub-graphs of ray traces formed when a distant object is focused at the retinal plane (distant focus) and when a near object is focused at the retinal plane (near focus). In each of the graphs, light rays passing through the respective out-of-focus regions are represented as out-of-focus blur circles at the image plane. The distant objects in the distant focus graph are further defined by three points: a central object point 1 (OP1) on the axis and points 2 and 3 (OP2 and OP3) positioned 0.5 degrees apart on either side of OP1. Similarly, the near objects in the near focus sub-graph have been further defined by three points: a central object point 1 (OP1) on the axis and points 2 and 3 (OP2 and OP3) positioned 0.15 degrees apart on either side of OP1.

[0275] The distance focus diagram illustrates the focal points of distant objects OP1, OP2 and OP3 as DF1, DF2 and DF3 at the image plane and the out-of-focus rays passing through the near additional area OP1, OP2 and OP3 constitute the remaining light rays falling at the image plane (below the point of focus of distant objects). The near focus diagram illustrates the focal points of near objects OP1, OP2 and OP3 as NF1, NF2 and NF3 at the image plane and the out-of-focus rays passing through the distance vision area OP1, OP2 and OP3 constitute the remaining light rays falling above the near focal point at the image plane. Fig.33 The diagram illustrates the spacing between focused and out-of-focus light at the image plane on either side of the geometric center of the 5 mm aperture in the eyeglass lens plane and the absence of interaction between the out-of-focus light rays at object points OP1, OP2 and OP3 and the images of OP1, OP2 and OP3 produced by one (or more) distance or near power zones in these laterally spaced ring eyeglass lens designs.

[0276] Fig.34A and 34B It is shown by Fig.32 Schematic diagram of the point diagram and RMS value of the focal points DF1 and NF1 of the object point OP1 formed by the ophthalmic lens at the retinal plane.

[0277] Fig.34A The diagram shows Fig.32 Spot diagram and RMS values ​​of focus DF1 of a distant object point OP1 formed at the retinal plane by a spectacle lens having laterally spaced optics for sampling the distance and near optical zones over a 5 mm aperture at the spectacle lens plane. In this example, DF1 has an RMS size of 0.8 um. These values ​​are similar to those of the focus produced by a single vision optical design of similar aperture size. However, in contrast to e.g. Fig. 10AUnlike the case of the lens configured with coaxial optics in FIG. 1 , there may be no interaction (RMS value = 0) of defocused light rays from object points OP2 and OP3 formed by the near area. Focus DF1 does not overlap and increase the RMS spot size of defocused light rays from neighboring object points, so the overall average RMS value remains slightly at 0.84um for the lens configured with laterally spaced focal points. Likewise, DF2 and DF3 may also be similarly unaffected by defocused light from neighboring object points.

[0278] Fig.34B The diagram shows Fig.32 Spot diagram and RMS value of near focus NF1 of near object point OP1 formed by a spectacle lens at the retinal plane. In this example, NF1 has an RMS size of 1.49um. These values ​​are similar to the expected values ​​of the focus produced by the single-vision optical design due to the lack of interaction of defocused light rays from near object points OP2 and OP3 formed by the distance zone (RMS value = 0). Focus NF1 does not overlap and increase the RMS spot size of defocused light rays from neighboring object points, so the overall average RMS value remains slightly at 1.49um for the lens configured with laterally spaced near focus points. Likewise, NF2 and NF3 can also be similarly unaffected by defocused light from neighboring object points.

[0279] Therefore, the configuration of the laterally spaced optical device described herein Fig.32 The spectacle lenses show a difference of Fig. 10A The coaxial-based design improves sharpness and higher long-distance and near image quality. In addition, the lateral spacing of both long-distance and near focal points in the upper and lower parts, respectively, does not affect the desired image quality of focal points DF-1 and NF-1.

[0280] Fig.35 is a schematic diagram showing a plan view of an ophthalmic lens (e.g., a bifocal spectacle lens) according to certain embodiments, the ophthalmic lens including laterally spaced optics for a distance optical zone 3501 and a near optical zone 3502. In this example, both the distance and near power zones are configured with a single focus, wherein their optical axes and focal points are configured to be laterally spaced 0.5 mm apart. The near add has a power of +2.5D. As Fig.35 lenses, Fig.35 The lens in has been configured so that the distance focus has been displaced 0.25mm in the upper portion, while the near focus has been displaced downward by an equal and opposite amount of 0.25mm, with a total net lateral spacing of 0.5mm between the focuses. The plan view shows the optical zone divided into two zones: an upper zone and a lower zone. In this example the upper zone contains the distance power, while the lower zone contains both the peripheral near power zone and the distance power zone. As Fig.32The spectacle lens described in the embodiment of the present invention is configured such that the junction between the distance and near zones is substantially seamless and / or substantially free of junctions. The substantially seamless and / or substantially free of junctions intersection between the zones can be achieved by using a spherical front surface curvature. When the optical axis and the focal point are laterally spaced, a certain amount of prismatic power can be introduced into the spectacle lens. Fig.35 The lens has been designed with a spherical back surface curvature that creates an equal and opposite amount of lateral spacing (-0.25 mm) to that provided to the distance and near zones of the front surface. The net result of this back surface design is that the prismatic power introduced by the front surface design is eliminated while retaining the advantages of lateral spacing of the distance and near optical zones in creating a substantially seamless and / or substantially seam-free intersection.

[0281] Fig.36 It is shown by Fig.35 Schematic illustration of ray tracing of distant and near objects imaged by an ophthalmic lens. Fig.36 Also provided are higher magnification sub-graphs of ray traces formed when a distant object is focused at the retinal plane (distant focus) and when a near object is focused at the retinal plane (near focus). In each of the graphs, light rays passing through the respective out-of-focus regions are represented as out-of-focus blur circles at the image plane. The distant objects in the distant focus graph are further defined by three points: a central object point 1 (OP1) on the axis and points 2 and 3 (OP2 and OP3) positioned 0.5 degrees apart on either side of OP1. Similarly, the near objects in the near focus sub-graph have been further defined by three points: a central object point 1 (OP1) on the axis and points 2 and 3 (OP2 and OP3) positioned 0.15 degrees apart on either side of OP1.

[0282] The distance focus diagram illustrates the focal points of the distant objects OP1, OP2 and OP3 as DF1, DF2 and DF3 at the image plane and the out-of-focus rays passing through the near additional area OP1, OP2 and OP3 constitute the remaining light rays falling at the image plane (above the focus distant object point). The near focus diagram illustrates the focal points of the near objects OP1, OP2 and OP3 as NF1, NF2 and NF3 at the image plane and the out-of-focus rays passing through the distance vision area OP1, OP2 and OP3 constitute the remaining light rays falling at the image plane. Fig.36 The diagram illustrates the spacing between focused and out-of-focus light at the image plane on either side of the geometric center of the 5 mm aperture in the plane of the eyeglass lens, and the degree of interaction between the out-of-focus light rays of object points OP1, OP2 and OP3 and the images of OP1, OP2 and OP3 produced by one (or more) distance or near focal power zones in these laterally spaced eyeglass lens designs that incorporate laterally spaced optical axes and focal points.

[0283] Fig.37A and 37B is a diagram showing that according to some embodiments Fig.35 Schematic diagram of the spot diagram and RMS values ​​of the focal points DF1 and NF1 of the corresponding object point OP1 formed by an ophthalmic lens at the retinal plane. In this example, DF1 has an RMS size of 5.79um. The small amount of lateral separation of the focal points (0.25mm) is not enough to eliminate the overlap of out-of-focus light on DF1 from passing through the near zone. However, in contrast to e.g. Fig. 10A Unlike the case of an ophthalmic lens configured with coaxial optics in the example, even with a relatively small amount of lateral spacing (0.25 mm) such as used in the example, there is still no interaction (RMS value = 0) of defocused light rays from distant object points OP2 and OP3 formed by the near zone. Focus DF1 only has defocused light rays from the object point that overlaps and increases the reduced amount of RMS spot size, so the overall average RMS value remains slightly at 5.79um for the lens configured with laterally spaced focal points. Likewise, DF2 and DF3 will also be similarly affected by defocused light from neighboring object points.

[0284] Fig.37B The diagram shows Fig.36 Spot diagram and RMS value of near focus NF1 of near object point OP1 formed by the eyeglass lens at the image plane. In this example, NF1 has an RMS size of 1.84um. These values ​​are similar to the expected values ​​of the focus produced by the single-vision optical design due to the lack of interaction (RMS value = 0) of defocused light rays from near object points OP2 and OP3 formed by the distance zone. However, since the back surface is designed to optically eliminate the lateral separation of the focus to offset the induced prismatic power of the overall lens, the focus NF1 has no coverage from the adjacent object point OP2 and increases the RMS spot size to 41.29um, so the overall average RMS value is increased to 23.86um for the lens configured without prismatic power. Similarly, NF2 and NF3 can also be similarly affected by the defocused light from the adjacent object points without the residual lateral separation of the focus.

[0285] Therefore, the front and rear surfaces are provided with laterally spaced optical devices. Fig.36 The spectacle lenses exhibit a substantially seamless and / or substantially seam-free surface without prismatic power, but with a slight detriment to image quality. Image quality may be improved to single vision quality with a slight increase in lateral spacing and the introduction of a small amount of prismatic power.

[0286] Fig.38is a schematic diagram of a progressive addition lens (PAL) according to certain embodiments. A PAL lens can be designed with a distance zone 3801 that can be larger than the distance zone available for conventional PAL-type lenses; and a near power zone 3802 located at the bottom surrounded by one or more progressive power zones. The progressive power zone in this example progresses in three steps from the distance diopter to the full near diopter of +2.5D. In some embodiments, an increase in the power progression profile can be incorporated into this lens design based on the patient's refractive and visual requirements and the desired focal length progression. In this example, the focal length progression is about 17mm. The three power zones and their focal points in the progressive power zone of this example are laterally spaced from the distance focus. The first, second, and third power zones of the progressive power zone are laterally spaced 1.5mm from the distance power focus. In this example, the front surface curvature of the distance zone and the progressive power zone is spherical, and the joints between the zones are substantially seamless and / or substantially free of joints (e.g., little or no blending is required). The diameter of the first zone in the progressive power area is larger than that of the second progressive power area, and both the first and second zones are larger in diameter than the third progressive area. The position of the improved junction of this example is Fig.38 Lines B, C, D and E are illustrated in FIG. 1 , but are substantially invisible to the viewer and no actual lines or markings exist on the ophthalmic lens. Fig.38 Schematic diagram including the profile of a PAL eyeglass lens. A smooth progressive power profile and spherical surface curvature and substantially seamless and / or substantially seam-free intersections of the surface curvatures are shown along with the hypothetical locations of seam lines B, C, D and E.

[0287] Fig.38 The PAL lens shown in has been designed so that there is a 1.5 mm lateral spacing between the optical axis of the distance zone, on which the distance focus is formed, and the first optical axis and the first focus of the three power zones of the progressive power zone. Therefore, a certain amount of prismatic power is introduced to the front surface of the PAL eyeglass lens through the difference in surface curvature of the zone. However, similar to Fig.35 lenses, Fig.38 PAL eyeglass lenses have been designed with a back surface that creates an amount of lateral spacing (e.g., -1.5 mm) that is equal (or substantially equal) and opposite (or substantially opposite) to that provided to the front surface progressive power zone in the lower region of the lens. The net result of incorporating this opposite amount of lateral spacing in the back surface curvature can be that the prismatic power introduced in the lower zone of the front surface can be eliminated while retaining the advantages of lateral spacing of the distance and near optical zones in creating a substantially seamless and / or substantially seam-free intersection.

[0288] Fig.39 is shown for forming Fig.38. The figure shows the optical center A of the lens, the location B of the imaginary connection of the upper and lower zones of the lens, and three progressive power zones C, D and E. The upper zone of the lens in this example contains only the distance power. The lower zone can be a zone where a portion of the zone contains the progressive power zone and the near power zone and the rest is the distance power zone. The upper distance power zone can be described by a spherical curvature, and the lower zone can be described by a series of spherical curvatures to create three powers in the progressive power zone, and the rest is the same curvature as describing the distance power. The values ​​are in millimeters, where the distance radius is 180 and the near radius is R93, R120 and R150. The lateral spacing of the progressive power zones can be shown as the distance difference between the optical center A of the lens and the progressive power zones.

[0289] Fig.40 Detailed Fig.39 Power diagrams for the PAL eyeglass lens designs shown in . Two power diagrams covering the eyeglass lens zones. Mean spherical power for a PAL eyeglass lens designed with lateral spacing of distance and progressive power zones Fig.35 mm x 35mm and cylindrical power Fig.35 mm x 60mm. In this example, the spherical power diagram shows large, wide areas of uniform power in the distance power, progressive power, and near power zones. Fig.40 The spherical and cylindrical power diagrams shown in are substantially more uniform and significantly wider average spherical power areas (than those of other PAL designs) that are substantially free of blended zones and overall and surface cylindrical powers, yet still provide a substantially seamless and substantially seam-free surface. Thus, ophthalmic lens designs and constructions have maintained substantially similar tangential and sagittal surface curvatures and powers through a progressive channel. In order to provide a channel of progressive powers in a substantially seam-free surface, prior art PAL designs suffer from significant blended zones containing significant cylindrical powers greater than 0.5DC, greater than 1.DC, and even greater than 2.DC.

[0290] Fig.39The exemplary embodiment PAL spectacle lens depicted in is symmetrical about the vertical meridian. Additional embodiments of the PAL spectacle lens can be designed for customized or personalized parameters desired by the wearer or practitioner (e.g., the size or location of the desired distance and progressive zones). The PAL lens can be asymmetrical, for example, and can be designed for the right eye or the left eye, as well as changes in eye convergence and the associated distance changes between the two eyes when looking from distance vision to near vision, or a user's preference to shift the object being looked at to one side when using a portion of the progressive focal zone. The PAL spectacle lens can be designed with a certain amount of lateral spacing, and this lateral spacing can be distributed between the lens zones to the upper and lower portions of the lens and to the desired extent between the distance zone and the progressive zone and within the progressive zone. The lateral spacing can be distributed between the front and rear surfaces to the desired appropriate extent to meet the ophthalmic needs of the wearer, practitioner, manufacturer, and / or manufacturing process. The design can be included in whole or in part on the front surface of the ophthalmic lens or on the rear surface of the ophthalmic lens. The lateral spacing of the optical axis can be contained in whole or in part in the semi-finished lens blank, and once the patient's complete prescription is determined and ordered, the final desired lens design can be completed in the final manufacturing process at the same location or at a different location and at a different time. The new design can be applied to suitable manufacturing processes, such as other ophthalmic lenses, spectacle lenses, contact lenses or intraocular lenses. In the case of spectacle lenses and, for example, PALs, the lens can be fully molded, partially produced on a semi-finished blank or single-vision blank containing a front or back surface portion of the PAL surface, and the PAL can be surface-treated on the back surface of the blank by a surface cutting and polishing process. Ophthalmic lenses can be constructed and applied to improve the efficiency of the manufacturing process and supply chain by using a reduced number of inventory semi-finished blanks or base arc blanks, or to reduce the need for unique left-right asymmetric designs because the field of view of the vision correction area is wider.

[0291] The axes of final spherical and cylindrical power and astigmatism power desired for the patient's refractive error can be completed in a finishing step from a stock of semi-finished or unfinished lens blanks in a laboratory or office. The final lateral spacing of the optical axes can also be completed to the desired levels during the final finishing step along with the progressive power profile and fit height and interpupillary distance required for the most desired function of presbyopia or myopia. For example, residual prismatic power that may be present on a semi-finished or finished lens blank can be eliminated by the final finishing production of the eyeglass lens. For example, it may be desired that the prismatic power be less than 0.12D or 0.25D or less than 0.5D or less than 1.5D or less than 3D prismatic power or more.

[0292] Extended Depth of Focus (EDOF)

[0293] In some embodiments, the ophthalmic lenses described herein may provide an extended depth of focus (EDOF). In some embodiments, light rays passing through the ophthalmic lens and converging to form one or more off-axis focal points continue further beyond the one or more off-axis focal points and may provide an EDOF together with the on-axis light rays. In some embodiments, light rays passing through the ophthalmic lens and converging to form one or more off-axis focal points continue further beyond the one or more off-axis focal points and may provide good image quality for the EDOF together with the on-axis light rays. In some embodiments, a desired amount of EDOF may be achieved by having a desired amount of focal lateral spacing between one or more on-axis and one or more off-axis focal points, wherein the focal lateral spacing between the on-axis and off-axis focal points is caused by the ophthalmic lens incorporating an optically perpendicular configuration to the surface. In some embodiments, a desired amount of EDOF may be achieved using an ophthalmic lens incorporating a first and a second optical zone, wherein the power profile of the second optical zone combines a relatively more negative power (m component) and a relatively more positive power (p component) than the first zone power and wherein m=p<+ / -20%. In some embodiments, the EDOF is substantially in front of the retinal image plane.

[0294] Fig.41 is a schematic diagram showing an ophthalmic lens 4100, which includes a first optical zone 4101 having a first focal power; at least one second zone 4102, which is concentric with the first optical zone and has a curvature structure referred to as a configuration that is geometrically perpendicular to the substrate surface (i.e., curvature). Geometric features perpendicular to the substrate (here, the substrate refers to the first optical zone) surface can be used to configure or achieve a desired amount of lateral spacing between the off-axis focus formed by the second optical zone 4102 and the on-axis focus formed by the first optical zone 4101. As shown Fig.41 As shown, the curvature that is geometrically perpendicular to the surface is where the center of the second optical zone 4102 of the ophthalmic lens 4100, the center of the curvature / arc of 4102, and the center of curvature of the first optical zone can be located along a single line. In some embodiments, the optical axes of the first and second optical zones of a lens designed with features that are geometrically perpendicular to the surface can be separated by a specific amount of lateral spacing. Configuring the second optical zone 4102 to be geometrically perpendicular to the surface can cause the second optical zone to be discontinuous (not a smooth transition) with surrounding areas (e.g., the first optical zone and the third annular optical zone 4103).

[0295] Fig.42is a schematic diagram of an on-axis power profile of an optical zone of an ophthalmic lens configured with a first central optical zone 4201 and an annular second optical zone 4202 configured to be geometrically perpendicular to the base (i.e., the central optical zone). As shown, the first optical zone 4101 can have a first power 4201 that is more positive than the distance refractive error power of the eye, and thus light traveling through the first optical zone can result in one or more focal points at planes other than the retina of the eye and a third optical zone 4203 whose power is used to provide an on-axis focus that coincides with the central zone focus. The second annular optical zone 4102 can incorporate a power profile 4202 that has a component that is more positive ("p", 4202a) and / or more negative ("m", 4202b) relative to the first power 4201 and a progressive power profile component 4202c that increases from 4202d to 4202e in positive power. The absolute power difference between 4202d and 4202e is a measure of the on-axis depth of focus in diopters. The "m" component arises from a discontinuity geometrically perpendicular to the surface between the innermost portions of the first optical zone and the second optical zone; the "p" component arises from a discontinuity geometrically perpendicular to the surface between the outermost portion of the second optical zone and the innermost portion of the third optical zone, thereby providing a coaxial focus coincident with the central zone. The progressive power distribution 4202c in the second annular optical zone connecting 4202d and 4202e can be an inclined (e.g., curved, curvilinear or linear or other) power distribution, depending on the surface configuration of the second optical zone and the lateral spacing of the optical axes of the first and second optical zones. Fig.41In an embodiment, an ophthalmic lens is configured with features that are geometrically perpendicular to the surface, thereby creating a lateral spacing between the on-axis and off-axis focal points, resulting in an on-axis focal power distribution where m=p is < about ±20%. When m=p<about ±20%, the ophthalmic lens is considered to satisfy the "optically perpendicular to the surface condition". In some embodiments, an ophthalmic lens configured with a configuration that is optically perpendicular to the surface provides better image quality because a configuration that is geometrically perpendicular to the substrate surface may not result in the lens satisfying conditions such as (as an example) m=p<about ±20%. As the difference between m and p becomes larger, the image quality along the depth of focus is impaired by increased interference between on-axis light rays and off-axis light rays. In some embodiments, the position and diameter of the first optical zone can affect the m:p ratio. For example, a smaller central optical zone (e.g., < about 2 mm) may result in an m:p ratio > 20% because the light rays passing through the innermost portion of the second optical zone tend to be flatter (more parallel and causing the 'm' to have a greater relative negative power than the 'p' component), and therefore the angle between these rays and the optical axis is reduced, resulting in the rays intersecting the optical axis, which may result in the 'm' component having a relatively more negative power than the 'p' component, and increased interference between on-axis and off-axis light rays at the image plane along the depth of focus. In addition, the geometrically normal to the surface configuration on a wider (e.g., > 1.5 to 2.0 mm or larger) second optical zone may not maintain the geometrically normal to the surface configuration. As the zone widens, the outermost portion of the second optical zone may increase the p component, and therefore, increase the interference between on-axis and off-axis light rays at the image plane along the depth of focus.

[0296] Therefore, in the exemplary embodiments described herein, in order to achieve a depth of focus that does not substantially compromise image quality, the 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 combining one or more features that are optically perpendicular to the surface, which is obtained by considering and combining one or more of the following features: a) substantially similar discontinuities at both edges of the second optical zones, b) the components of m and p of one or more second optical zones, wherein the m:p component is < about ±20%, between 1 to 20%, 1 to 5%, 5 to 10%, 10-15% or about 10 to 20%, and c) the location and width of one or more second optical zones on the ophthalmic lens, and d) the width of the central optical zone on the ophthalmic lens.

[0297] In some embodiments, an ophthalmic lens configured with features that are optically perpendicular to a surface may include at least one first optical zone having a first axis, the at least one first optical zone configured such that, when used with an eye, at least a portion of light passing through the at least one first optical zone is refracted to one or more focal points on the first axis; and at least one second optical zone configured such that, when used with 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. The one or more focal points 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 focal points continues or extends beyond the one or more focal points and provides an extended depth of focus together with light rays from the first optical zone.

[0298] In some embodiments, at least one first optical zone of an ophthalmic lens having features that are optically perpendicular to a surface may include a first portion having a substantially circular shape located at the center of the ophthalmic lens; and a second optical zone having a substantially annular shape and located between the first portion of the first optical zone and the second portion of the first optical zone. At least one first optical zone and at least one second optical zone may be concentric (e.g., substantially concentric, and / or partially concentric). In some embodiments, the ophthalmic lens may include alternating areas of the first optical zone and the second optical zone. In some embodiments, the second optical zone may include one or more areas that are combined and have variable focal power.

[0299] In some embodiments, at least one second optical zone of an ophthalmic lens having features that are optically perpendicular to a surface can be configured such that, when used with an eye, light passing through the at least one second optical zone is refracted to a plurality of (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, or 16) focal points that are not on the first axis. In some embodiments, the plurality of focal points caused by light passing through the at least one second optical zone can form a continuous ring of focal points (e.g., having a large and / or infinite number of focal points) around the first axis and spaced apart from the first axis. In certain embodiments, the plurality of focal points caused by light passing through the at least one second optical zone can form an incomplete ring of focal points.

[0300] In some embodiments, one or more characteristics of one or more second optical zones of an ophthalmic lens having features that are optically perpendicular to a surface can be configured such that light that passes through the one or more second optical zones and converges to form one or more focal points continues or extends beyond the one or more focal points and can provide an extended depth of focus together with light that passes through the first optical zone. In some embodiments, one or more characteristics of the second optical zone, such as the width, circumferential extent (e.g., arc or ring), curvature, number of zones, focal power, and focal length of one or more focal points associated with one or more segments of the zone, location on the ophthalmic lens, base power of the ophthalmic lens, and degree and / or manner of lateral spacing between the first and second optical zones, can affect the extended depth of focus provided by the ophthalmic lens.

[0301] In some embodiments, one or more second optical zones can be between about 0.05 mm and 3 mm. For example, in some embodiments, the optical zone width can 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 can be between about 0.05 to 2.0 mm, about 0.1 mm to 2.0 mm, about 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.

[0302] In some embodiments, the absolute power of the curvature of one or more second optical zones can be between about -10 and +10 D. For example, in some embodiments, the annular curvature can 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" can refer to a geometric curvature (or line) or a curvature (or line) that mathematically best fits a lens surface (power profile) area or cross-section.

[0303] In some embodiments, the lateral separation of the focal points from the first optical zone and the second optical zone can be between 0.2 and 2 mm. For example, the lateral separation of the focal points from one or more first optical zones and 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 points from the first optical zone and the second optical zone at the image plane can be less than about 50um, 60um, 70um, 80um, 90um, 0.1mm, 0.15mm, 0.2mm, 0.25mm, 0.3mm, 0.35mm, 0.4mm, 0.45mm, 0.5mm, 0.55mm, 0.6mm, 0.7mm, 0.75mm, 0.8mm, 0.85mm, 0.9mm, 0.95mm, and / or 1mm. In some embodiments, the lateral separation of the focal points from one or more first optical zones and one or more second optical zones at the image plane can be greater than about 50um, 60um, 70um, 80um, 90um, 0.1mm, 0.15mm, 0.2mm, 0.25mm, 0.3mm, 0.35mm, 0.4mm, 0.45mm, 0.5mm, 0.55mm, 0.6mm, 0.7mm, 0.75mm, 0.8mm, 0.85mm, 0.9mm, 0.95mm, and / or 1mm.

[0304] Fig.43A and 43B is a schematic diagram illustrating an exemplary embodiment of an ophthalmic lens incorporating a central optical zone 4301 surrounded by an annular zone 4302, wherein light rays passing through the annular zone 4302 result in one or more off-axis focal points that interact with on-axis rays from the central optical zone 4301. However, in Fig.43A and 43B In an embodiment, a line is used instead of Fig.41 In an embodiment, a curved second optical zone is configured to form an annular zone ( Fig.43A). As shown, the central zone power 4301 is more correct than the refractive error of the eye, so light traveling through the first optical zone can result in one or more focal points at planes other than the retina of the eye and a third optical zone 4303 whose power is used to provide an on-axis focus that coincides with the central zone focus. A second annular optical zone 4302 ( Fig.43B ) can be combined with a power profile 4202 having a component that is more positive ("p", 4302a) or more negative ("m", 4302b) relative to the first power 4301 and a progressive power profile component 4302c that increases from 4302d to 4302e in positive power. The "m" component arises from a discontinuity that is geometrically perpendicular to the surface between the innermost portions of the first optical zone and the second optical zone; the "p" component arises from a discontinuity that is geometrically perpendicular to the surface between the outermost portion of the second optical zone and the innermost portion of the third optical zone, thereby providing an on-axis focus that coincides with the central zone. The progressive power profile 4302c in the second annular optical zone connecting 4302d and 4302e is a linear power profile. This configuration on the back surface of the ophthalmic lens causes the innermost portion of the second optical zone to form a less positive power than the first central zone, so the power distribution appears more positive (p) at the innermost portion of the second optical zone and less positive (m) at the outermost portion of the second optical zone. Fig.42 The embodiments described in are consistent with because p=m, about <±20%, the second optical zone is optically perpendicular to the surface, and using a line to form the second optical zone results in a desired lateral spacing of the focal points between the first and second optical zones.

[0305] Fig.44A and 44B is a schematic diagram illustrating an ophthalmic lens according to certain embodiments that incorporates a central optical zone (first optical zone 4401) surrounded by an annular zone (second optical zone 4404) to create an off-axis focal plane 4404a and an extended depth of focus 4403. Specifically, Fig.44A and 44B The ophthalmic lens has a central optical zone 4401 that forms an on-axis (high intensity) focus 1A in front of a retinal image plane 4405 along an optical axis 4402; an annular zone 4404 that is relatively more positive than the central zone 4401 and forms a non-on-axis focus 5 at the image plane 4404a (in some embodiments, the non-axis point causes a defocus ring understood in 3D). Light rays passing through the inner 7, outer 8, and central portion 9 of the annular zone 4404 intersect the optical axis 4402 to form on-axis focuses 10, 11, and 12 in front of the retina (10), between the front and the retinal plane (11), and at the retinal plane (12), respectively.

[0306] In some embodiments, the optical intensities of the focal points 10, 11, and 12 may be lower than the optical intensities of the focal point 1A formed by the rays passing through the first optical zone 4401, while in other embodiments, they may be higher than the optical intensities of the focal points 10, 11, and 12. In some embodiments, the optical intensities of the focal points 10, 11, and 12 may be different from each other. In some embodiments, the focal points 10, 11, and 12 may be equally spaced from each other, while in other embodiments, they may not be spaced from each other. Fig.44B In an embodiment, the focal points 10, 11, and 12 are substantially dissimilar in light intensity. The focal point 1A from the central optical zone 4401 coincides with the focal point 11 formed by the centralmost ray 9 of the annular zone 4404. Light rays passing through the central zone 4401 also form higher intensity light zones 13 and 14 at image planes 10B (in front of the retina) and 12B (at the retina) of equal size and intensity. Light rays passing through the annular zone 4404 to form on-axis focal points 10, 11, and 12 and light intensity zones 10A, 11A, and 12A at image planes 10B, 11B, and 12B constructively interfere with light rays from the central zone 4401 to form on-axis focal points 1A and light intensity zones 13 and 14 at image planes 10B and 12B to form a depth of focus 4403 extending from image plane 10B to image plane 12B.

[0307] exist Fig.44A and 44B In some embodiments, rays passing through annular region 4404 create a relatively myopic (in front of the retina) off-axis focal plane 4404a that is in front of the focal point 1A created by the central optical zone, but in some other embodiments, the off-axis focal plane 4404a can be in front of, behind, or in substantially the same plane as the image plane for rays passing through central optical zone 11B. In addition, rays continue and extend beyond the off-axis focal plane to form a depth of focus behind and in front of the central focal point 1A. In some embodiments, the depth of focus 4403 can be completely in front of 1A or completely behind the central focal plane 11B. In some embodiments, a portion of the depth of focus 4403 can be in front of the central focal point at 11B and another portion can be behind the central focal point at 11B. In some embodiments, the ratio of depth of focus in front of versus behind the central focus can be approximately 100:0 (completely in front of the central focus), 90:10, 80:20, 75:25, 70:30, 60:40, 50:50 (equally 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).

[0308] Fig.44A and 44BThe examples shown in create a depth of focus that is continuous and in some embodiments improves the image quality in front of the retina compared to behind it, and thus can be used to control / slow / reduce the progression of myopia.

[0309] In some embodiments, the focal point created by the central or first optical zone can be located on (or substantially on) the retinal image plane, in front of the retinal image plane, and / or behind the retinal image plane.

[0310] In some embodiments, rays from the central optical zone 4401 can have a higher light intensity relative to rays from the annular optical zone. By positioning the higher intensity rays at the midpoint between the near (anteriormost) and far (posteriormost or retinal image) image planes (e.g., at the midpoint of the depth of focus), the effect of these rays on the spot characteristics can be substantially evenly 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 Fig.44B As shown, because the light rays from the annular region have lower light intensity, they can have reduced or lower disruptive effects on near, intermediate and / or distant planes, and thus do not affect or interfere with vision even when the light is distributed over a larger area. As shown, in this embodiment, the light rays created by the annular region 4404 interfere less with the light intensity zone at the plane most forward of the retina (near plane 10B) than with the light intensity zone formed at the rear (distant plane 12B), so the image on the near plane can be better than the image on the distant plane.

[0311] Fig.45 is a schematic diagram of an ophthalmic lens incorporating a central optical zone 4501 surrounded by an annular zone 4502, wherein light rays passing through the annular zone 4502 result in one or more off-axis focal points 4502a that interact with on-axis rays 4501a and result in depth of focus. Fig.45In the embodiment of the present invention, the posterior surface of the annular optical zone 4502 is relatively more negatively powered (steeper in curvature) than the posterior surface of the central zone 4501 and results 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 can be configured to be optically perpendicular to the surface (the annular zone 4502 power profile provides m=p<about ±20% resulting in a) some of the off-axis foci being laterally spaced from the on-axis focus and, b) light rays from the centralmost portion of the annular zone 4503a being substantially coincident with the central zone focus 4501a when they intersect the optical axis. Similarly, light rays from the innermost portion 4503b and the outermost portion 4503c 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 can be completely within the eye (i.e., in front of the retinal plane). However, because the steeper curvature of the rear surface of the lens causes the off-axis focal plane 4502b to be formed behind the retina, no off-axis focus (or defocus ring) is formed in front of the retinal image plane. This configuration may be desirable in some embodiments because the image quality at the retinal image plane can be improved. The lens of this embodiment can result in a low light intensity at the off-axis focus 4502a, and because the off-axis focus is positioned behind the on-axis image point 4502a, there is reduced light interference at A and therefore image quality can be improved. This is different from Fig.44A and 44B An example in which the interference of light rays in the light intensity region at the innermost image plane 10B is less than the interference formed at the retinal image plane 12B.

[0312] According to one embodiment, Fig.46 is a schematic diagram showing an ophthalmic lens incorporating a central optical zone 4601 surrounded by an annular zone 4602 to create an off-axis focal plane and depth of focus. As shown, light passing through the central zone 4601 forms an on-axis focus 4601a in front of the retinal image plane; the central zone 4601 is surrounded by an annular zone 4602 that includes a flatter posterior surface curvature (with a more positive focal power than the central optical zone 4601). In some embodiments, the use of the flatter posterior surface curvature of the annular zone 4602 can provide a focal power that is positive relative to the focal power of the central optical zone 4601, and can provide a focal power that is more positive than the focal power of the central optical zone 4601. Fig.44A and 44B Thus, the off-axis focal plane 4602b is positioned in front of the central focus 4601a, and the depth of focus 4610 can be positioned in front of and behind the central focus 4601a. ​​Thus, as described herein, the curvature of the annular region 4602 relative to the central region 4601 can affect the position of the off-axis focal plane relative to the central focus and the depth of focus. Fig.46Exemplary ophthalmic lenses include Fig.44A and 44B similar properties to an ophthalmic lens of the type described herein. For example, an ophthalmic lens includes a central optical zone 4601 whose on-axis focus 4601a is not formed on the retinal plane; an annular zone configured to be optically perpendicular to the surface (the annular zone power profile provides m=p<about ±20%), thereby resulting in a) lateral spacing of one or more off-axis focuses from one or more on-axis focuses and, b) light rays 4602a from the centralmost portion of the annular zone 4602 substantially coinciding with the central zone focus 4601a when they intersect the optical axis. Similarly, light rays from the innermost portion 4602d and the outermost portion 4602c of the annular zone 4602 form endpoints of the depth of focus at 4612 and 4611 when they intersect the optical axis equidistant from the central zone focus 4601a. ​​In this configuration, the depth of focus can be completely within the eye (i.e., in front of the retinal plane). In some embodiments, Fig.46 A configuration of an ophthalmic lens in which the posterior surface of the annular zone 4602 has a curvature 4603 that is flatter than the curvature of the central optical zone 4601 may be desirable because the droop difference between the optical zones may be reduced and the surface may not be recessed into the lens. Such a configuration may be less noticeable and therefore may be more cosmetically appealing and may increase compliance with lens wear. Additionally, in some embodiments, the flatter posterior 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 production.

[0313] According to one embodiment, Fig.47 is a schematic diagram showing an ophthalmic lens incorporating a central optical zone 4701 surrounded by an annular zone 4702 to create an off-axis focal plane and depth of focus. As shown, light passing through the central optical zone 4701 forms a focus 4701a at the retinal image plane, and the annular zone 4702 may include an inclined curvature such that the depth of focus 4710 is entirely within the eye. Thus, this embodiment may provide for off-axis focal planes and depth of focus. Fig.44A and 44BThe results of different implementations. For example, the central optical zone 4701 incorporates the ability to correct for distance refractive errors, so the central focus 4701a is substantially located at the retinal image plane 4712. The off-axis focal plane 4702b is positioned in front of the central focus 4701a, however, when the annular zone 4702 is not configured to be optically perpendicular to the surface (annular zone focal power distribution m=p>±20%), the depth of focus 4710 can also be positioned further in front of the central focus 4701a. Therefore, the lateral spacing of the off-axis focus 4702b from the on-axis focus 4701a can cause the light rays from the innermost portion 4702d of the annular zone 4702 to be approximately coincident with the central zone focus 4701a when they intersect the optical axis at the retinal image plane. The light rays at the retinal plane 4701a and the light rays from the outermost portion 4702c of the annular zone now form the endpoints of the depth of focus at 4712 and 4711. Light rays from the centermost portion 4702a of the annular region now intersect the optical axis equidistant from the end point of the depth of focus. In this configuration, the depth of focus for the illustrated embodiment can be completely within the eye (i.e., in front of the retinal plane), however, unlike Fig.44A and 44B different, Fig.47 The central region focus 4701a in the annular region is now at the retinal plane and does not coincide with the centralmost rays of the annular region 4702 as they intersect the optical axis. The change in the power distribution in the annular region has changed the m:p ratio so that p>m and the depth of focus can be shifted more forward in front of the retina to avoid any focus behind the retina. However, in some embodiments, this can result in increased interference of high intensity light rays at the near image plane 4711, which can reduce the near image plane image quality and can also adversely affect the image quality at the far image plane 4712 (e.g., as with Fig.44A and 44B , compared to the example described in ).

[0314] According to one embodiment, Fig.484800 is a schematic diagram showing an ophthalmic lens 4800 having a central optical zone 4801 and an annular zone 4802 to create one or more off-axis focal planes and depth of focus. The annular zone 4802 contains three joint curvatures 4802a, 4802b, and 4802c (as opposed to a single curvature) of substantially similar curvature. For the joint curve, the innermost and outermost portions of the curve transition to the base curve (the curvature of the first optical zone). For simplicity, a description of light rays passing through the first two joint curvatures 4802a and 4802b is provided. Light rays passing through the central zone 4801 form an on-axis focus 4801a at 4813a and are located in front of the retinal image plane 4812a. Light rays passing through the joint curvatures 4802a and 4802b of the annular zone 4802 can create off-axis focal planes 4805a and 4805b and depths of focus 4806a and 4806b, respectively. The combined curvature of the annular zone 4802 is on the anterior surface and can have a steeper curvature than the curvature of the central optical zone 4801 (resulting in a relatively positive focal power of the zone 4802 than the focal power of the central optical zone). Fig.44A and 44BEach joint curvature may perform similarly compared to a single curvature in the annular optical zone of the embodiment of the present invention. The off-axis focal planes 4805a and 4805b may be positioned in front of the central focus 4801a, and the depth of focus 4806a and 4806b for each joint curvature may be positioned on either side of the central focus 4801a (i.e., both in front and behind). In some embodiments, the joint curvature may be on the front surface or the back surface or both. In addition, as described herein, the curvature of the annular zone 4802 relative to the central optical zone 4801 may affect the position of the off-axis focal plane relative to the central focus and the depth of focus. As configured, light rays passing through the central optical zone 4801 form an on-axis focus 4801a in front of the retinal plane; the annular zone 4802 is configured with joint curvatures 4802a and 4802b that are optically perpendicular to the surface (the focal power distribution in each joint curve provides m=p, approximately <±20%) and light passing through the annular zone 4802 results in off-axis foci 4805a and 4805b; the lateral spacing of the off-axis foci 4805a and 4805b from the on-axis focus 4801a can cause light rays from the centralmost portions 4807a and 4807b of each joint curve in the annular zone to approximately coincide with the central zone focus 4801a when they intersect the optical axis. Similarly, light rays passing through the innermost portions 4808a and 4808b and the outermost portions 4809a and 4809b of the annular region form endpoints of the depth of focus at 4812a and 4811a when they intersect the optical axis equidistant from the central region focus 4801a. In this configuration, the depth of focus 4806a and 4806b for the illustrated embodiment may be completely within the eye (i.e., in front of the retinal plane). A magnified view of the light rays intersecting the three image planes forming the depth of focus is shown in FIG. Fig.484802a and 4802b. The central region focus 4801a is located at the intermediate image plane 4813a and is approximately coincident with the light rays 4809a and 4809b formed by the centralmost portions of the combined curvatures 4802a and 4802b. The near image plane 4811a and the far image plane 4812a from the first combined curvature 4802a, and therefore the depth of focus 4806a, can be slightly longer than the depth of focus 4806b formed by the second combined curvature 4802b between the image planes 4813b and 4812b. However, the light interference of light rays originating from the central region 4801 and the first combined curvature (approximately 5 mm aperture) at the image planes 4811 (a and b), 4812 (a and b), and 4813a can be similar to the light interference of light rays originating from the central region and the two combined curvatures (approximately 7 mm aperture) at the same three image planes. In some embodiments, a slight difference in the depth of focus formed by the combined curvatures 4802a and 4802b may be caused by the more peripheral location of the second combined curvature relative to the center of the lens. In some embodiments, the off-axis optical power of the combined curvatures can decrease as each curvature is located farther from the central area. This illustration shows that as the annular area increases in width, the combined curvature can continue to provide good image quality and depth of focus. A desirable feature of combining multiple annular curvatures is that a larger area of ​​the annular optical zone surrounding the central optical zone can be used to extend the depth of focus. In some embodiments, Fig.44A and 44B The ophthalmic lens of can provide the best image quality for a pupil size of 5 mm 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, for larger pupil sizes (i.e., about 6 mm or larger), light rays can pass through Fig.44A and 44B A third optical zone of an ophthalmic lens (comprising an optical power similar to that of the central optical zone) is provided to contribute additional high-intensity focal points and may increase interference with image quality at important image planes. In addition, in some embodiments, Fig.44A and 44B The lens described in the foregoing may also have a second annular region that surrounds the first annular ring to form an on-axis focus that coincides with the focus formed by the central region. For larger pupil sizes, on-axis light rays that form an on-axis focus from the second annular ring may fall into the pupil and increase the light intensity zone formed at the image plane (e.g., the retinal image plane). Thus, in some embodiments, a ratio of Fig.44A and 44BA wider annular zone provided in may be advantageous. However, increasing the width of the annular zone (e.g., 0.50 mm or more to 1.50 mm or wider) using a single curvature may result in increased light interference at various image planes and reduced image quality because the condition of being optically normal to the surface (where the annular zone focal power distribution provides m=p<about ±20%) may not be maintained over the wider annular optical zone. Therefore, in order to maintain good image quality over a larger annular optical zone, multiple combined annular zones with individual widths that substantially maintain the condition of being optically normal to the surface (i.e., m=p, <about ±20%) result in improved image quality and depth of focus. Therefore, Fig.48 Exemplary embodiments of the invention may provide improved depth of focus and improved and consistent image quality, particularly in eyes with larger pupils or eyes whose pupil size varies significantly (e.g., with changes in illumination).

[0315] In some embodiments, Fig.48 Multiple combined curvatures of an ophthalmic lens can increase the depth of focus beyond the annular optical zone containing a single curvature. For example, the depth of focus produced by the combined curvatures 4802a, 4802b, and 4802c can be further extended by using a higher diopter (e.g., +4.00D) in each curvature. Thus, in some embodiments, Fig.48 The joint zone design can be applicable to myopia treatment by expanding the area and light intensity on the image plane located in front of the retinal image plane. Similarly, in some embodiments, an annular zone containing multiple joint curvatures can be applicable to presbyopia correction. For presbyopes, the depth of focus required to achieve vision from far to near may depend on their degree of presbyopia. Early presbyopes may need a smaller depth of focus because their remaining eye accommodation can support focusing at an intermediate distance of up to 50 or 60 cm, while late presbyopes with minimal residual eye accommodation may need a longer depth of focus. Therefore, in some embodiments, an annular optical zone containing only two joint curvatures may be sufficient for early or mid-stage presbyopes, while higher add presbyopes may require three or more joint curvatures. In addition, late presbyopes may need a longer depth of focus from up to 30-40 cm from hyperopia. In addition to multiple joint curvatures, the increase in diopter in each curvature can increase the depth beyond a single annular optical zone. Therefore, the amount of focus in each joint curvature and the added area for the depth of focus can be manipulated to extend the depth of focus accordingly while still providing optimal image quality at intermediate and close distances.

[0316] In some embodiments, the annular region can include 2, 3, 4, 5, 6, 7, 8, 9 and / or 10 combined curvatures. In some embodiments, a plurality of single curvatures placed adjacent to each other can be used to create a combined curvature. In some embodiments, this design can create multiple myopia treatment planes (e.g., multiple off-axis focal planes). In some embodiments, one or more of the myopia treatment planes may not be positioned off-axis. In some embodiments, multiple myopia treatment planes can be utilized to increase more depth of focus for presbyopia and / or additional myopia treatment.

[0317] According to one embodiment, Fig.49A and 49B 4900 is a schematic diagram of an ophthalmic lens 4900 having a central optical zone 4901 and an annular zone 4902 to create one or more off-axis focal planes and depth of focus. The annular zone 4902 contains multiple injected curvatures 4902a, 4902b, 4902c, and 4902d (as opposed to a single curvature), each of which has the same curvature except for 4902d which is wider and has a steeper curvature. An injected curvature refers to a partial or incomplete ring having an innermost portion and / or outermost portion that may not meet the curvature of the substrate surface (central optical zone), and is different from, for example, a joint curvature where the ring is complete and the inner and outermost portions of the ring generally meet the substrate curvature (and may be symmetrical). In some embodiments, an annular region comprising multiple injection curves may have a first injection where the innermost portion of the first (innermost) injection curve meets the substrate surface curvature, and the outermost portion of the last (outermost) injection curve of the annular region meets the substrate surface (or the surface of the next optical zone), but the injection curves in between may not have portions that meet the substrate surface curvature. In some embodiments, the first curve injection may not be geometrically or optically perpendicular to the surface because the innermost portion may be on the substrate surface, however, the outermost portion may not be geometrically or optically perpendicular to the surface as it transitions to the next injection curve.

[0318] For simplicity and ease of illustration, light rays from the first, second, and last curvature injections 4902a, 4902b, and 4902d will be described. The central region 4901 forms an on-axis focus 4901a in front of the retinal image plane 4912b. According to certain embodiments, the curvature injections 4902a, 4902b, and 4902d can create off-axis focal planes 4905a, 4905b, and 4905d and focal depths 4906a, 4906b, and 4906d. In this example, the curvature injection in the annular region 4902 is on the anterior surface and can have a steeper curvature than the curvature of the central optical zone 4901 (e.g., a more positive focal power than the central optical zone focal power). The curvature injection shapes and sagittal depths can be shown enlarged in 49-1 and are similar except for 4902c mentioned above. The degree of injection between each curvature is determined by the amount of overlap between the curvatures (e.g., distances 4914, 4915, and 4916). The degree of injection in the annular region 4902 is similar between the first and second injections 4902a and 4902b (4914) and between the third and final injection 4916 and between the second and third injections (4915). In some embodiments, the degree of overlap controls the diameter of each injection, the symmetry, and the contribution of the light rays to provide depth of focus and interference to the image plane formed by the ophthalmic lens 4900.

[0319] In some embodiments (e.g. Fig.49A ), the off-axis focal plane formed by the curvature injections 4902a, 4902b, and 4902d can be positioned in front of the central focus 4901a, and the depth of focus 4906a, 4906b, and 4906d of each curvature injection can be positioned both in front of and behind the central focus 4901a. In some embodiments, the annular region 4902 can be located on the back surface of the ophthalmic lens and can have multiple curvature injections and still create similar or substantially similar results. In addition, as described herein, the curvature of the annular region relative to the central region can affect the position and depth of focus of the off-axis focal plane relative to the central focus. In some embodiments, the spherical geometry discussed herein can be used to obtain the features described herein, and in some embodiments, other techniques can be used.

[0320] As configured, Fig.49A The exemplary ophthalmic lens in includes a central optical zone 4901 having an on-axis focus 4901a that is not formed on the retinal plane (e.g., in front of the retinal plane); an annular zone configured with injected curvatures 4902a, 4902b, and 4902d, wherein only 4902b (and 4902c) are optically perpendicular to the surface (wherein the power distribution in each curvature provides m=p, < about ±20%). Thus, in some embodiments (e.g. Fig.49A), the first injection curvature 4902a can have a focal power profile where m:p>20% (i.e., not optically perpendicular to the surface), and similarly, the last injection 4902d can have a similar and opposite focal power profile where m:p>20% and not optically perpendicular to the surface, as shown in Fig.49B Depicted.

[0321] like Fig.49A As shown, the lateral spacing of the off-axis focal points 4905a, 4905b and 4905d from the on-axis focal point 4901a can cause only the light rays from the most central portion 4907b of the second curvature injection (4902b) to approximately coincide with the central area focus 4901a when they intersect the optical axis and the depth of focus formed is 4906b. Since the injection curves 4902a and 4902d are not configured to be optically perpendicular to the surface, the light rays passing through the most central portion of the injection curves do not intersect the optical axis at 4901a but at 4917a and 4917d. The depth of focus formed by the injection curvatures 4902a and 4902d is 4906a and 4906d. In this configuration, the depth of focus of each injection curvature of the ophthalmic lens 4900 can be completely within the eye (i.e., in front of the retinal plane). A magnified view of the light rays that intersect the image plane to form the depth of focus is shown in FIG. Fig.49A 49-1. Each injection curvature can create a different depth of focus. For example, the depth of focus 4906b of the second injection curve configured perpendicular to the surface is shorter than the depth of focus 4906a formed by the first injection curvature and the depth of focus 4906d formed by the second injection curvature. In addition, these depths of focus 4906a and 4906d are not equidistant around the on-axis focus of the central area 4901a. The depth of focus 4906a is longer and shifted further forward, while 4906d is shifted further back but shorter than 4906a because the injection curvature is located farther from the center of the lens. All depths of focus formed by the injection curvatures extend less than the depth of focus 4906e formed by the annular area containing a single curvature.

[0322] The width of the injection curve can be narrower than that of multiple combined curves or annular zones comprising a single curvature, thus providing a shorter depth of focus for each injection curve. However, in an ophthalmic lens formed from multiple narrower injection curves in an appropriately configured configuration, the overall depth of focus can be maintained or can exceed the depth of focus obtained with a single annular zone or several multiple combined zones. Thus, an ophthalmic lens incorporating multiple injection curves in an annular zone can be used with Fig.48In some embodiments, the lateral spacing of the off-axis focus from the on-axis focus obtained with an ophthalmic lens having multiple injection curves can be the same or can be different. In some embodiments, the injection curvatures can be created with substantially the same or substantially different curvatures or can include "lines" placed adjacently or interspersed between curvatures. In some embodiments, all injection curvatures can be formed as Fig.49B The optical power distribution shown, wherein the injection curvatures, except for the first and last injection curvatures, can satisfy the condition of being optically perpendicular to the surface, where m=p<about ±20%. In some embodiments, the injection curvature can be adjusted to provide a power distribution with a range of m and p ratio conditions. Therefore, due to its narrow size, the injection curvature can provide the lens designer with greater flexibility in obtaining the desired image quality and depth of focus. For example, using multiple injection curves, the annular area may not be geometrically perpendicular to the surface, but can provide such a power distribution, where m=p<about 20%, thereby satisfying the condition of being optically perpendicular to the surface, and can therefore be configured to provide the best depth of focus and image quality at the respective image planes with the minimum amount of interference between light rays. The ophthalmic lens can provide more beneficial vision with, for example, an extended depth of focus sufficient for late presbyopes, or a more consistent image quality for presbyopes with larger pupils and those who may experience wider fluctuations in their pupil size under different lighting conditions. In some embodiments, forming the annular region using multiple implant curvatures can enable a continuous surface to be formed with the central region and at the same time can provide a continuous power profile with substantially no discontinuities.

[0323] In some embodiments, the annular region can contain 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 curved injections. In some embodiments, multiple curved injections can reduce the depth of focus provided by the annular region, but can provide a more pupil-independent design. Multiple curved injections can also allow the overall width of the annular region to be increased without affecting the depth of field. In some embodiments, multiple curved injections can also create a design that is optically significant and non-perpendicular to the surface. In some embodiments, multiple curved injections can have similar or identical optical properties. For example, Fig.49B As shown, multiple curved injections can also have different optical properties. For example, based on the normalized base lens aberration distribution, the curved injections can have different m and / or p focal values. Fig.49B, the power distribution of the first (closest to the center) injection curve can have m negative power (ma) that is significantly greater than the pa positive power. Similarly, the power distribution of the last (farthest from the center) injection curve D can have m negative power (md) that is significantly less than the pd positive power, while the power distributions of the middle two (second and third) injection curves B and C can have m negative power (mb and mc) that are approximately equal to the pb and pc positive power values, respectively. Therefore, the power distribution of injection curves B and C is optically perpendicular to the surface. In addition, the positive and negative power distributions of the first injection curve A can be longer than the power distributions of the second, third, etc. injection curves (e.g., curves B, C, and D). This can be created by the asymmetry of the curve injection. The curve injection is asymmetric when the innermost portion of the curve injection is at a different sagittal height than the outermost portion. As previously described, Fig.49A The first and last curve injections are asymmetric and provide a focal power of m=p>±20%.

[0324] According to one embodiment, Fig.50 is a schematic diagram showing an ophthalmic lens 5000 having a central optical zone 5001 and an annular second optical zone 5002 to create an off-axis focal plane and depth of focus. In some embodiments, the annular second optical zone 5002 can be created by utilizing a surface having zero curvature or substantially zero curvature (referred to herein as a line curvature) and forming an annular zone 5002 that is more positive than the central optical zone 5001. In some embodiments, this line can be combined with the curvature of the front surface to cause the ophthalmic lens to act as a plano-convex lens and create 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 can create a relatively similar amount of depth of focus, but using a much smaller annular width (e.g., about 1 / 5, 1 / 10, or 1 / 15 for contact lens designs). In some embodiments, this design can also be used in conjunction with the injection and / or joint curvatures described herein. While this line may be applicable to all ophthalmic lenses, when used for contact lenses, the line curvature may be very narrow, such as 50um wide, and may produce very high off-axis power, such as >50D or about 100D, so the light rays emitted from such an off-axis focus of this power may be highly divergent and reduce contrast despite the extended depth of focus. Applied to eyeglass lenses, a line of about 1mm may provide an off-axis power of about 5.0D while also maintaining depth of focus.

[0325] In some embodiments, the ophthalmic lens 5000 can provide a 3D image with a 3D image by using a line (aspherical torus) on the back surface of the lens. Fig.44A and 44BIn other words, several forms of aspherical tori that rotate around the surface of an ophthalmic lens can increase the positive power in the annular optical zone relative to the central optical zone power required to create an off-axis focal plane and depth of focus according to certain embodiments. In some embodiments, an aspherical tori, such as a line or conical surface, or multiple joint or injected curves or lines, or lines and curves dispersed in an annular region can be utilized to obtain the features described herein, and in some embodiments other techniques can be utilized. Thus, the off-axis focal plane 5001b is positioned in front of the central focus 5001a, and the depth of focus 5006 can be positioned both in front of and behind the central focus 5001a. In addition, as described herein, the curvature of the annular region relative to the central region can affect the position of the off-axis focal plane relative to the central focus and the depth of focus.

[0326] Fig.50 The exemplary ophthalmic lens in includes features similar to those of FIGS. 44(A and 44B . For example, the ophthalmic lens includes a central optical zone 5001 having an on-axis focus 5001a formed not in the retinal plane (e.g., in front of the retinal plane); an annular zone 5002 configured by lines optically perpendicular to the posterior surface (wherein the annular zone focal power profile provides m=p, < about ±20%) such that the lateral spacing of the off-axis focus from the on-axis focus can cause light rays 5002a from the centralmost portion of the annular zone to substantially coincide with the central zone focus 5001a when they intersect the optical axis. Similarly, light rays from the innermost portion 5002b and the outermost portion 5002c of the annular zone form endpoints of the depth of focus 5006 when they intersect the optical axis equidistant from the central zone focus 5001a. In this configuration, the depth of focus for the illustrated embodiment can be entirely within the eye (i.e., in front of the retinal plane).

[0327] According to one embodiment, Fig.51A is a schematic diagram showing an ophthalmic lens incorporating a central optical zone surrounded by an annular zone to create off-axis focal planes and depth of focus according to certain embodiments. As shown in this example, two surfaces of the annular optical zone of the lens can be formed using surfaces with zero curvature or substantially zero curvature (referred to herein as line curvature). In some embodiments, this configuration can create a depth of focus with a minimum light intensity zone from low-intensity annular zone rays and therefore produce better image quality. In some embodiments, this design can also reduce or eliminate the presence of off-axis focal planes along the optical axis.

[0328] Fig.51Ais a schematic diagram showing an ophthalmic lens including a central optical zone 5101 resulting in an on-axis focus 5101a in front of the retinal plane; an annular zone 5102 surrounding the central optical zone, the curvature of the annular optical zone 5102 being formed on the front surface by line 5102a (e.g., a flat line or a line flatter than the central zone) and on the back surface by line 5102b (e.g., a flat line or a line steeper than the central zone), wherein light rays passing through the annular zone 5102 may have no off-axis optical power, thereby causing light rays 5104a, 5104b, and 5104c passing through the annular zone 5102 to travel in parallel straight paths to image planes 5111, 5113, and 5112. The off-axis light rays intersect the optical axis and interact with the on-axis rays from the central optical zone and result in a depth of focus 5106. The lens of this embodiment may not form off-axis focal points, nor may there be converging or diverging light rays beyond the off-axis focal points that may increase light interference at the image plane along the depth of focus 5106.

[0329] The annular region 5102 is configured such that it is possible to form no lines of off-axis power, so that the annular region is optically perpendicular to the surface (where the annular region on the on-axis power distribution provides m=p<about ±20%) and light rays 5104b from the centralmost portion of the annular region approximately coincide with the central region focus 5101a when they intersect the optical axis. Similarly, light rays from the innermost portion 5104c and the outermost portion 5104a of the annular region form endpoints of the depth of focus at 5107 and 5108 when they intersect the optical axis equidistant from the central region focus 5101a. In this configuration, the depth of focus 5106 for the illustrated embodiment can be located entirely within the eye (i.e., in front of 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 image quality can be improved at the image plane along the depth of focus 5106 because interference with light rays along the depth of focus may be less than in many embodiments, such as Fig.44A and 44B ophthalmic lenses.

[0330] Fig.51B An exemplary power profile of a lens is illustrated that includes a central zone and three zones within an annular region formed by lines on the front and back surfaces. Fig.51BThe ophthalmic lens simulated in FIG. 1 incorporates a central optical zone 5121 having a 2.0 mm diameter having an on-axis focus that is not formed on the retinal plane (e.g., in front of the retinal plane); surrounded by an annular zone 5122 formed by 3 joint lines 5123a, 5123b, and 5123c on the anterior surface and 5124a, 5124b, and 5124c configured on the posterior surface to form a 3 mm wide annular optical zone containing 3 x 1 mm wide concentric annular optical zones of zero off-axis power. Fig.51A As described in , light rays passing through the annular region having no off-axis optical power simply pass through to intersect the optical axis and interact with on-axis rays from the central optical region 5121 and result in a depth of focus 5206 with reduced optical interference at the image plane along the depth of focus. Fig.51B Shown in Fig.51B Simulation of the sagittal power distribution over a 6 mm aperture of the lens described in . The 6 mm aperture can capture light rays from the center and 2 of the 3 annular line regions. The power distribution shows the on-axis power of the central region 5122 and the on-axis power distribution of the two annular concentric regions (5123a innermost and 5123b middle) formed by the lines on the front and back surfaces. As shown, the exemplary design provides a depth of focus 5129 of approximately 1.5D. In these two annular regions, p = m, < approximately ±20%, and is consistent with the configuration that is optically perpendicular to the surface in each region.

[0331] One desirable feature of forming an annular zone with lines on both surfaces of the lens is that it creates an annular zone with no off-axis power, so wearability can be very easy. The width of the zone can be similar to the annular zone created with a single curve or multiple combined or injected curves, and can be wider. 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. Since light rays emanating from the off-axis ring defocus are absent, interference of light rays at the image plane is correspondingly reduced.

[0332] Fig.52 is a comparison calculated by focusing retinal image quality (RIQ) between: a) a commercially available lens comprising a distance central zone surrounding alternating annular zones of coaxial lens having more correct and distance powers and referred to herein as a 'coaxial lens design (CLD)'; and b) Fig.44A and 44B and Fig.51B The key parameters of these three lens designs are Fig.52 Described in detail. Fig.44A and 44BThe contact lens (FIG44CL) has a 3 mm central optical zone having an optical power that is hyperopic (positive) relative to the distance refractive error of the eye, and a 1 mm wide annular zone having a +3.5D added power. Fig.51B Contact lenses ( Fig.51B The CLD has a 2mm diameter central optical zone with an optical power that is hyperopic (positive) relative to the distance refractive error of the eye and is surrounded by 2 x 1mm joint annular zones with 'plano' off-axis power configured with 'lines' on both the anterior and posterior surfaces. The CLD has a 3.0mm central optical zone with a power for the distance refractive error of the eye and is surrounded by 3 annular optical zones of 1mm diameter with a power of +2.00D relative to the central optical zone and alternating with the central zone power. All optical zones of the CLD are coaxial with the optical axis. RIQ is calculated for through focus ranging from -1.75D (behind the retina) to +2.25D (in front of the retina) at a pupil size of 5mm ( Fig.52 ). As shown in the figure, the RIQ of CLD is bimodal around two on-axis zone powers, namely the distance power centered on the retinal plane (RIQ=0.34) and +2.00D of additional power in front of the retinal image plane (RIQ=0.38). The RIQ between the two peaks is significantly lower. In contrast, Fig.44A and 44B and Fig.51B The lenses have peak RIQs of 0.46 and 0.44, which are better than the RIQ of the CLD over a wide range of vergence and indicate a true extended depth of focus with good RIQ.

[0333] In some embodiments, an ophthalmic lens may have a central zone power equal to the distance refractive error of the eye plus about 1.00D for both myopia and presbyopia. In other embodiments, the central zone power is equal to the distance refractive error of the eye plus about 0.75D, 0.50D, or 0.25D, which may be about 1.00D-0.50D, 0.75D to 0.25, 0.50D to 0.25D. In some embodiments, more than one refractive zone of an ophthalmic lens helps restore visual acuity of the eye. In some embodiments, more than one refractive zone of an ophthalmic lens may include a central zone plus one of the following: alternating angular rings (zones), combined annular rings, injected rings, annular zones with flat lines, etc.

[0334] In some embodiments, the tilt of the annular zone relative to the central optical zone can be configured to provide desired functionality with respect to 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 perpendicular to the surface.

[0335] In some embodiments, the depth of focus provided by the ophthalmic lens can range from about 0.25D to 5.0D. For example, the depth of focus can 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 can be about 1D or more, or 1.5D or more and / or 2D or more. As discussed above, the depth of focus can be balanced or unbalanced relative to the on-axis focus. In some embodiments, the depth of focus can be considered balanced (i.e., the on-axis focus is at the approximate midpoint of the depth of focus range) when present on either side of the on-axis focus, where the depth of focus is the distance between the more positive plane closest to the anterior eye and the less positive focus farthest from the anterior eye. In some embodiments, the size and position of the depth of focus can be controlled by the ring and / or annular zone width, the annular zone / ring focal power, and the central visual zone size of a given annular zone. Some embodiments may have a constant depth of focus within the focal power range of the central zone of the lens set, while the depth of focus range of other embodiments may depend on the focal power of the central optical zone. In some embodiments, a set of lenses may be provided that has a certain depth of focus range to manage patients (e.g., myopia control with short depth of focus, average depth of focus, and long depth of focus to slow / control / reduce the axial progression of the eye). Some embodiments may have a lens set that has a certain depth of focus range, thereby providing one or more depths of focus to manage patients (e.g., presbyopia may have a short depth of focus, an average depth of focus, and a long depth of focus for additional correction). In some embodiments (e.g., presbyopia correction), the prescribed depth of focus may not be similar for the two eyes of an individual. For example, in some embodiments, the depth of focus in one eye may be 1.0D and the depth of focus in the contralateral eye may be 2.0D, or may be equal but offset from each other. For example, the depth of focus in both eyes can be 2D, but the depth of focus in the non-dominant eye can be positioned further in front of the retina than in the dominant eye, thereby providing a range of additional depth of focus and thus a range of clear vision from intermediate to near distances to manage presbyopia. In some embodiments, the offset can 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.

[0336] In some embodiments, the off-axis focus may result in an annular focus, while in some other embodiments, it may result in an incomplete annulus. For example, the incomplete focal annulus may have only a limited number of focal points (one focal point every 0.5 degrees, i.e., 720 focal points; or one focal point every 1.0 degrees, i.e., 360 focal points; or one focal point every 2 degrees, i.e., 180 focal points), may have a result caused by the structure of the annular optical zone [the treatment area is not a complete annulus, (e.g., an arc of 10 degrees or 15 degrees includes all focal points and / or an arc of 10 degrees or 15 degrees has no focal points)]; and / or one (or more) relevant areas on the ophthalmic lens are configured in a spiral, polygonal, or any predefined direction, thereby forming a continuous off-axis focus shape, which is a spiral, linear shape when viewed from a top view of the lens.

[0337] As described herein, the desired surface profile of the annular region can be provided on the front surface (e.g., a positive raised surface profile) and / or the back surface (e.g., a negative recessed surface height), or both. In some embodiments, the surface profile of the annular region may or may not be a spherical torus. In some embodiments, the surface profile of the annular region may be injected. In some embodiments, the annular region may have a coaxial spherical curvature as part of the annular region incorporating an injected ring. In some embodiments, the surface profile of the annular region may be a conical surface. In some embodiments, the torus may be on the back surface and equal and opposite to the front surface (e.g., a tilt may be within the lens and if applied on the back surface, move the focus in a direction opposite to the case where a precise tilt is applied to the same curve on the front surface).

[0338] In some embodiments, the ophthalmic lenses described herein may provide improved vision as determined by any combination of an overall vision score, a retinal image quality (RIQ) value, and / or a through-focus image quality (TFIQ) vision score.

[0339] In some embodiments, the ophthalmic lens may include a joint ring around the central area. In some embodiments, the ophthalmic lens may include an injected ring around the central area. In some embodiments, the ophthalmic lens may include a central area 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 area is about 3 mm or less or greater than about 0.5 mm.

[0340] In some embodiments, an ophthalmic lens may include a central optical zone and an annular optical zone including a plurality of rings, wherein the width of each ring of the annular optical zone may range from 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 annulus width can be less than about 0.05mm, 0.1mm, 0.15mm, 0.2mm, 0.25mm, 0.3mm, 0.35mm, 0.4mm, 0.45mm, 0.5mm, 0.55mm, 0.6mm, 0.65mm, 0.7mm, 0.75mm, 0.8mm, 0.85mm, 0.9mm, 0.95mm, 1mm, 1.1mm, 1.2mm, 1.3mm, 1.4mm, 1.5mm, 1.6mm, 1.7mm, 1.8mm, 1.9mm, and / or 2mm. In some embodiments, the width can vary within the annulus, or the width can vary on each individual annulus. In some embodiments, the width of each of the annulus is less than 2mm and / or less than 1.5mm. In some embodiments, the annular region can have a tilt of about zero. In some embodiments, for an annulus with a relative power of +2.0D, the retinal image quality (RIQ) can be above 0.4.

[0341] The lens design group of Lens 1 and Lens 2 in Table 1 are designed with annular zones configured perpendicular to the surface. Both Lenses 1 and 2 have a central optical zone and an annular optical zone, where the annular optical zone is relatively positive in power (referred to as ADD) than the central zone. The central optical zone of Lens 1 incorporates power to correct the distance refractive error of the eye, while the central optical zone of Lens 2 has no power to correct the distance refractive error of the eye. Lens 1 is configured so that the annular zone power provides a constant relatively positive power regardless of the central zone power, e.g., the ADD power is constant and does not change as the central zone power changes. In contrast, the annular zone of Lens 2 can be configured to provide different amounts of relatively positive power or ADD power within the power range of the central optical zone. Lens 2 can be configured with different add values ​​for each central zone power while maintaining two important criteria: the annular optical zones are designed with a geometry perpendicular to the surface to achieve the desired amount of lateral separation, and the add refractive correction for the eye is not based on the central optical zone whose power is used to correct the eye's distance refractive error.

[0342]

[0343]

[0344] Table 1. Exemplary designs of peripheral zone focal power dependent (Example 1) and independent (Example 2) on the central zone focal power.

[0345] As described herein, the image quality at an image plane can be directly related to the properties of a light spot formed at one or more image planes by light rays from an optical zone located on an ophthalmic lens. Therefore, the optical quality of an ophthalmic lens can result from the interaction between the image qualities of light spots formed at an infinite number of image planes formed between the lens and the final image plane. The cross-section of a light spot has a dimension measured in microns called the spot size. A light spot will also have a light intensity distribution in the form of a series of peaks with higher and lower intensities over a range of diameters. The Strehl ratio is a measure of the light intensity distribution at a light spot and is determined by the ratio of the peak light intensity of a point image at a specified diameter divided by the peak light intensity of an image formed by a diffraction limited lens. Perfect image quality will have a ratio of 1, while poor image quality will be close to 0. A light spot at an image plane can consist of all light rays from on-axis and off-axis optical elements located within the lens aperture that pass through the image plane to form an image at the image plane. Therefore, a light spot can include light rays focused at the image plane and any light rays converging toward a focal point behind the image plane and any light rays diverging from a focal point formed in front of the image plane of interest. Therefore, the size and light intensity distribution of the light spot at the image plane, and therefore the image quality, reflects the interference between any lower intensity light rays emanating from the off-axis optical zone and any higher intensity light rays formed at the image plane by the on-axis optical zone. The relative importance of the light spot characteristics can vary, depending on the optical design and application. Light intensity distribution can be an important characteristic in the context of improved ophthalmic lenses for myopia control and presbyopia, and other applications that benefit from extended depth of focus.

[0346] Therefore, the light intensity distribution of the light spot formed at the image plane is crucial to the image quality and should be specified.

[0347] In some embodiments, to optimize the ophthalmic lens image quality, optical simulations have shown light distributions of points formed at several image planes, and their positions can be specified. The first image plane can be located at the retinal image plane and the second image plane can be located further in front of the retinal image plane and together can form a boundary of at least 0.50D or greater depth of focus, while the third image plane can be located at the midpoint of the distance between the other two image planes.

[0348] Unexpectedly, it was found that the best image quality occurs when the high intensity rays from the central region are focused at the third image plane rather than at the retinal image plane. In this regard, in some embodiments, it is desirable that the high intensity light rays from the central region form defocused spot sizes without strong peaks at the first and second image planes and result in lower Strehl ratios at these two planes compared to the third image plane. Since the third image plane is at the midpoint of the distance between the first and second image planes, the light distribution of the high intensity spot size formed on the first image plane (from the light rays converging to the third image plane) and the light distribution of the high intensity spot size formed on the second image plane (from the light rays diverging from the third image plane) are approximately equal and have approximately similar Strehl ratios.

[0349] Clinical observations of eyes wearing prototype contact lenses having varying central optical zone sizes and powers, annular optical zone widths and powers, and m:p ratios have determined that for a 5 mm lens aperture, the optimal light distribution intensity formed in the light spots at the first and second image planes, as measured by the Strehl ratio, is less than 0.15 (e.g., <0.10 or 0.07 or less). Likewise, the optimal Strehl ratio at the third image plane is higher than at the first and second image planes and is, for example, <0.15, <0.10, and / or 0.07 or less. Based on the above, the optimal Strehl ratio at the third image plane is less than 0.15, <0.10, and / or 0.07 or less. Fig.44A – Fig.51B In the optical simulations discussed in several examples in , the m=p ratio of the power profile formed in the annular ring has been shown to be a control parameter that has an impact on optical quality, i.e., m is approximately equal to p. In the case where the third image plane is located at a midpoint distance between the first and second image planes, m is also equal to p, and clinical observations have determined that optimal image quality occurs when the m:p ratio is between approximately <20%.

[0350] In some embodiments, the ophthalmic lenses described herein can be implemented in a variety of ways for a range of purposes, including: contact lenses and / or eyeglass lenses to correct and / or reduce myopia; contact lenses, contact lenses for presbyopia (high, medium, and low); lenses for anti-fatigue; as single vision lenses; contact lenses for astigmatism; toric multifocal contact lenses; intraocular lenses; implantable contact lenses; corneal inlays, and keratomorphic materials for use in refractive surgery.

[0351] The lens designs disclosed herein can be produced using suitable ophthalmic lens production methods. For example, a contact lens can be fully molded, spin-cast, or semi-molded, wherein one surface is molded and a second surface is created by an additional process such as turning and the lens surface can be fully turned. An ophthalmic lens can be an intraocular lens with a bifocal, trifocal, or multifocal power zone for distance vision correction and intermediate and near vision correction. Eyeglass lenses can be produced entirely by molds or grinding or digital freeform processes. Semi-finished blanks or blank stocks with different base curves and parameters can contain a formed front surface or rear surface, and can be manufactured to a patient's final prescription in one or more additional processing steps, which has one or more advantages of the described improved ophthalmic lenses. For example, a semi-finished ophthalmic lens blank can have a size of at least 40 mm. In some embodiments, the semi-finished ophthalmic lens blank may have a size of at least 55 mm, 60 mm, 70 mm, 75 mm or more in diameter, and may have a greater thickness than the final eyeglass lens, and may have a rear surface that is substantially not the final shape or curvature of the finished ophthalmic lens that can be used by the patient, and may also be used as a precursor to the final ophthalmic lens. The semi-finished lens blank may require further processing steps so that the final ophthalmic lens having the final lens surface and thickness to correct the wearer's final prescription can then be formed to fit the eyeglass lens frame. The semi-finished lens blank or the final ophthalmic lens may also contain desired lens markings to enable further production steps or lens assembly or frame assembly steps. The lens markings may be laser engraved and may be added at appropriate points in the manufacturing process. The front surface of the ophthalmic lens in this example may be the same as the front surface of the semi-finished blank, so that the final lens for the patient may also be the final front surface shape of the final prescription, so the semi-finished lens blank may or may not include or have included the application of any lens coating for anti-reflection, anti-scratch, light modification or light filtering treatment, or color change or tinting of the lens. In this example, the semi-finished lens blank may require processing of the blank back surface in order to complete the final ophthalmic lens, the final back surface shape that works in conjunction with the lens refractive index, the front surface lens surface curvature, lens processing and lens thickness to provide the final prescription and shape of the ophthalmic lens in a variety of distance or near refractive errors, including but not limited to sphere, cylinder, cylinder axis, center, prismatic, progressive addition or multifocal power arrangements that the patient may require. The improved ophthalmic eyeglass lens design can provide improved optical performance, including improved image quality, reduced skew astigmatism or other distortions or aberrations, including cylindrical power and a wider field of view regardless of monocular pupil distance, fitting height, progression length, tetrahedron angle, panoramic tilt or vertex distance.

[0352] One or more ophthalmic lens embodiments disclosed herein may also be incorporated into suitable systems or processes, additional steps or treatments, or procedures to improve the efficiency of lens production. One or more ophthalmic lens embodiments disclosed herein may also be incorporated into a lens supply chain from material production to lens design to lens forming and lens coatings, as well as the special features applied or included, or the assembly of lenses into spectacle frames. One or more ophthalmic lens embodiments disclosed herein may be applicable to ophthalmic spectacle lenses in which there are multiple focal points or other optical designs that may be inherently distorted and require improved image quality and / or vision. For example, a unique lens shape, frame shape, or highly curved lens surface that may be required for a wrap frame. Laterally spaced optical axes may be applicable to aberration control, including: surface distortion, skew astigmatism, and / or aberrations, wherein improved designs may benefit from including upper spacing, lower spacing, temporal spacing, or nasal spacing of the optical axis, or a combination of these items in Cartesian or polar coordinates, and may be designed to manipulate the lens power to obtain a substantially seamless and / or substantially non-jointed surface curvature with desired optical performance. The final shape of the exemplary embodiments of the ophthalmic lenses disclosed herein can be produced by a suitable process and can include a grinding process, a digital diamond grinding process, or a digital freeform process. For example, from a standard single-vision lens, a lens blank, or a semi-finished blank having a final front surface shape, the final lens design features can then be designed to incorporate the patient's prescription to correct one or more of: refractive error, presbyopia, myopia control, and other optical functions to support the patient's requirements as prescribed by the practitioner or ordered by the user, or both. The exemplary design embodiments can be used in conjunction with a digital surface processing algorithm from the manufacturer, for example, a digital surface and a freeform process, such as digital ray path tracing (IOT, Madrid, Spain), combined on the same surface, or can be just a single surface.

[0353] 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 around the first axis.

[0354] In some embodiments, the ophthalmic lens can be configured to slow, reduce or prevent myopia progression in the eye. In some embodiments, the ophthalmic lens can be configured to correct myopia. In some embodiments, the ophthalmic lens can be configured to correct presbyopia.

[0355] In some embodiments, the ophthalmic lens may be a synoptic lens. In some embodiments, the ophthalmic lens may be a synoptic bifocal lens. In some embodiments, the ophthalmic lens may be a distance center bifocal lens. In some embodiments, the ophthalmic lens may be a distance center bifocal contact lens. In some embodiments, the ophthalmic lens may be a synoptic multifocal lens. In some embodiments, the ophthalmic lens may be a segmented vision lens.

[0356] In some embodiments, an ophthalmic lens may be configured to correct any combination of more than one of distance vision, intermediate vision, and near vision.

[0357] In some embodiments, the ophthalmic lens can be one or more of the following: a spectacle lens, a contact lens, a corneal onlay, a corneal inlay, an intraocular lens, a sheet or film that can be applied to or attached to an ophthalmic lens.

[0358] Other advantages of the claimed subject matter will become apparent from the following examples describing certain embodiments of the claimed subject matter.In certain embodiments, one or more than one (including, for example, all) of the following further embodiments may include each or a portion thereof in the other embodiments.

[0359] Example A

[0360] A1. An ophthalmic lens comprising: a first optical zone, the first optical zone being at least partially defined by a sphere having a first radius and having a first axis, the first optical zone being configured such that, when used with an eye, light passing through the first optical zone is refracted to a first focus on the first axis; and a second optical zone, the second optical zone being at least partially defined by a sphere having a second radius different from the first radius and being configured such that, when used with an eye, light passing through the second optical zone is refracted to a second focus (e.g., on a second axis); wherein the amount by which the second focus is displaced relative to the first axis is substantially equal to a central zone diameter of the ophthalmic lens.

[0361] Embodiment B:

[0362] B1. An ophthalmic lens comprising: a plurality of optical zones (e.g., 2, 3, 4, or 5 optical zones), wherein the plurality of optical zones are configured such that, when used 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; wherein at least two of the plurality of optical zones do not share a common axis.

[0363] Example C:

[0364] C1. An ophthalmic lens comprising: at least one first optical zone having a first axis, wherein the at least one first optical zone is configured such that, when used with an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focus on the first axis; and at least one second optical zone, wherein the at least one focus from the at least one second optical zone is not on the first axis.

[0365] C2. The ophthalmic lens of any of embodiments A, B or C, wherein at least one first optical zone and at least one second optical zone define an optical zone of the ophthalmic lens.

[0366] C3. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone and at least one second optical zone occupy a majority of the visual zone of the ophthalmic lens (e.g., at least 90%, 95%, 98% or 99% of the surface area of ​​the visual zone of the ophthalmic lens).

[0367] C4. An ophthalmic lens as described in any of embodiments A, B or C, wherein the ophthalmic lens is configured such that, when used with an eye, out-of-focus light associated with at least one second optical zone does not substantially interfere with the focus associated with at least one first optical zone.

[0368] C5. An ophthalmic lens as described in any of embodiments A, B or C, wherein the ophthalmic lens is configured such that, when used with an eye, defocused light associated with at least one first optical zone does not substantially interfere with focus associated with at least one second optical zone.

[0369] C6. An ophthalmic lens as described in any of embodiments A, B or C, wherein the ophthalmic lens is configured such that, when used with an eye, interference from out-of-focus light at the focused focus is reduced, substantially reduced, or eliminated.

[0370] C7. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone comprises a first optical power and at least one second optical zone comprises a second optical power different from the first optical power.

[0371] C8. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone comprises a first optical power and at least one second optical zone comprises a second optical power that is relatively more positive than the first optical power.

[0372] C9. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone comprises a first optical power and at least one second optical zone comprises a second optical power that is relatively less positive than the first optical power.

[0373] C10. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone is configured to correct one of the following: far vision, intermediate vision and near vision; and / or at least one second optical zone is configured to correct a different one of far vision, intermediate vision or near vision.

[0374] C11. The ophthalmic lens of any of embodiments A, B or C, wherein at least one first optical zone is configured to correct for distance vision and at least one second optical zone is configured to correct for near vision.

[0375] C12. The ophthalmic lens of any of embodiments 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.

[0376] C13. The ophthalmic lens of any one of embodiments A, B or C, wherein the first axis passes through the first optical zone.

[0377] C14. The ophthalmic lens of any of embodiments A, B or C, wherein at least one first optical zone occupies an upper portion of the optic zone and at least one second optical zone occupies a lower portion of the optic zone.

[0378] C15. The ophthalmic lens of any one of embodiments A, B or C, wherein the first axis is an axis of symmetry, and the optic zone of the ophthalmic lens is rotationally symmetric about the axis of symmetry.

[0379] C16. An ophthalmic lens as described in any of embodiments A, B or C, wherein the first axis is an optical axis of at least one first optical zone.

[0380] C17. An ophthalmic lens as described in any of embodiments A, B or C, wherein the first focal point is at a first distance from the ophthalmic lens on the first axis and the second focal point is at a second distance from the ophthalmic lens, the second distance being different from the first distance and shifted relative to the first axis.

[0381] C18. The ophthalmic lens of any of embodiments A, B or C, wherein the second optical zone has a second axis associated with the second optical zone, the second axis being displaced relative to the first axis.

[0382] C19. An ophthalmic lens as described in any of embodiments A, B or C, wherein the lateral spacing between the first axis and the second axis on the surface of the ophthalmic lens is about 0.5 mm (for example, 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 about 1 mm) or in some embodiments, the lateral spacing between the first axis and the second axis on the surface of the ophthalmic lens can be about 0.25 mm, about 0.5 mm, or about 0.75 mm.

[0383] C20. An ophthalmic lens as described in any of embodiments A, B or C, wherein the lateral spacing between the first axis and the second axis on the surface of the ophthalmic lens is less than about 0.5 mm (for example, less than about 50 um, about 60 um, about 70 um, about 80 um, about 90 um, 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 in some embodiments, the lateral spacing between the first axis and the second axis on the surface of the ophthalmic lens can be less than about 0.1 mm to about 0.25 mm, or about 0.5 mm.

[0384] C21. An ophthalmic lens as described in any of embodiments A, B or C, wherein the lateral spacing between the first axis and the second axis on the surface of the ophthalmic lens is less than about 0.5 mm (for example, less than about 50 um, about 60 um, about 70 um, about 80 um, about 90 um, 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 in some embodiments, the lateral spacing between the first axis and the second axis on the surface of the ophthalmic lens can be less than about 0.1 mm to about 0.25 mm, or about 0.5 mm.

[0385] C22. An ophthalmic lens as described in any of embodiments A, B or C, wherein the lateral spacing between the first axis and the second axis on the surface of the ophthalmic lens is greater than about 50um (for example, greater than about 50um, about 60um, about 70um, about 80um, about 90um, about 0.1mm, about 0.15mm, about 0.2mm, about 0.25mm, about 0.3mm, about 0.35mm, about 0.4mm, about 0.45mm, about 0.5mm, about 0.55mm, or about 0.6mm) or in some embodiments, the lateral spacing between the first axis and the second axis on the surface of the ophthalmic lens can be greater than about 0.1mm about 0.25mm, or about 0.5mm.

[0386] C23. An ophthalmic lens as described in any of embodiments A, B or C, wherein the second focus is on a second axis associated with at least one second optical zone, and the second axis is displaced relative to the first axis.

[0387] C24. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one second optical zone is configured such that, when used with an eye, light passing through the at least one second optical zone is refracted to a plurality of second focal points, the plurality of second focal points being on a corresponding one or more of a plurality of second axes associated with the at least one second optical zone, the plurality of second axes being displaced relative to the first axis.

[0388] C25. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone has a substantially circular shape.

[0389] C26. The ophthalmic lens of any one of embodiments A, B or C, wherein at least one first optical zone is located at the center of the ophthalmic lens.

[0390] C27. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone has a substantially circular shape located at the center of the ophthalmic lens and at least one second optical zone has a substantially annular shape surrounding the at least one first optical zone.

[0391] C28. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least a portion of at least one first optical zone has a substantially circular shape located at the center of the ophthalmic lens and at least a portion of at least one second optical zone has a substantially annular shape surrounding at least one first optical zone.

[0392] C29. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone comprises a first portion having a substantially circular shape located at the center of the ophthalmic lens and a second portion having a substantially annular shape surrounding the first portion.

[0393] C30. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one second optical zone includes 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.

[0394] C31. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone and at least one second optical zone are concentric (e.g., substantially concentric, and / or partially concentric).

[0395] C32. The ophthalmic lens of any of embodiments A, B or C, wherein at least one first optical zone and at least one second optical zone are substantially concentric but do not share a common axis.

[0396] C33. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone and / or at least one second optical zone is rotationally symmetric about the first axis.

[0397] C34. An ophthalmic lens as described in any of the preceding claims, wherein at least one first optical zone directly contacts at least one second optical zone.

[0398] C35. An ophthalmic lens as described in any of embodiments A, B or C, wherein the hybrid zone is located between at least one first optical zone and at least one second optical zone.

[0399] C36. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone occupies greater than 50% (e.g., approximately 55%, 60%, 65%, 70%, or 75%) of the surface area of ​​the optic zone of the ophthalmic lens.

[0400] C37. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone occupies less than 50% (e.g., approximately 45%, 40%, 35%, 30%, or 25%) of the surface area of ​​the visual zone of the ophthalmic lens.

[0401] C38. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone occupies approximately 60% (e.g., approximately 55%, 56%, 57%, 58%, 59%, 60%, 61%, 62%, 63%, 64%, or 65%) of the surface area of ​​the optic zone of the ophthalmic lens.

[0402] C39. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone occupies approximately 40% (e.g., approximately 35%, 36%, 37%, 38%, 39%, 40%, 41%, 42%, 43%, 44%, or 45%) of the surface area of ​​the optic zone of the ophthalmic lens.

[0403] C40. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone occupies less than about 75% (e.g., about 55%, 60%, 65%, 70%, or 75%) of the surface area of ​​the optic zone of the ophthalmic lens.

[0404] C41. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone occupies greater than about 25% (e.g., about 25%, 30%, 35%, 40%, or 45%) of the surface area of ​​the optic zone of the ophthalmic lens.

[0405] C42. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone is at least partially defined by a sphere having a first radius and / or at least one second optical zone is at least partially defined by a sphere having a second radius different from the first radius.

[0406] C43. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone is at least partially defined by a sphere having a first radius and / or at least one second optical zone is at least partially defined by a sphere having a second radius smaller than the first radius.

[0407] C44. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone is at least partially defined by a sphere having a first radius and / or at least one second optical zone is at least partially defined by a sphere having a second radius greater than the first radius.

[0408] C45. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone is substantially circular in shape and has a diameter of about 3 mm (for example, in some embodiments, the diameter can be about 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 2-4 mm, 2-3 mm, 3-4 mm, less than 4 mm, less than 3.5 mm, and / or less than 3 mm).

[0409] C46. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one second optical zone is substantially annular in shape and has an inner diameter of about 3 mm (for example, in some embodiments, the inner diameter can be about 2 mm, 2.5 mm, 3 mm, 3.5 mm, 4 mm, 2-4 mm, 2-3 mm, 3-4 mm, less than 4 mm, less than 3.5 mm, and / or less than 3 mm) and an outer diameter of about 7 mm (for example, in some embodiments, the outer diameter can 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, less than 8 mm, less than 7.5 mm, and / or less than 7 mm).

[0410] C47. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one first optical zone is substantially circular in shape and at least one second optical zone is substantially annular in shape and the inner diameter of at least one second optical zone is substantially equal to the diameter of at least one first optical zone.

[0411] C48. An ophthalmic lens as described in any of embodiments A, B or C, wherein the position of the second focus is determined at least in part by reducing and / or eliminating the inclination of the front surface of the second optical zone relative to the radius of curvature of the first optical zone.

[0412] C49. An ophthalmic lens as described in any of embodiments A, B or C, wherein at least one second optical zone is configured such that, when used with 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 that are not on the first axis.

[0413] C50. The ophthalmic lens of any one of embodiments A, B or C, wherein the ophthalmic lens is configured to slow, reduce or prevent myopia progression in the eye.

[0414] C51. An ophthalmic lens as described in any of embodiments A, B or C, wherein the ophthalmic lens is configured for correction of myopia.

[0415] C52. An ophthalmic lens as described in any of embodiments A, B or C, wherein the ophthalmic lens is configured for correcting presbyopia.

[0416] C53. The ophthalmic lens of any one of embodiments A, B or C, wherein the ophthalmic lens is a synopic lens.

[0417] C54. An ophthalmic lens as described in any of embodiments A, B or C, wherein the ophthalmic lens is a segmented vision lens and / or a progressive addition multifocal (PAL) lens.

[0418] C55. The ophthalmic lens of any one of embodiments 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.

[0419] Embodiment D:

[0420] D1. An ophthalmic lens comprising: at least one first optical zone having a first axis, the at least one first optical zone being configured such that, when used with an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focus on the first axis; and at least one second optical zone being configured such that, when used with 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, the one or more focal points being positioned off-axis relative to the first focal point and on at least one focal plane different from the focal plane corresponding to the first focus; wherein the at least one second optical zone is configured such that light extending beyond the one or more focal points provides an extended depth of focus.

[0421] D2. An ophthalmic lens comprising: at least one first optical zone having a first axis, the at least one first optical zone being configured such that, when used with an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focus on the first axis; and at least one second optical zone being configured such that, when used with 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, the one or more focal points being positioned off-axis relative to the first focus and on at least one focal plane different from the focal plane corresponding to the first focus; wherein the at least one first optical zone is configured such that the first focus is positioned in front of the retinal plane; and wherein the at least one second optical zone is configured such that light extending beyond the one or more focal points together with light refracted to the first focus provides an extended depth of focus.

[0422] D3. An ophthalmic lens comprising: at least one first optical zone having a first axis, the at least one first optical zone being configured such that, when used with an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focus on the first axis; and at least one second optical zone being configured such that, when used with an eye, at least a portion of light passing through the at least one second optical zone is refracted to one or more foci, the one or more foci being positioned off-axis relative to the first focus and on at least one focal plane different from the focal plane corresponding to the first focus; wherein the at least one first optical zone is configured such that the first focus is positioned in front of a retinal plane; and wherein the at least one second optical zone is configured such that light extending beyond the one or more foci together with light refracted into the first focus provides an extended depth of focus, the extended depth of focus extending from a retinal image plane to a front plane positioned in front of the first focus at a position that causes the first focus to be substantially equidistant from the front plane and the retinal plane.

[0423] D4. An ophthalmic lens comprising: at least one first optical zone having a first axis, the at least one first optical zone being configured such that, when used with an eye, at least a portion of light passing through the at least one first optical zone is refracted to a first focus on the first axis; and at least one second optical zone being configured such that, when used with 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, the one or more focal points being positioned off-axis relative to the first focus and on at least one focal plane different from the focal plane corresponding to the first focus; wherein the at least one first optical zone is configured such that the first focus is positioned in front of the retinal plane; and wherein the at least one second optical zone is configured such that light extending beyond the one or more focal points together with light refracted to the first focus provides an extended depth of focus that is completely within the eye.

[0424] D5. The ophthalmic lens of any one of embodiment D, wherein at least one first optical zone has a substantially circular shape and is located at the center of the ophthalmic lens and at least one second optical zone has a substantially annular shape surrounding the at least one first optical zone.

[0425] D6. The ophthalmic lens of any one of Embodiment D, wherein at least one first optical zone and at least one second optical zone are concentric.

[0426] D7. An ophthalmic lens as described in any of Example D, wherein one or more foci positioned off-axis relative to the first focal point include a limited 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).

[0427] D8. An ophthalmic lens as described in any of Example D, wherein the one or more focal points positioned off-axis relative to the first focal point include an infinite number of focal points.

[0428] D9. An ophthalmic lens as described in any of Example D, wherein one or more focal points positioned off-axis relative to the first focal point are positioned on at least 2 focal planes (e.g., at least 2, 3, 4, or 5 focal planes).

[0429] D10. An ophthalmic lens as described in any of Example D, wherein the number and position of one or more focal points are determined at least in part based on any combination of one or more of the following: a width of at least one second optical zone, a curvature of at least one second optical zone, a position of at least one second optical zone, a base focal power of at least one second optical zone, and / or a lateral spacing value of at least one second optical zone.

[0430] D11. An ophthalmic lens as described in any of Example D, wherein the depth of focus provided by the ophthalmic lens is determined at least in part based on any combination of one or more of the following: a width of at least one second optical zone, a curvature of at least one second optical zone, a position of at least one second optical zone, a base focal length of at least one second optical zone, a lateral spacing value of at least one second optical zone, and / or m and p components.

[0431] D12. An ophthalmic lens as described in any of Example D, wherein at least one second optical zone has a substantially annular shape having 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).

[0432] D13. An ophthalmic lens as described in any of Example D, wherein at least one second optical zone has a substantially annular shape with a curvature between approximately -10 and +10D (e.g., approximately -10D, -9D, -8D, -7D, -6D, -5D, -4D, -3D, -2D, -1D, +1D, +2D, +3D, +4D, +5D, +6D, +7D, +8D, +9D, and / or +10D).

[0433] D14. An ophthalmic lens as described in any of Example D, wherein at least one second optical zone has a substantially annular shape with a base focal power between approximately -20 and +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).

[0434] D15. An ophthalmic lens as described in any of Example D, wherein at least one second optical zone has a substantially annular shape, wherein the lateral spacing value on the surface of the lens is between 0.2 and 1 mm (for example, the lateral spacing value on the surface of the lens 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 or about 1 mm).

[0435] D16. An ophthalmic lens as described in any of Example D, wherein at least one second optical zone has a substantially annular shape, wherein the lateral spacing value on the surface of the lens is between 0.2 and 1 mm (for example, the lateral spacing value on the surface of the lens can be less than about 50um, 60um, 70um, 80um, 90um, 0.1mm, 0.15mm, 0.2mm, 0.25mm, 0.3mm, 0.35mm, 0.4mm, 0.45mm, 0.5mm, 0.55mm, and / or 0.6mm).

[0436] D17. An ophthalmic lens as described in any of Example D, wherein at least one second optical zone has a substantially annular shape, wherein the lateral spacing value on the surface of the lens is between 0.2 and 1 mm (for example, the lateral spacing value on the surface of the lens can be greater than about 50um, 60um, 70um, 80um, 90um, 0.1mm, 0.15mm, 0.2mm, 0.25mm, 0.3mm, 0.35mm, 0.4mm, 0.45mm, 0.5mm, 0.55mm, and / or 0.6mm).

[0437] D18. The ophthalmic lens of any one of Embodiment D, wherein at least one focal plane is in front of, behind, or in substantially the same plane as the first focus.

[0438] D19. An ophthalmic lens as described in any of Example D, wherein rays extending beyond at least one focal plane also form a depth of focus behind and in front of the first focus.

[0439] D20. An ophthalmic lens as described in any of Example D, wherein the ratio of the depth of focus in front of the first focus to the depth of focus behind the first focus can be approximately 100:0 (completely in front of the first focus), 90:10, 80:20, 75:25, 70:30, 60:40, 50:50 (equally 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).

[0440] D21. The ophthalmic lens of any of Embodiment D, wherein at least one second region cross-section has a focal length in two dimensions that is independent of the rest of the ophthalmic lens.

[0441] D22. The ophthalmic lens of any one of Embodiment D, wherein the at least one second region is created by adjusting the curvature of the base lens on at least one of the front surface of the ophthalmic lens and / or the back surface of the ophthalmic lens.

[0442] D23. The ophthalmic lens of any one of Embodiment D, wherein at least one second zone is created by adjusting the curvature of the base lens on the front surface of the ophthalmic lens to create one of a positive optical zone or a negative optical zone.

[0443] D24. The ophthalmic lens of any one of Embodiment D, wherein at least one second zone is created by adjusting the curvature of the base lens on the back surface of the ophthalmic lens to create one of a positive optical zone or a negative optical zone.

[0444] D25. An ophthalmic lens as described in any of Embodiment D, wherein at least one second optical zone has a substantially annular shape comprising an inclined curvature to affect (e.g., shift) depth of focus.

[0445] D26. An ophthalmic lens as described in any of Example D, wherein at least one second optical zone has a substantially annular shape comprising multiple curved injections (e.g., 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 curved injections) having the same optical properties or different optical properties.

[0446] D27. An ophthalmic lens as described in any of Example D, wherein at least one second optical zone has a substantially annular shape comprising multiple combined curvatures (e.g., 2, 3, 4, 5, 6, 7, 8, 9, and / or 10 combined curvatures).

[0447] D28. An ophthalmic lens as described in any of Embodiment D, wherein at least one second optical zone has a substantially annular shape created by replacing at least one (or two) surface curvatures of the lens with a line (e.g., a surface with no or substantially no curvature).

[0448] D29. An ophthalmic lens as described in any of Example D, wherein the depth of focus provided by the ophthalmic lens and / or the annular region can 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).

[0449] D30. The ophthalmic lens of any one of Embodiment D, wherein at least one first optical zone and at least one second optical zone define an optical zone of the ophthalmic lens.

[0450] D31. The ophthalmic lens of any one of Embodiment D, wherein at least one first optical zone and at least one second optical zone occupy substantially all of the optic zone of the ophthalmic lens.

[0451] D32. An ophthalmic lens as described in any of Example D, wherein the ophthalmic lens is configured such that, when used with an eye, out-of-focus light associated with at least one second optical zone does not interfere with the focus associated with at least one first optical zone (e.g., does not substantially interfere with the focus associated with at least one first optical zone).

[0452] D33. An ophthalmic lens as described in any of Example D, wherein the ophthalmic lens is configured such that, when used with an eye, out-of-focus light associated with at least one first optical zone does not interfere with the focus associated with at least one second optical zone (e.g., does not substantially interfere with the focus associated with at least one second optical zone).

[0453] D34. An ophthalmic lens as described in any of Example D, wherein the ophthalmic lens is configured such that, when used with an eye, interference from out-of-focus light at the focused focal point is controlled, reduced, substantially reduced, and / or eliminated.

[0454] D35. An ophthalmic lens as described in any of Example D, wherein at least one first optical zone comprises a first optical power and at least one second optical zone comprises one or more second optical powers different (e.g., relatively positive or negative) from the first optical power.

[0455] D36. An ophthalmic lens as described in any of Example D, wherein at least one first optical zone is configured to correct one of far vision, intermediate vision, or near vision; and / or at least one second optical zone is configured to correct a different one of far vision, intermediate vision, or near vision.

[0456] D37. An ophthalmic lens as described in any of Example 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.

[0457] D38. An ophthalmic lens as described in any of Example D, wherein the first axis passes through the first optical zone.

[0458] D39. The ophthalmic lens of any one of Embodiment D, wherein the first axis is an axis of symmetry, and the optic zone of the ophthalmic lens is rotationally symmetric around the axis of symmetry.

[0459] D40. The ophthalmic lens of any one of Embodiment D, wherein the first axis is an optical axis of the first optical zone.

[0460] D41. An ophthalmic lens as described in any of Example D, wherein the lateral spacing 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 about 1 mm).

[0461] D42. An ophthalmic lens as described in any of Example D, wherein the lateral spacing between the first axis and the second axis on the surface of the ophthalmic lens is less than about 0.5 mm (for example, less than about 50 um, about 60 um, about 70 um, about 80 um, about 90 um, 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).

[0462] D43. An ophthalmic lens as described in any of Example D, wherein the lateral spacing between the first axis and the second axis on the surface of the ophthalmic lens is less than about 0.5 mm (e.g., about 50 um, about 60 um, about 70 um, about 80 um, about 90 um, 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).

[0463] D44. An ophthalmic lens as described in any of Example D, wherein the lateral spacing between the first axis and the second axis on the surface of the ophthalmic lens is greater than about 50um (for example, greater than about 50um, about 60um, about 70um, about 80um, about 90um, about 0.1mm, about 0.15mm, about 0.2mm, about 0.25mm, about 0.3mm, about 0.35mm, about 0.4mm, about 0.45mm, about 0.5mm, about 0.55mm, or about 0.6mm).

[0464] D45. The ophthalmic lens of any one of Embodiment D, wherein at least one first optical zone and / or at least one second optical zone is rotationally symmetric about a first axis.

[0465] D46. The ophthalmic lens of any one of Embodiment D, wherein at least one first optical zone directly contacts at least one second optical zone.

[0466] D47. An ophthalmic lens as described in any of Example D, wherein at least one first optical zone occupies greater than 50% (e.g., about 55%, about 60%, about 65%, about 70%, or about 75%) of the surface area of ​​the optic zone of the ophthalmic lens.

[0467] D48. An ophthalmic lens as described in any of Example D, wherein at least one first optical zone is at least partially defined by a sphere having a first radius and / or at least one second optical zone is at least partially defined by a sphere having a second radius different from (e.g., smaller than or larger than) the first radius.

[0468] D49. An ophthalmic lens as described in any of Example D, wherein at least one first optical zone is substantially circular in shape and has a diameter of about 3 mm (e.g., in some embodiments, the diameter can 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, less than about 4 mm, less than about 3.5 mm, and / or less than about 3 mm).

[0469] D50. An ophthalmic lens as described in any of Example D, wherein at least one second optical zone is substantially annular in shape and has an inner diameter of about 3 mm (for example, in some embodiments, the inner diameter can 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, less than about 4 mm, less than about 3.5 mm, and / or less than about 3 mm) and an outer diameter of about 7 mm (for example, in some embodiments, the outer diameter can 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, less than about 8 mm, less than about 7.5 mm, and / or less than about 7 mm).

[0470] D51. An ophthalmic lens as described in any of Example D, wherein at least one first optical zone is substantially circular in shape and at least one second optical zone is substantially annular in shape and an inner diameter of at least one second optical zone is substantially equal to a diameter of at least one first optical zone.

[0471] D52. The ophthalmic lens of any one of Embodiment D, wherein the ophthalmic lens is configured to slow, reduce or prevent myopia progression in the eye.

[0472] D53. An ophthalmic lens as described in any of Example D, wherein the ophthalmic lens is configured for correction of myopia.

[0473] D54. The ophthalmic lens of any one of Embodiment D, wherein the ophthalmic lens is configured for correcting presbyopia.

[0474] D55. The ophthalmic lens of any one of Embodiment D, wherein the ophthalmic lens is a synopic lens.

[0475] D56. The ophthalmic lens of any one of Embodiment D, wherein the ophthalmic lens is a segmented vision lens and / or a progressive addition multifocal (PAL) lens.

[0476] It should be understood that the embodiments disclosed and defined in this specification extend to all alternative combinations of two or more of the individual features mentioned or evident from the text or drawings. All of these different combinations constitute various alternative aspects of the present disclosure.

[0477] The foregoing summarizes the features of several embodiments so that those skilled in the art can better understand various aspects of the present disclosure. Those skilled in the art will appreciate that they can easily use the present disclosure as a basis for designing or modifying other processes and structures to achieve the same purposes and / or achieve the same advantages as the embodiments described herein. Those skilled in the art will also appreciate that such equivalent constructions do not depart from the spirit and scope of the present invention, and that they can make various changes, substitutions, and modifications to the present invention without departing from the spirit and scope of the present disclosure.

Claims

1. An ophthalmic lens comprising: a first optical zone having a first axis, the first optical zone being configured such that, in use with an eye, at least a portion of light passing through the first optical zone is refracted to a first focus on the first axis; and a second optical zone configured such that, in use with an eye, at least a portion of light passing through the second optical zone is refracted to one or more focal points located off-axis relative to the first focal point and in at least one focal plane different from the focal plane corresponding to the first focal point; in, the first optical zone being configured such that the first focal point is positioned in front of a retinal plane; wherein the second optical zone is configured such that light extending beyond the one or more focal points together with light refracted into the first focal point provides an extended depth of focus extending from the retinal image plane to the front plane positioned anterior to the first focal point at a position that causes the first focal point to be substantially equidistant from the front plane and the retinal plane; Wherein the ophthalmic lens is configured to, when in use, space and / or shift at least one focal point associated with a focused image at a given image plane and a focal point associated with one or more out-of-focus images or rays using one or more optical surfaces, wherein the optical surfaces comprise two or more optical elements, wherein the two or more optical elements are positioned, offset, rotated, tilted or shifted relative to each other such that all or some of the two or more optical elements do not share a common optical axis.

2. The ophthalmic lens according to claim 1, wherein: The two or more optical elements are selected from the group consisting of spherical, elliptical, conical, aspherical, and aspherical toric elements.

3. The ophthalmic lens according to claim 1 or 2, wherein: The first optical zone and the second optical zone are substantially concentric and preferably do not share a common axis.

4. An ophthalmic lens according to any one of the preceding claims, wherein: The first optical zone is located at the center of the ophthalmic lens and the second optical zone has a substantially annular shape surrounding the first optical zone.

5. An ophthalmic lens according to any one of the preceding claims, wherein: The first optical zone is substantially circular in shape and has a diameter of approximately 3 mm.

6. An ophthalmic lens as claimed in any one of the preceding claims, wherein: The second optical zone is substantially annular in shape and has an inner diameter of at least 3 mm and an outer diameter of approximately 7 mm.

7. An ophthalmic lens according to any one of the preceding claims, wherein: The one or more focal points located off-axis relative to the first focal point include a finite number of focal points.

8. An ophthalmic lens according to any one of the preceding claims, wherein: The one or more focal points located off-axis relative to the first focal point comprise an infinite number of focal points.

9. An ophthalmic lens according to any one of the preceding claims, wherein: The one or more focal points located off-axis relative to the first focal point are located on at least 2 focal planes.

10. An ophthalmic lens as claimed in any one of the preceding claims, wherein: The number and position of the one or more focal points are determined at least in part based on any combination of one or more of the following: a width of the second optical zone, a curvature of the second optical zone, a position of the second optical zone, a base power of the second optical zone, and / or a lateral separation value of the second optical zone.

11. An ophthalmic lens as claimed in any one of the preceding claims, wherein: The depth of focus provided by the ophthalmic lens is determined at least in part based on any combination of one or more of: a width of the second optical zone, a curvature of the second optical zone, a position of the second optical zone, a base power of the second optical zone, a lateral separation value of the second optical zone, and / or m and p components.

12. An ophthalmic lens as claimed in any one of the preceding claims, wherein: The lateral separation of the first axis and the second axis on the surface of the ophthalmic lens is greater than about 0.1 mm.

13. An ophthalmic lens as claimed in any one of the preceding claims, wherein: The lateral separation of the first axis and the second axis on the surface of the ophthalmic lens is less than about 0.5 mm.

14. An ophthalmic lens as claimed in any one of the preceding claims, wherein: The first optical zone is configured to correct distance vision and wherein the second optical zone is preferably configured to correct near vision.

15. An ophthalmic lens as claimed in any one of the preceding claims, wherein: The first optical zone has a first power and the second optical zone has a second power different from the first power.

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