Achromatic lenses for vision therapy

Abstract

The present invention provides apparatus, systems, and methods for providing improved ophthalmic lenses, particularly intraocular lenses (IOLs), including features for reducing the effects of flare and glare. An exemplary ophthalmic lens may include an optic having a central region disposed about an optical axis and a peripheral region extending outward from the central region, wherein a diffractive achromatic lens is positioned on the peripheral region, the central region lacks an achromatic lens, and the base optical power for distances in the central region is the same as the base optical power for distances in the peripheral region.

Description

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS

[0002] This application claims priority to U.S. Provisional Patent Application No. 62 / 955,341, filed on December 30, 2019, which is hereby incorporated by reference in its entirety. Background Art

[0003] Embodiments of the present disclosure relate to vision therapy technologies, and in particular to ophthalmic lenses, such as, for example, contact lenses, corneal inlays or onlays, or intraocular lenses (IOLs), including, for example, phakic IOLs and piggyback IOLs (i.e., an IOL implanted in an eye that already has an IOL).

[0004] Presbyopia is a condition that affects the eye's adaptive properties. As objects move closer to a young, normally functioning eye, the action of ciliary muscle contraction and zonular relaxation allows the eye's lens to change shape, thereby increasing its refractive power and close-focusing ability. This adaptation allows the eye to focus and refocus between near and far objects.

[0005] Presbyopia typically develops as people age and is associated with a natural, gradual loss of adaptability. Presbyopes often lose the ability to quickly and easily refocus on objects at different distances. The effects of presbyopia typically become noticeable after the age of 45. By the age of 65, the lens has often lost almost all of its elastic properties and has only a limited ability to change shape.

[0006] As the eye's ability to adapt decreases, aging can also cause clouding of the lens due to the formation of cataracts. Cataracts can form in the hard central nucleus of the lens, in the softer peripheral cortical portion of the lens, or on the back of the lens. Cataracts can be treated by replacing the clouded natural lens with an artificial lens (IOL). An artificial lens replaces the natural lens in the eye and is often called an intraocular lens, or "IOL."

[0007] Monofocal IOLs are intended to provide vision correction at only one distance, typically far focus. Minimally, because monofocal IOLs provide vision treatment at only one distance, and because typical correction is for far distances, glasses are generally required to achieve good near vision and sometimes good intermediate vision. The term "near vision" generally corresponds to the vision provided when an object is: equal to or less than 1.5 feet from the subject's eye. The term "far vision" generally corresponds to the vision provided when an object is at least about 5 feet to 6 feet away, or more. The term "intermediate vision" corresponds to the vision provided when an object is about 1.5 feet to about 5 feet to 6 feet away from the subject's eye. Such characteristics of near, intermediate and distance vision correspond to those described in: Morlock R, Wirth RJ, Tally SR, Garufis C, Heichel CWD, Patient-Reported Spectacle Independence Questionnaire (PRSIQ): Development and Validation. Am J Ophthalmology 2017;178:101-114.

[0008] Various attempts have been made to address the limitations associated with monofocal IOLs. For example, multifocal IOLs have been proposed, which, in principle, provide two focal points, one near and one far, optionally with some degree of intermediate focus. Such multifocal or bifocal IOLs are intended to provide good vision at both distances and include both refractive and diffractive multifocal IOLs. In some cases, multifocal IOLs intended to correct vision at two distances may provide approximately 3.0 or 4.0 diopters of near (additional) refractive power.

[0009] For example, multifocal IOLs may rely on diffractive optical surfaces to direct portions of light energy to different focal lengths, thereby allowing patients to clearly see both near and far objects. Multifocal ophthalmic lenses (including contact lenses, etc.) have also been proposed to treat presbyopia without removing the natural lens. Monofocal or multifocal diffractive optical surfaces may also be configured to provide reduced chromatic aberration.

[0010] Diffractive single-focus lenses and diffractive multifocal lenses can utilize materials with a given refractive index and surface curvature that provide refractive power. Diffractive lenses have a diffractive profile that imparts diffractive power to the lens that contributes to the overall refractive power of the lens. The diffraction profile is typically characterized by a plurality of diffractive regions. When used in ophthalmic lenses, these regions are typically annular lens regions or gratings spaced around the optical axis of the lens. Each grating can be defined by an optical zone, a transition region between the optical zone and the optical zone of an adjacent grating, and a grating geometry. The grating geometry includes the inner and outer diameters and shape or slope of the optical zone, the height or step height and shape of the transition region. The surface area or diameter of the grating primarily determines the diffractive power of the lens, and the step height of the transition zone between the gratings primarily determines the light distribution between the different refractive powers. Together, these gratings form the diffraction profile.

[0011] The multifocal diffractive profile of the lens can be used to alleviate presbyopia by providing two or more refractive powers; for example, one for near vision and one for distance vision. The lens can also take the form of an intraocular lens that is placed in the capsular bag of the eye, replacing the natural lens, or placed in front of the natural lens. The lens can also be in the form of a contact lens, most commonly a bifocal contact lens, or any of the other forms mentioned herein.

[0012] While multifocal ophthalmic lenses have improved the quality of vision for many patients, additional improvements would also be beneficial. For example, some pseudophakic patients experience undesirable visual effects (photopsia) such as glare or halos. Halos can occur when light from an unfocused image creates a defocused image that overlaps the focused image. For example, if light from a distant point source is imaged on the retina through the far focus of a bifocal IOL, the near focus of the IOL will simultaneously overlap a defocused image over the image formed by the far focus. This defocused image can manifest itself in the form of a halo around the in-focus image and is known as a halo. Another area for improvement relates to the typical bifocality of multifocal lenses. While multifocal ophthalmic lenses typically provide adequate near and far vision, intermediate vision may be sacrificed.

[0013] Improvements can also be found in the area of achromatic lenses. Achromatic lenses can be used to improve the color contrast of a lens. However, if such achromatic lenses are provided as diffraction patterns, they can result in undesirable visual effects such as glare or halos. Therefore, improvements in lenses with achromatic lenses are needed. Summary of the Invention

[0014] Embodiments described herein include an ophthalmic lens comprising an optic having a central region disposed about an optical axis and a peripheral region extending outward from the central region, wherein a diffractive achromatic lens is positioned on the peripheral region and the central region lacks an achromatic lens, and a base power for distances in the central region is the same as a base power for distances in the peripheral region.

[0015] The optical element may include a transition portion between a central region and a peripheral region, at which the base curvature of the optical element changes. The central region may be adjacent to the peripheral region. The base refractive power for distance in the peripheral region may have the distance power of a diffractive achromatic lens combined with the distance refractive power of the peripheral region. The optical element may also extend outward from the optical axis to an outer periphery of the optical element, and the base refractive power for distance of the optical element may extend outward from the optical axis to the outer periphery of the optical element.

[0016] The central region can be a refractive region, and the base optical power for the distance of the central region can be the refractive power. The central region can extend outward from the optical axis to a radius of at least 1 mm, at least 1.5 mm, or at least 2 mm. In other embodiments, the central region can include an extended depth of focus diffractive region or utilize a bifocal, trifocal, or aperiodic design (or can be a refractive extended depth of focus region).

[0017] Embodiments described herein include a method comprising manufacturing an optic for an ophthalmic lens having a central region disposed about an optical axis and a peripheral region extending outward from the central region, wherein a diffractive achromatic lens is positioned on the peripheral region, the central region lacks an achromatic lens, and a base refractive power for distances in the central region is the same as a base refractive power for distances in the peripheral region.

[0018] The method may include receiving an ophthalmic lens prescription and manufacturing an optical element based on the ophthalmic lens prescription. The method may include determining a profile of one or more of a central region or a diffractive achromatic lens based on the ophthalmic lens prescription. The base refractive power for distance in the peripheral region may include the distance refractive power of the diffractive achromatic lens combined with the distance refractive power of the peripheral region. The manufacturing method may be used to manufacture any of the lenses disclosed herein.

[0019] Embodiments described herein include a system for manufacturing an ophthalmic lens. The system may include a processor configured to determine at least a portion of a profile of an optical component having a central region disposed about an optical axis and a peripheral region extending outward from the central region, wherein a diffractive achromatic lens is positioned on the peripheral region, the central region lacks an achromatic lens, and a base optical power for distances in the central region is the same as a base optical power for distances in the peripheral region. The system may include a manufacturing component that manufactures the optical component based on the profile.

[0020] The system may also include an input for receiving an ophthalmic lens prescription, and the processor may be configured to determine a profile of one or more of the central region or the diffractive achromatic lens based on the ophthalmic lens prescription. The base refractive power for distance in the peripheral region may include the distance refractive power of the diffractive achromatic lens combined with the distance refractive power of the peripheral region. The optic extends outward from the optical axis to an outer periphery of the optic, and the base refractive power for distance in the optic is the same from the optical axis to the outer periphery of the optic. The manufacturing system may be used to manufacture any of the lenses disclosed herein. BRIEF DESCRIPTION OF THE DRAWINGS

[0021] Figure 1A A cross-sectional view of an eye with an implanted multifocal refractive intraocular lens is shown.

[0022] Figure 1B A cross-sectional view of an eye with an implanted multifocal diffractive intraocular lens is shown.

[0023] Figure 2A A front view of a diffractive multifocal intraocular lens is shown.

[0024] Figure 2B A cross-sectional view of a diffractive multifocal intraocular lens is shown.

[0025] Figures 3A to 3B A graphical representation of a portion of the diffraction profile of a conventional diffractive multifocal lens.

[0026] Figure 4 The diffraction profile of a diffractive achromat lens is shown.

[0027] Figure 5 Embodiments of an optical element are shown that include a central region disposed about an optical axis and having a peripheral region extending outwardly from the central region.

[0028] Figure 6 A graph showing the over-frequency modulation transfer function (MTF) of an optic that does not include an achromatic lens.

[0029] Figure 7Graph showing the through-frequency MTF of an optic including an achromatic lens along the entire optical surface.

[0030] Figure 8 A graph showing the through-frequency MTF of an optic including a central region and including a diffractive achromat over a peripheral region is shown.

[0031] Figure 9 Shown Figure 7 Graph of the point spread function (PSF) of an optical component.

[0032] Figure 10 Shown Figure 8 Graph of the point spread function (PSF) of an optical component.

[0033] Figure 11 An embodiment of the system is shown. DETAILED DESCRIPTION

[0034] Figure 1A 、 Figure 1B 、 Figure 2A 、 Figure 2B 、 Figure 3A and Figure 3B A multifocal IOL lens geometry is shown, aspects of which are described in US Patent Publication No. 2011-0149236A1, which is hereby incorporated by reference in its entirety.

[0035] Figure 1A is a cross-sectional view of an eye E fitted with a multifocal IOL 11. As shown, the multifocal IOL 11 may comprise a bifocal IOL, for example. The multifocal IOL 11 receives light from at least a portion of the cornea 12 in front of the eye E and is generally centered about the optical axis of the eye E. For ease of reference and clarity, Figure 1A and Figure 1B The refractive properties of other parts of the eye, such as the corneal surface, are not disclosed. Only the refractive and / or diffractive properties of the multifocal IOL 11 are shown.

[0036] Each major surface of the lens 11 (including the anterior (front) surface and the posterior (back) surface) typically has a refractive profile, such as biconvex, plano-convex, plano-concave, a meniscus, etc. These two surfaces together define the effect of the lens 11 on the imaging performance of the eye E relative to the properties of the surrounding aqueous humor, the cornea, and other optical components of the overall optical system. Conventional monofocal IOLs have a refractive power based on the refractive index of the lens material and also based on the curvature or shape of the anterior and posterior surfaces or the anterior and posterior surfaces of the lens. One or more support elements can be configured to secure the lens 11 to the patient's eye.

[0037] Multifocal lenses may also optionally utilize the refractive properties of the lens. Such lenses typically include different refractive powers in different areas of the lens in order to mitigate the effects of presbyopia. For example, Figure 1A As shown, a peripheral region of a refractive multifocal lens 11 may have a refractive power suitable for vision at a distance. The same refractive multifocal lens 11 may also include an inner region having a higher surface curvature and generally higher overall refractive power suitable for near vision (sometimes referred to as a positive add power).

[0038] Multifocal diffractive IOLs or contact lenses can also have diffractive refractive power, rather than relying entirely on the refractive properties of the lens, such as Figure 1B 18 is shown. The diffractive power can, for example, include positive or negative power and can be the largest (or even the primary) factor in increasing the overall optical power of the lens. The diffractive power is imparted by a plurality of concentric diffractive zones that form a diffractive profile. The diffractive profile can be applied to the anterior or posterior surface, or both.

[0039] The diffraction profile of a diffractive multifocal lens directs incident light into multiple diffraction orders. When light 13 enters from in front of the eye, multifocal lens 18 directs light 13 to form a far-field focal point 15a for viewing distant objects and a near-field focal point 15b for viewing objects close to the eye on retina 16. Depending on the distance from light source 13, the focal point on retina 16 may alternatively be a near-field focal point 15b. Typically, far-field focal point 15a is associated with the 0th diffraction order, and near-field focal point 15b is associated with the 1st diffraction order, but other diffraction orders may also be used.

[0040] Bifocal ophthalmic lenses 18 typically distribute most of the light energy into two visual levels, typically with the goal of having a roughly even split (50%:50%) of the imaging light energy, one visual level corresponding to distance vision and one visual level corresponding to near vision, but typically with some portion attributed to the non-visual level.

[0041] Corrective optics can be provided by a phakic IOL, which can be used to treat a patient while leaving the natural lens in place. Phakic IOLs can be angle-supported, iris-supported, or ciliary sulcus-supported. Phakic IOLs can be placed on the natural lens or piggybacked on another IOL. It is also contemplated that the present disclosure can be applied to inlays, onlays, accommodating IOLs, intraocular phakic IOLs, other forms of intraocular implants, spectacles, and even laser vision correction.

[0042] Figure 2A and Figure 2BVarious aspects of a conventional diffractive multifocal lens 20 are shown. The multifocal lens 20 can have certain optical properties generally similar to those of the multifocal IOLs 11, 18 described above. The multifocal lens 20 has an anterior lens face 21 and a posterior lens face 22 disposed about an optical axis 24. The faces 21, 22, or optical surfaces, extend radially outward from the optical axis 24 to an outer periphery 27 of the optic. The faces 21, 22, or optical surfaces, face opposite each other.

[0043] When worn on the eye of a subject or patient, the optical axis of the lens 20 is substantially aligned with the optical axis of the eye E. The curvature of the lens 20 imparts a front refractive profile and a back refractive profile to the lens 20. Although the diffractive profile may also be applied to either or both of the front face 21 and the back face 22, Figure 2B The posterior face 22 is shown having a diffraction profile. The diffraction profile is characterized by a plurality of annular diffraction regions or gratings 23 spaced about the optical axis 24. Although analytical optics theory generally assumes an infinite number of gratings, a standard multifocal diffractive IOL typically has at least 9 gratings and may have more than 30 gratings. For clarity, Figure 2B Only 4 gratings are shown. Typically, an IOL is biconvex, or possibly plano-convex or convexo-concave, but an IOL can be biplanar or have other combinations of refractive surfaces.

[0044] Figure 3A and Figure 3B is a graphical representation of a portion of a typical diffraction profile for a multifocal lens. Although the graph shows only 3 gratings, a typical diffractive lens extends to at least 9 gratings to over 32 gratings. Figure 3A In the figure, the surface relief profile of each point on the grating surface (from the plane perpendicular to the light rays) is plotted as a function of the square of the radial distance (r) relative to the optical axis of the lens (called r-squared space). 2 In a multifocal lens, each grating 23 may have a diameter or distance relative to the optical axis that is generally proportional to √n, where n is the number of gratings 23 counted from the optical axis 24. Each grating has a characteristic optical zone 30 and a transition zone 31. The optical zone 30 generally has a diameter such as Figure 3B However, the slope of each raster in r-squared space (e.g. Figure 3A As shown here, for a typical diffractive multifocal lens, all gratings have the same surface area. The area of grating 23 determines the diffractive power of lens 20, and as area and radius are related, the diffractive power is also related to the grating radius. The trailing edge of each grating is physically offset relative to the leading edge of the adjacent grating by the step height. An exemplary step height between adjacent gratings is Figure 3A Marked as reference number 33. The step height in r square space ( Figure 3A ) and linear space ( Figure 3B The step offset is the height offset of the transition area relative to the base arc below.

[0045] Diffractive profiles can be used to provide multifocality in lenses and can be used to correct chromatic aberration. Diffractive achromatic lenses that include diffractive profiles can be used with optical components to reduce chromatic aberration. For example, Figure 4 The diffraction profile of a diffractive achromatic lens is shown. The diffraction profile 400 of the diffractive achromatic lens is shown relative to the Y-axis 402, which represents the phase shift of the diffraction profile 400. The height is shown in millimeters (mm) and may represent the distance relative to the fundamental spherical wavefront generated by the lens. In other embodiments, other units or scales may be used. The height or phase shift of the diffraction profile 400 is shown relative to the radius from the optical axis 406 on the X-axis 404 in r-squared space. The radial coordinate represents the distance from the optical axis 406 in r-squared space and is shown in square millimeters, although in other embodiments, other units or scales may be used.

[0046] The diffraction profile 400 of the diffractive achromat comprises a repeating pattern of small steps (representative small steps 408a, 408b, and 408c are labeled), each of which has the same width in r-squared space. The step height of each small step in the diffraction profile 400 is also the same. Notably, the diffraction profile 400 of the diffractive achromat extends along the entire optic, extending outward from the optical axis 406 toward the outer periphery of the optic. The entire optic can have the same base curvature, which can be reduced throughout the optic to compensate for the added optical power of the diffractive achromat.

[0047] Figure 5 An embodiment of an optical element is shown that includes a central region 500 disposed about an optical axis 502 and having a peripheral region 504 extending outward from the central region 500. The central region 500 may lack an achromatic lens. A diffractive achromatic lens having a diffraction profile 506 may be positioned on the peripheral region 504 and may extend outward from the central region 500. The base optical power for distances from the central region 500 may be the same as the base optical power for distances from the peripheral region 504. With respect to the diffraction profile 506, the diffraction profile 506 is shown relative to a Y-axis 508, which represents the phase shift of the diffraction profile 506. The height is shown in millimeters (mm) and may represent the distance relative to the fundamental spherical wavefront generated by the lens. In other embodiments, other units or scales may be used. The height or phase shift of the diffraction profile 506 is shown relative to the radius from the optical axis 502 on the X-axis 510 in r-squared space. The radial coordinate represents the distance from the optical axis 502 in r-squared space and is shown in units of square millimeters, although in other embodiments other units or scales may be used.

[0048] The diffraction profile 506 of the diffractive achromatic lens can be Figure 4 The diffraction profile 400 shown is similarly configured and can include a plurality of small steps. The small steps can be repeated across the peripheral region 504 and can have the same width in terms of r-squared space and step height, but other configurations can be used in other embodiments. The diffraction profile 506 of the diffractive achromat can extend outward from the transition 512 with the central region 500 to the outer periphery of the optic. In other embodiments, the diffraction profile of the diffractive achromat can extend another radial distance as desired.

[0049] The central region 500 may include the portion of the optical component through which the optical axis 502 extends and may extend outward from the optical axis 502 to a desired radial distance. In certain embodiments, the distance may be up to about 1.4 mm or to a larger or smaller radius (e.g., 1 mm, 1.25 mm, 1.5 mm, 1.75 mm, 2 mm, etc.) as desired. The distance may be at least 1 mm, at least 1.5 mm, or at least 2 mm, as well as other smaller or larger distances. The central region 500 may be adjacent to the peripheral region 504. An achromatic lens, diffractive achromatic lens, or other diffractive profile is not located on the central region 500. The central region may be configured to correct for ocular aberrations of the patient's eye, including spherical optical aberrations, etc. A diffractive achromatic lens located on the peripheral region 504 may be configured to correct for longitudinal chromatic aberration.

[0050] The base curvature of the optic can be configured such that the base curvature of the central region 500 is greater than the base curvature of the peripheral region 504. The base curvature of the optic decreases at a transition 512 in a direction outward from the optical axis 502. The base curvature of the central region 500 can be greater than the base curvature of the peripheral region 504 so that the optic has the same base refractive power for distances spanning the central region 500 and the peripheral region 504, which includes the diffractive profile 506 of the diffractive achromat. The base refractive power for distances in the peripheral region 504 can include the distance refractive power of the diffractive achromat combined with the distance refractive power of the peripheral region 504. The base refractive power for distances of the optic can be the same from the optical axis 502 to the outer periphery of the optic.

[0051] The presence of central region 500 can account for the dilation and constriction of the patient's pupil to provide the desired optical effect. When the pupil is constricted and small, the radius of central region 500 can be set so that light only passes through central region 500 to reduce the possibility of glare or other adverse optical effects that may be caused by the diffractive achromatic lens. However, when the pupil is dilated and large, light can be provided on the diffractive achromatic lens to allow for greater color contrast (this may be at night when the need for color contrast is highest).

[0052] The central region 500 can be a refractive region. The base optical power for the distance of the central region 500 can be the refractive power. In other embodiments, the central region 500 can include an extended depth of focus diffractive region or utilize a bifocal, trifocal, or aperiodic design (or can be a refractive extended depth of focus region). The extended depth of focus or multifocal features (which can include a diffractive profile) can be applied to the central region 500 or the entire optic as desired.

[0053] Figure 6 A graph showing the over-frequency modulation transfer function (MTF) of an optic that does not include an achromatic lens is shown. The MTF is shown on the Y-axis 600 and the frequency is shown on the X-axis 602. Figure 7 A graph showing the through-band MTF of an optic including an achromatic lens along the entire optical surface is similar to Figure 4 The embodiment shown. The MTF is shown on the Y-axis 700 and the frequency is shown on the X-axis 702.

[0054] Figure 8 For example, Figure 5 A graph of the through-frequency MTF of an optic including a central region and including a diffractive achromatic lens on a peripheral region is shown. The MTF is shown on the Y-axis 800 and the frequency is shown on the X-axis 802. Figure 5 The MTF of the illustrated embodiment is shown to preserve most of the contrast gain. However, the reference Figure 9 and Figure 10 , which show the scattering (point spread function), Figure 5 The embodiment shown will have Figure 4 The illustrated embodiment has a lower incidence of visual symptoms.

[0055] Figure 9 The point spread function (PSF) is shown, where the PSF is shown on the Y-axis 900 and the angle is shown on the X-axis 902. The PSF is Figure 7 The embodiment shown. The cliff 904 in the outline indicates the risk of visual symptoms. Figure 10 Shown for Figure 8 Point spread function (PSF) of the embodiment shown, where PSF is shown on the Y-axis 1000 and angle is shown on the X-axis 1002. The presence of cliffs is reduced, indicating Figure 8 The embodiment shown is Figure 7 The embodiment shown has a lower risk of visual symptoms.

[0056] Optics for ophthalmic lenses comprising the profiles disclosed herein (profiles of the central region and / or profiles of diffractive achromatic lenses) can be manufactured using a variety of methods. One method can include determining optical aberrations of a patient's eye. Measurements of the patient's eye can be performed in a clinical setting, such as by an optometrist, ophthalmologist, or other medical or optical professional. Measurements can be performed using explicit refraction, autorefraction, tomography, or a combination of these methods or other measurement methods. Optical aberrations of the patient's eye can be determined. Physical properties of the patient's eye can also be measured, such as pupil size and the size of the pupil's dilation and constriction.

[0057] The measurements of the patient's eye can be placed into an ophthalmic lens prescription that includes features of the optics designed to account for the optical aberrations of the patient's eye, as well as features that account for the patient's pupil size (including both dilated and constricted sizes).

[0058] An ophthalmic lens prescription can be used to manufacture an optic for an ophthalmic lens. Based on the ophthalmic lens prescription, a refractive profile for the central region of the optic can be determined to correct for optical aberrations of the patient's eye. This refractive profile can be applied to the optic. A desired diffractive profile for a diffractive achromatic lens can also be determined. The optical power of the diffractive achromatic lens can be determined, and the base curvature of the peripheral region of the diffractive achromatic lens can be reduced so that the optic has the same base refractive power for distances in the central and peripheral regions. The patient's pupil size can be used to determine the size (radius) of the central region from the optical axis.

[0059] Determination of the profile of one or more of the central region or diffractive achromatic lenses and fabrication of the optic can be performed remotely from the optometrist, ophthalmologist, or other medical or optical professional performing the measurements of the patient's eye, or can be performed at the same clinical facility as such individual. If performed remotely, the fabricated optic can be delivered to the optometrist, ophthalmologist, or other medical or optical professional for provision to the patient. For intraocular lenses, the fabricated optic can be provided for implantation in the patient's eye.

[0060] The manufactured optic may be a custom optic made specifically for the patient's eye, or may be manufactured in a manufacturing assembly and then selected by an optometrist, ophthalmologist, or other medical or optical professional for provision to the patient, which may include implantation in the patient's eye.

[0061] Figure 11 An embodiment of a system 1100 is shown that can be used to perform all or part of the methods disclosed herein. The system 1100 can include a processor 1102, an input 1104, and a memory 1106. In certain embodiments, the system 1100 can include a manufacturing component 1108.

[0062] The processor 1102 may include a central processing unit (CPU) or other form of processor. In certain embodiments, the processor 1102 may include one or more processors. The processor 1102 may include one or more processors that are distributed in certain embodiments. For example, the processor 1102 may be located remotely from other components of the system 1100 or may be used in a cloud computing environment. The memory 1106 may include a memory that is readable by the processor 1102. The memory 1106 may store instructions or characteristics of the intraocular lens, or other parameters that may be used by the processor 1102 to execute the methods disclosed herein. The memory 1106 may include a hard disk, read-only memory (ROM), random access memory (RAM), or other form of non-transitory media for storing data. The input 1104 may include a port, terminal, physical input device, or other form of input. The port or terminal may include a physical port or terminal or an electronic port or terminal. In certain embodiments, the port may include a wired or wireless communication device. The physical input device may include a keyboard, touch screen, keypad, pointing device, or other form of physical input device. The input 1104 may be configured to provide input to the processor 1102.

[0063] System 1100 may be used to perform methods disclosed herein, such as a process of determining a profile of one or more of a central region or a diffractive achromatic lens.

[0064] Processor 1102 can provide the profile of one or more of the central region or the diffractive achromatic lens to a manufacturing component 1108, which can be configured to manufacture an optic for an ophthalmic lens based on the profile of the central region or the diffractive achromatic lens. Manufacturing component 1108 can include one or more devices for forming the optic and can include a high-volume manufacturing component or a low-volume manufacturing component. Manufacturing component 1108 can be used for manufacturing away from the clinic where the individual eye measurements are taken, or for manufacturing locally at such a clinic. Manufacturing components can include equipment such as lathe tools or other lens forming devices to manufacture the optic.

[0065] In one embodiment, the processor 1102 may be provided with an ophthalmic lens prescription for an individual's eye, which may be provided as discussed herein. The processor 1102 may receive the ophthalmic lens via an input 1104. The system 1100 may manufacture an optic for the ophthalmic lens based on the prescription.

[0066] The system 1100 may be configured to manufacture any embodiment of the ophthalmic lenses disclosed herein.

[0067] In one embodiment, Figure 5The profile shown can be located on the surface of the lens opposite the aspheric surface.The aspheric surface on the opposite side of the lens can be designed to reduce the patient's corneal spherical aberration.

[0068] In one embodiment, one or both surfaces of the lens may be aspheric, or include a refractive surface designed to extend the depth of focus or create multifocality.

[0069] Any of the embodiments of lens profiles discussed herein can be apodized to produce the desired result.Apodization can cause the step heights and step offsets of the grating to gradually change according to the apodization so as to gradually increase the amount of light in the afar focus as a function of pupil diameter.

[0070] The features of the optics disclosed herein can be used alone or in combination with the refractive profile of the optic and / or with other features that provide correction for chromatic aberration.

[0071] The ophthalmic lenses disclosed herein in the form of intraocular lenses are not limited to lenses placed in the capsular bag of an individual. For example, intraocular lenses may include those positioned within the anterior chamber of the eye. In certain embodiments, the intraocular lenses may include "piggyback" lenses or other forms of supplemental intraocular lenses.

[0072] The features of the embodiments may be modified, replaced, eliminated or combined as desired.

[0073] Furthermore, the methods herein are not limited to the specifically described methods and may include methods utilizing the systems and apparatus disclosed herein.

[0074] Finally, it should be understood that although various aspects of this specification have been highlighted with reference to specific embodiments, it will be readily understood by those skilled in the art that these disclosed embodiments are merely illustrative of the principles of the subject matter disclosed herein. Therefore, it should be understood that the disclosed subject matter is by no means limited to the specific methods, schemes, and / or reagents described herein. Therefore, various modifications or changes or alternative configurations may be made to the disclosed subject matter according to the teachings herein without departing from the essence of this specification. Finally, the terms used herein are only used for the purpose of describing specific embodiments and are not intended to limit the scope of the systems, devices, and methods disclosed herein, which scope is limited only by the claims. Therefore, the systems, devices, and methods are not limited to precisely as shown and described.

[0075] Certain embodiments of systems, devices, and methods are described herein, including the best modes known to the inventors for carrying out these embodiments. Of course, after reading the above description, variations of these described embodiments will become apparent to those of ordinary skill in the art. The inventors expect that those skilled in the art will appropriately adopt such variations, and the inventors intend to practice systems, devices, and methods in a manner different from that specifically described herein. Therefore, as permitted by applicable law, systems, devices, and methods include all modifications and equivalents of the subject matter described in the appended claims. In addition, unless otherwise specified herein or clearly contradicted by the context, any combination of all possible variations of the above-described embodiments is encompassed within the systems, devices, and methods.

[0076] The grouping of alternative embodiments, elements or steps of the systems, devices and methods should not be construed as limiting. Each group member may be referred to and claimed individually or in any combination with other group members disclosed herein. For reasons of convenience and / or patentability, it is contemplated that one or more members of a group may be included in or deleted from the group. When any such inclusion or deletion occurs, the specification is deemed to contain the modified group and therefore satisfies the written description of all Markush groups used in the appended claims.

[0077] Unless otherwise indicated herein or clearly contradicted by context, the terms "a", "an", "the / said" and similar referents used in the context of describing systems, devices and methods (especially in the context of the following claims) should be interpreted to cover both the singular and the plural. Unless otherwise indicated herein or clearly contradicted by context, all methods described herein can be performed in any suitable order. The use of any and all examples or exemplary language (e.g., "such as") provided herein is intended only to better illustrate the systems, devices and methods and does not constitute a limitation on the scope of the otherwise claimed systems, devices and methods. No language in the specification should be interpreted to indicate that any element not protected by the claims is necessary to implement the systems, devices and methods.

[0078] All patents, patent publications, and other publications cited and identified in this specification are individually and expressly incorporated herein by reference in their entirety for the purpose of describing and disclosing, for example, the compositions and methods described in such publications that can be used in conjunction with the systems, devices, and methods. These publications are provided solely for their disclosure prior to the filing date of the present application. Nothing herein should be construed as an admission that the inventors are not entitled to antedate such disclosure by virtue of prior invention or for any other reason. All statements regarding the dates or contents of these documents are based on the information available to the applicants and do not constitute an admission as to the correctness of the dates or contents of these documents.

Claims

1. An ophthalmic lens comprising: An optical element having a central region disposed about an optical axis and a peripheral region extending outward from the central region, wherein a diffractive achromat lens is positioned on the peripheral region and is configured to correct longitudinal chromatic aberration, and wherein the central region lacks an achromat lens, and wherein a base refractive power for distances in the central region is the same as a base refractive power for distances in the peripheral region, and wherein a portion of the peripheral region on which the diffractive achromat lens is positioned has a base curvature that is less than a base curvature of the central region.

2. The ophthalmic lens according to claim 1, wherein The optic includes a transition portion between the central region and the peripheral region, where a base curvature of the optic changes.

3. The ophthalmic lens according to claim 1, wherein The central area is adjacent to the peripheral area.

4. The ophthalmic lens according to claim 1, wherein The base optical power for the distance of the peripheral region comprises the distance optical power of the diffractive achromatic lens combined with the distance optical power of the peripheral region.

5. The ophthalmic lens according to claim 1, wherein The optic extends outwardly from the optical axis to an outer periphery of the optic, and a base optical power for a distance of the optic is the same from the optical axis to the outer periphery of the optic.

6. The ophthalmic lens according to claim 1, wherein The base optical power for the distance of the central area is the refractive power.

7. The ophthalmic lens according to claim 1, wherein: The central region is a refractive region.

8. The ophthalmic lens according to claim 1, wherein The central region extends outwardly from the optical axis to a radius of at least 1 mm.

9. The ophthalmic lens according to claim 1, wherein: The central region extends outwardly from the optical axis to a radius of at least 1.5 mm.

10. The ophthalmic lens according to claim 1, wherein The central region extends outwardly from the optical axis to a radius of at least 2 mm.

11. A method comprising: An optic is manufactured for an ophthalmic lens, the optic having a central region disposed about an optical axis and a peripheral region extending outward from the central region, wherein a diffractive achromat is positioned on the peripheral region and is configured to correct longitudinal chromatic aberration, and the central region lacks an achromat, and wherein a base refractive power for distances in the central region is the same as a base refractive power for distances in the peripheral region, and wherein a portion of the peripheral region on which the diffractive achromat is positioned has a base curvature that is less than a base curvature of the central region.

12. The method of claim 11, further comprising receiving an ophthalmic lens prescription, and manufacturing the optic based on the ophthalmic lens prescription.

13. The method of claim 12, further comprising determining a profile of one or more of the central region or the diffractive achromatic lens based on the ophthalmic lens prescription.

14. The method according to claim 11, wherein The base optical power for the distance of the peripheral region comprises the distance optical power of the diffractive achromatic lens combined with the distance optical power of the peripheral region.

15. The method according to claim 11, wherein The central region is a refractive region.

16. A system for manufacturing an ophthalmic lens, the system comprising: a processor configured to determine at least a portion of a profile of an optical member having a central region disposed about an optical axis and a peripheral region extending outward from the central region, wherein a diffractive achromat is positioned on the peripheral region and is configured to correct longitudinal chromatic aberration, and wherein the central region lacks an achromat, and wherein a base optical power for distances in the central region is the same as a base optical power for distances in the peripheral region, and wherein a portion of the peripheral region on which the diffractive achromat is positioned has a base curvature that is less than a base curvature of the central region; as well as A manufacturing assembly is provided to manufacture the optical component based on the profile.

17. The system of claim 16, further comprising an input for receiving an ophthalmic lens prescription, and wherein the processor is configured to determine a profile of one or more of the central region or the diffractive achromatic lens based on the ophthalmic lens prescription.

18. The system according to claim 16, wherein: The base optical power for the distance of the peripheral region comprises the distance optical power of the diffractive achromatic lens combined with the distance optical power of the peripheral region.

19. The system according to claim 16, wherein: The central region is a refractive region.

20. The system of claim 16, wherein: The optic extends outwardly from the optical axis to an outer periphery of the optic, and a base optical power for a distance of the optic is the same from the optical axis to the outer periphery of the optic.

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