Optimization of high-resolution and extended depth-of-field intraocular lenses

Abstract

Disclosed are configurations of lenses that are optimized, enhanced, or improved for a desired extended depth of focus, extended depth of field, or other properties of the lens. The disclosed systems and methods enable the selection of lens parameters such as optic zone diameter, radius of curvature, conic constant, and alpha coefficient to maximize or enhance one or more properties of the lens.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS

[0001] This application claims priority to U.S. patent application Ser. No. 63 / 330,590, filed April 13, 2022, Ser. No. 63 / 340,617, filed May 11, 2022, and Ser. No. 63 / 425,587, filed November 15, 2022, entitled "Optimization of High Resolution and Extended Depth Intraocular Lenses," the contents of which are incorporated by reference in their entireties herein. [Background technology]

[0002] Conventional optical lens solutions for extending depth of focus while eliminating common drawbacks include diffractive and refractive multifocal lenses with discrete zones. Other conventional solutions include aspheric lenses with a power profile that varies along the diameter of the lens. For aspheric lens shapes, the degree to which the power varies along the diameter is set by varying the conic constant K and the nth order aspheric coefficient term.

[0003] Such technology has its drawbacks. For example, in the case of intraocular lenses (IOLs), the placement of discrete zones is sensitive to pupil size. When a particular power zone is exposed by a dilated pupil or covered by a constricted pupil, the power of the IOL changes dramatically. In another example, multi-zone configurations, by definition, introduce unwanted visual artifacts such as halation. One zone may be in good focus for an object at a certain distance, while the other zones are not in perfect focus. This results in multiple images and halation around the primary object. Furthermore, with fewer zones, the halation is more noticeable and distinct.

[0004] What is needed is a lens configuration that mitigates or eliminates the aforementioned shortcomings. Summary of the Invention

[0005] Disclosed herein are solutions for constructing intraocular lenses that are optimized, enhanced, or improved for a desired extended depth of focus, extended depth of field, or other properties of the intraocular lens. The disclosed systems and methods allow for the selection of lens parameters such as the diameter of the optical zone, the radius of curvature, the conic constant, and the alpha coefficient to maximize or enhance the desired properties. Examples of properties that may be optimized or enhanced include depth of focus, minimizing poor performance (less than 20 / 20) zones, and ensuring robust operation against decentering, tilt, off axis light sources, implantation errors during surgery, and intraocular lens power selection errors.

[0006] The details of one or more variations of the subject matter described herein are set forth in the accompanying drawings and the description below. 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]

[0007] [Figure 1A] Diagram showing the basic method of using myopic eye pupil size to reduce monochromatic aberrations and increase or extend depth of field. [Figure 1B] Diagram showing the basic method of using myopic eye pupil size to reduce monochromatic aberrations and increase or extend depth of field. [Figure 2A] A diagram showing the basic method of using the pupil size of a hyperopic eye to reduce monochromatic aberrations and increase depth of field. [Figure 2B] A diagram showing the basic method of using the pupil size of a hyperopic eye to reduce monochromatic aberrations and increase depth of field. [Figure 3A] Diagram showing the basic method of using emmetropic pupil size to reduce monochromatic aberrations and increase depth of field. [Figure 3B] Diagram showing the basic method of using emmetropic pupil size to reduce monochromatic aberrations and increase depth of field. [Figure 4A] Diagram showing the basic method of using pupil size to reduce chromatic aberration. [Figure 4B]Diagram showing the basic method of using pupil size to reduce chromatic aberration. [Figure 5A] FIG. 1 illustrates the basic concept of a virtual aperture for limiting the effective pupil size. [Figure 5B] FIG. 1 illustrates the basic concept of a virtual aperture for limiting the effective pupil size. [Figure 6A] FIG. 1 is a diagram showing the overall structure of an example of an intraocular lens. [Figure 6B] FIG. 1 is a diagram showing the overall structure of an example of an intraocular lens. [Figure 6C] FIG. 1 is a diagram showing the overall structure of an example of an intraocular lens. [Figure 6D] FIG. 13 illustrates another embodiment of an intraocular lens. [Figure 7] FIG. 1 illustrates an example of an intraocular lens with hexagonal sampled microlenses in the virtual aperture zone. [Figure 8] FIG. 1 illustrates an example partitioning of the optical zone of an intraocular lens to provide both myopic and hyperopic partitioning. [Figure 9] 1 is a diagram of a system for modifying a sub-surface region of an intraocular lens. [Figure 10] 1 is a diagram of a system for modifying a sub-surface region of an intraocular lens. [Figure 11] 1 is a diagram of a system for modifying a sub-surface region of an intraocular lens. [Figure 12] FIG. 1 illustrates a computer system. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0008] Before further describing the subject matter, it should be understood that the subject matter described herein is not limited to the particular embodiments described, as they may, of course, vary. It should also be understood that the terms used herein are for the purpose of describing particular embodiments only, and are not intended to be limiting. Unless otherwise defined, all technical terms used herein shall have the same meaning as commonly understood by those skilled in the art to which the subject matter belongs.

[0009] Disclosed herein are solutions for constructing an intraocular lens that are optimized, enhanced, or improved for desired intraocular lens properties. The disclosed systems and methods allow for the selection of lens parameters (or parameters of the equations that define the lens), such as optical zone diameter, radius of curvature, conic constant, alpha coefficient, and / or polynomial coefficients, to maximize or enhance desired properties. Examples of properties that may be optimized or enhanced include depth of focus, minimizing poor performance (less than 20 / 20) zones, and ensuring robust operation against decentering, tilt, off axis light sources, implantation errors during surgery, and intraocular lens power selection errors.

[0010] Further disclosed are systems, devices, and methods that overcome at least the limitations of intraocular lenses by providing a phakic or aphakic intraocular lens that provides correction of defocus and astigmatism, reduces higher order monochromatic and chromatic aberrations, and provides extended depth of field to improve quality of vision. The disclosed intraocular lens is sometimes referred to herein as a Z+ optic or Z+ intraocular lens. Related systems and methods are described in U.S. Patent No. 10,285,807, U.S. Patent Application No. 16 / 380622, and PCT Application No. PCT / US20 / 37014, and are incorporated herein by reference in their entireties.

[0011] Here we will explain the basic principles used to reduce monochromatic and chromatic aberrations and increase depth of field. Figure 1A shows a schematic of a single converging lens 1 centered on an optical axis 2. An incident ray 3 from a distant object is parallel to the optical axis and intersects with the focal point 4 of the lens (labeled b, c, d, e, f according to the corresponding figures). If the lens power is properly selected, the focal point will coincide with the observation plane 5, otherwise there will be a mismatch between the lens power and the position of the observation plane and the focal point will be located in front of or behind the observation plane.

[0012] In FIG. 1A, the focal point is in front of the observation plane. If all incident rays are traced with the same ray height as incident ray 3, a blur circle 6 is located on the observation plane 5. The observation plane is oriented perpendicular to the optical axis, so it is shown as a vertical line in the figure. Although the blur circles 6 and 8 are shown on the plane of the figure for visibility, the blur circle is actually on the observation plane. Other parallel incident rays with a lower ray height than incident ray 3 fall inside this blur circle 6. One such ray is parallel incident ray 7, which is closer to the optical axis than incident ray 3. Incident ray 7 also intersects with focal point 4 and then with observation plane 5. If all incident rays with a ray height equal to incident ray 7 are traced, a blur circle 8 with a smaller diameter than blur circle 6 is drawn.

[0013] FIG. 1B shows the same optical system as FIG. 1A, but now the incident rays are for objects closer to the optical system, as indicated by the gradient of the incident rays 3b, 7b. This causes the focal point 4 (with subscripts b, c, d, e, f based on the corresponding figure) for the closer object to be closer to the observation plane, and both blur circles 6b and 8b are smaller than their counterparts in FIG. 1A, but the principle is the same. That is, rays intersecting the lens 1 closer to the optical axis will constitute smaller blur circles on the observation plane. Relating this simple optical structure of FIG. 1 to the human eye, the converging lens 1 represents the main plane of the eye's optical system, including the cornea and the crystalline lens or intraocular lens. The observation plane 5 represents the retina. Since the focal point 4 is in front of the observation plane (retina), this figure is for a myopic eye. The size of the blur circles 6, 8 (or 6b, 8b) represents the amount of defocus on the retina, and the smaller the diameter of the blur circle, the clearer the vision.

[0014] It should be noted that the same relationship between the height of the incident ray and the size of the blur circle also holds for hyperopic or far-sighted eyes. This is shown diagrammatically in Figures 2A and 2B, which show rays corresponding to a hyperopic eye. The lower the ray height, the smaller the blur circle on the retina (observation surface) for rays 3 and 7 from a distant object in Figure 2A, and for rays 3b and 7b in Figure 2B.

[0015] Similarly, Figures 3A and 3B (collectively Figure 3) show that the same parallel ray height and blur circle diameter characteristics hold for an emmetropic eye. For distant objects, the focus 4e is on the retina (because the eye is emmetropic), and the radii of the blur circles 6e and 8e are zero. For near objects, the focus 4f is behind the retina, and the blur circle 8f corresponding to the ray 7b closer to the optical axis has a smaller diameter than the blur circle 6f corresponding to the ray 3b farther from the optical axis.

[0016] In general, the eye has aberrations, and when the position of the incident light ray changes, the focal position of the eye also changes. However, regardless of the focal position (in front of the retina, on the retina, or behind the retina), the diameter of the blur circle on the retina decreases as the height of the incident light ray decreases. In other words, for a given amount of eye focus misalignment (refractive error), visual acuity improves as the height of the incident light ray decreases. This principle is used when we squint our eyes and block the incident light ray far from the optical axis of the eyeball with our eyelids in order to see out-of-focus distant or nearby objects more clearly.

[0017] The ray tracing shown in Figures 1A-3B is for a single wavelength of incident light. In the case of polychromatic light, multiple wavelengths are present. This is commonly represented by three rays of different wavelengths as shown in Figures 4A and 4B (collectively referred to as Figure 4). It is well known that the refractive index of components of the eye and typical optical materials decreases as the wavelength of light increases.

[0018] In FIG. 4A, a converging lens 21 has an optical axis 22. The incoming colored light rays 23 are composed of three wavelengths, blue (450 nm), green (550 nm), and red (650 nm), spanning almost the visible light range. Due to the different refractive indices of the three wavelengths, the blue light ray 24 is refracted more than the green light ray 25, and the green light ray is refracted more than the red light ray 26. When the green light ray is in focus, it intersects the viewing plane 27 at the optical axis. The color spread of these three light rays results in a chromatic blur 28 on the viewing plane.

[0019] In FIG. 4B, the incident color rays 29 have a lower ray height than the color rays 23 in FIG. 4A. This results in less chromatic aberration blur 33 at the observation plane. Thus, similar to the monochromatic blur in FIGS. 1A-3B, the lower the height of the color rays, the less chromatic aberration blur. The situation in FIG. 4 can be related to the eye by considering the converging lens 21 as the eye's principal plane and the observation plane 27 as the retina. Since the human eye typically has a large chromatic aberration (about 1.0-1.2 diopters in the central optical zone), a reduction in chromatic aberration is significant leading to a noticeable improvement in the eye's visual quality, especially as measured by contrast sensitivity.

[0020] Taken together, Figures 1A-4B show that by decreasing the beam height, both monochromatic and chromatic aberrations at the retina are reduced, improving the quality of vision. This can be accomplished by reducing the pupil diameter to block rays that are a large distance from the optical axis, or by spreading the light from these rays evenly and / or widely across the retina, so that more aberrated rays contribute much less light to the central blur circle on the retina. Another feature of this effect is that the depth of field increases as the beam height decreases, as shown in Figures 1B, 2B, and 3B.

[0021] Figure 5A shows a converging lens 34 with an optical axis 2 and a stop 35. An incident parallel ray 36 passes just through the stop, passes through the lens focal point 37, and intersects with an observation plane 38. All parallel rays at the same height as ray 36 will cause a small blur circle 39 on the observation plane. An incident parallel ray 40 is blocked by the stop and cannot continue to the observation plane and cause a larger blur circle 41. Thus, a stop that reduces the height of the incident ray will reduce the diameter of the blur circle on the observation plane.

[0022] FIG. 5B shows a "virtual aperture" i.e., it is not actually an aperture that blocks light rays, but the optical effect on central vision is approximately the same. In this figure, a bundle of light rays 40b incident on the virtual aperture propagates through the virtual aperture 42, resulting in a wide spread of light rays 43 with little stray light (blurred light) contribution at any one point on the viewing surface, by refraction, diffraction, scattering, reflection, and / or diffusion. This is the main working mechanism of the disclosed intraocular lens. The virtual aperture can be achieved via a structure added or placed on the intraocular lens, such as a surface modification, a sub-surface modification, or a mask structure. For example, the mask structure can be a ring-like structure or any ring-like mask that blocks at least a portion of the light passing through the intraocular lens.

[0023] Example of intraocular lens optical layout

[0024] 6A-6C show exemplary intraocular lens layouts employing optical principles to achieve the benefits of reduced monochromatic and chromatic aberrations and increased depth of field. FIG. 6A shows a front view of the intraocular lens, which may be a front view. FIG. 6B shows a rear view of the intraocular lens, which may be a rear view. FIG. 6C shows a side view of the intraocular lens. The intraocular lens includes a central optical zone 46 (having a back surface 46b) that provides other corrections required for the lens, such as defocus, astigmatism, and spherical aberration. In general, for intraocular lenses using a virtual aperture, the diameter of the central optical zone is smaller than that of a conventional intraocular lens. As a result, the thickness of the central portion is reduced, making it easier to implant the intraocular lens, and the corneal incision during surgery can be as small as 2.2 mm. The central optical zone can achieve various light transmittances.

[0025] The intraocular lens includes a virtual aperture 48 located further circumferentially outward relative to the central location of the central optical zone 46. At least one intraocular lens haptic 50 (having a back surface 50b) is located on the intraocular lens circumferentially outward from the virtual aperture 48. The haptic 50 can be formed of one or more arms that extend circumferentially outward to define the innermost periphery of the intraocular lens. In one example, the optical zone has a diameter of 1.5 mm. The haptic 50 may define the outermost peripheral region of the intraocular lens. A first plurality of light rays incident on the anterior optical surface of the optical zone can pass through the optical zone to form an image on the retina when the intraocular lens is placed in the eye. Meanwhile, a second plurality of light rays incident on the anterior virtual aperture surface are widely dispersed downstream from the intraocular lens toward the retina, such that the image includes an extended depth of field, and the virtual aperture further reduces monochromatic and chromatic aberrations of the image. The optical zone includes at least one of a bifocal optic, a trifocal optic, and a multifocal optic.

[0026] The virtual aperture is connected to the optical zone 46 by an optional first transition region 47 located at the periphery of the optical zone 46, which is located at the periphery of the optical zone, so that the virtual aperture is a first peripheral region surrounding or partially surrounding the optical zone. The haptics can form a second peripheral region for placing the intraocular lens in the eye. The first transition region is located at the outer periphery of the optical zone 46. An optional second transition region 49 connects the haptics 50 to the virtual aperture 48. The first transition region 47 and the second transition region 49 are configured to ensure zero-order and first-order continuity of the outer surface of the intraocular lens on either side of the respective transition region. A common method for implementing these transition regions is a polynomial function, such as a cubic Bezier function. Such transition methods are known to those skilled in the art. On the back side of the intraocular lens, there is a central optical zone 46b, haptics 50b, and a transition region 47b between them. 6A-6C are not necessarily to scale, and the haptic shapes are for illustration purposes. Other haptic shapes and sizes known to those of skill in the art are similarly suitable. The first and second transition regions are not necessarily present in the intraocular lens per se.

[0027] The intraocular lens has an anterior surface and a posterior surface. The components of the intraocular lens, including the optical zone 46, the first transition region 47, the second transition region 49, the virtual aperture 48, and the haptics 50, may each have an anterior surface and a posterior surface. The optical zone 46 has an anterior optical surface that may include at least one multifocal zone and / or a toric region. At least a portion or region of the anterior and / or posterior surface, such as a region of the virtual aperture or other portions of the intraocular lens, may have a surface profile or shape that achieves a desired or predetermined effect on the light passing therethrough. In a non-limiting example, the surface profile of the anterior and / or posterior surface includes a region having a ripple-type profile, such as a wave or undulating shape that forms a series of ascending and descending surfaces. The surface profile can achieve various effects on the light passing through the intraocular lens. For example, the surface profile can achieve a wide or relatively wide spread of stray light depending on the type of surface profile used. The surface profile can be used to achieve a spread of stray light that is directed away from the focal point of the retina.

[0028] 6D is a front view of another embodiment of an intraocular lens that includes a central optic zone, a plurality of peripheral haptics 605, and at least one zone having a ripple or wave-like surface profile as described further below. In one example, the optic zone has a diameter of 1.5 mm and functions as a lens to bring distant objects into sharp focus on the central retina.

[0029] The intraocular lens includes one or more orientation structures 610, such as one or more protuberances or bumps. In the illustrated embodiment, the orientation structures 610 are disposed on a portion of the periphery of the intraocular lens, with at least one orientation structure 610 on a first side of the vertical meridian of the intraocular lens and a second orientation structure 610 on a second side of the vertical meridian. The vertical meridian is shown in FIG. 6D by a dashed line. The orientation structures 610 are configured to allow a clinician, such as a surgeon, to easily detect that the intraocular lens has the correct side facing the front of the eye. It should be noted that when the intraocular lens is oriented with its back side facing the front of the eye, the orientation structures 610 are counterclockwise with respect to the vertical direction of the lens.

[0030] As described, the haptics 605 provide a mechanical interface with the eye and hold the various zones of the intraocular lens in the proper position relative to the eye.

[0031] Optical Zone Detail Example - Hexagonal Microlens Virtual Aperture

[0032] 7 illustrates a front view of an intraocular lens including a virtual aperture having one or more hexagonal structures. The intraocular lens has a central optical zone 709, a first transition zone 710, a hexagonal microlens virtual aperture 711, a second transition zone 712, and haptics 713. The first transition zone 710 connects the central optical zone 709 to the hexagonal microlens virtual aperture 711, and the second transition zone 712 connects the hexagonal microlens virtual aperture 711 to the haptics 713.

[0033] The virtual aperture employs a two-dimensional hexagonal sampling array of microlenses that mimics the photosensor sampling of the retina, a layout that is beneficial for spreading light widely across the retina when the intraocular lens is inserted into the eye.

[0034] The hexagonal microlens virtual aperture 711 includes a plurality of hexagonal shaped microstructures disposed on the anterior and / or posterior surface of the intraocular lens. The hexagonal shape with respect to the outer boundary of each hexagonal microstructure has an outer boundary defined by the hexagonal microstructure when viewed from the anterior or posterior of the intraocular lens. That is, the hexagonal microstructure may have an outer boundary defined by a hexagon. A small lens is disposed inside the boundary of each hexagonal microstructure. The lens may be a structure disposed on or within the microstructure. The lens may also be integrally formed as part of the microstructure during manufacturing. To prevent unwanted light patterns on the retina, the centers of the microlenses within each hexagon are randomly moved or positioned on the intraocular lens, and the radius of the microlenses is also adjusted. To facilitate the manufacturing of the hexagonal microlens virtual aperture, a blend region or fillet is disposed between the hexagonal boundaries of the microlenses, the blend region or fillet having a radius of curvature larger than the radius of the lathe cutter forming the microlenses. This radius is on the order of 0.05 mm in a non-limiting example.

[0035] The hexagons can have a variety of dimensions. In one embodiment, the hexagons of the microstructure are taller than they are wide. In another embodiment, the hexagons of the microstructure are wider than they are tall. In another embodiment, the outer boundary of the microstructure is a polygon of any shape.

[0036] With further reference to FIG. 7, the first transition zone 710 is configured to provide a smooth structural connection between the edge of the optical zone 709 and the central hexagonal microlens region 711. The second transition zone 712 is responsible for providing a smooth structural connection between the peripheral hexagonal microlens region 711 and the haptics 713. These transition zones can be effectively achieved using Bezier curves or portions of Bezier surfaces to define the surfaces of the respective zones. Other transition functions are similarly suitable and known to those skilled in the art. It should be noted that any of the embodiments of intraocular lenses described herein may be configured to not include a transition zone. In one embodiment, the system does not have the first transition zone 710 or the second transition zone. In another embodiment, the system has only one of the first transition zone or the second transition zone.

[0037] The microlenses are implemented as one or more surfaces defined at least in part by a sphere, conicoid, or other similar surface that can achieve high optical power to spread incident light widely across the retina. For example, the microlenses are implemented as one or more surfaces defined at least in part by a prism or pyramidal shape. As an example, in the following discussion, an embodiment with spherical microlenses is illustrated.

[0038] Multi-area Optical Zones

[0039] FIG. 8 illustrates generally a multi-region, such as two-region, optical zone 1101 that may be included in any intraocular lens described herein. The regions are indicated at 1109 and 1110. These represent two different regions of the optical zone for two different powers. For example, a first discrete region is a central region 1109, typically for providing far vision. A second discrete region is a peripheral region 1110, typically for providing near vision. The "add" of the near vision region is around 3.0D, ranging from 2.0-3.5D.

[0040] Due to the peculiarities of the optical mechanism of action of intraocular lenses, providing a bifocal optical zone is not as problematic as a normal-sized optical zone of 5.0 mm or more, because the extra aberrations caused by incident rays outside the central optical zone diameter, usually 1.5 mm, are distributed widely over the retina so as not to adversely affect the central vision of the eye.

[0041] In an exemplary configuration, the central optical zone distance power area occupies 75% of the optical zone area and the central optical zone near power area occupies 25% of the optical zone area. The central optical zone is typically 1.5 mm in diameter, so the central area 1109 of the optical zone has a diameter of 1.3 mm, leaving 25% of the optical zone as the near vision area 1110.

[0042] For some eyes, a distribution of distance and near zone areas of 50% each, or 25% distance and 75% near, may be preferred. Giving one eye the majority of the optical zone area for distance, such as 75-100%, and the other eye more optical zone area for myopia, may be used in extended depth of focus / monocular vision patients. In this case, both eyes have extended depth of focus, but one eye (usually the dominant eye) has slightly better distance performance and the other eye has slightly better myopic performance.

[0043] To provide the desired optical power in the optical zone region, a conical refractive profile can be used or a diffractive profile can be used.

[0044] For simple conic refractive profiles, each optical zone provides its optical power via a conic section, so that the apex radius of curvature provides the desired optical power and the conicity (K) value is set to reduce spherical aberration in that region. The optimization to determine the apex radius and conicity can be performed numerically using a commercially available optical design program such as Zemax, or using closed-form analytical equations. Both of these methods are known to those skilled in the art. Additionally, the conicity value can be adjusted to further enhance the depth of field performance of the intraocular lens. A conicity value in the range of -7.5 to -9.5, typically -8.717, provides such an enhancement for an equivalent biconvex conic optical zone.

[0045] When a simple conic refractive profile is used, with the central region 9 of the optical zone providing distance vision and the peripheral region 10 providing near vision, there is negligible transition between the regions. Generally, this is the preferred arrangement, since the transition region introduces stray light that would otherwise be properly focused by one of the two optical power regions.

[0046] When a simple conic refractive profile is used, with the central region 9 of the optical zone providing near vision and the peripheral region 10 providing far vision, a transition between the regions is required to smoothly connect the regions. This transition profile is typically implemented by either a Bezier curve or a circular fillet, both of which are known to those skilled in the art.

[0047] Subsurface correction of intraocular lenses

[0048] In an embodiment, at least one region of the intraocular lens, such as the virtual aperture 48 of the intraocular lens, includes at least one sub-surface modification that includes a modification to at least a portion of the internal structure of the intraocular lens. The intraocular lens may include such sub-surface modifications as well as any external surface features on the anterior and / or posterior surfaces of the intraocular lens, such as shape changes or contours on the external surface. The sub-surface modifications are configured to achieve a desired optical effect on light passing therethrough or otherwise interacting with the sub-surface modifications, such as, for example, diffusing the light, homogenizing the light, or redirecting the light. The sub-surface modifications of the intraocular lens provide an alternative, efficient, and reproducible mechanism for at least one region of the intraocular lens to diffuse and homogenize the light passing therethrough. The degree or level of diffusion and homogenization can be tailored to specific requirements by varying the size of the laser damage spot or loci of modified refractive index, as described below. The spacing or density of the placement of the damage spots or loci can be varied, as can the amount of layers of such damage spots or loci, to achieve a desired level of light diffusion. The configuration of the damage spot or track can also be used to achieve light direction control, such as directing light in a desired direction, allowing fine tuning and customization of the optical properties of intraocular lenses or light diffusing devices.

[0049] In one embodiment, the subsurface modifications are not located at the virtual aperture, but rather are part of an optical correction region of the intraocular lens, which may or may not be in the virtual aperture 48 region of the intraocular lens. In another embodiment, the subsurface modifications form a light diffusing region of the intraocular lens, or an optically transparent body or structure that is not an intraocular lens. For example, the features described herein can be used in light diffusing devices that are not intraocular lenses.

[0050] In a first exemplary embodiment of sub-surface modification, a laser is configured to interact with an interior region (i.e., a sub-surface region or location) of the intraocular lens to achieve a sub-surface modification, such as modifying a structure of the intraocular lens at the sub-surface location. The sub-surface region is located between at least an anterior surface and a posterior surface of the intraocular lens. In one example, a laser is focused on the sub-surface of the intraocular lens to heat the material of the intraocular lens and form a damage region or damage spot in the material of the intraocular lens at the sub-surface of the intraocular lens.

[0051] 9 illustrates generally a laser system 1205 configured to interact with an intraocular lens 1210 (or with a portion or body of material that is subsequently formed or otherwise incorporated into the intraocular lens 1210, or that forms a non-intraocular device, such as a light diffusing device). The laser system 1205 is configured to emit a laser 1220 that interacts with the intraocular lens (e.g., a laser 1220 that focuses or otherwise emits a predetermined amount of energy at a sub-surface location of the intraocular lens 1210).

[0052] The laser system 1205 is configured to emit a laser 1220 such that the laser 1220 is focused or configured to emit a predetermined level of energy at a sub-surface of the intraocular lens material (non-limiting examples include glass and polymeric materials). In one embodiment, the laser is pulsed at a high rate. The laser 1220 creates one or more micro-damage spots within the intraocular lens material (below the outer surface or between the anterior and posterior surfaces). In an exemplary embodiment, the pulsed laser causes rapid heating and expansion of the material in the vicinity of the focused laser spot, which creates stresses and small-scale fractures and gas expansions in the material, thereby creating the damage spots. The resulting fracture or damage spots are of extremely small dimensions (on the order of tens of microns).

[0053] The laser can be moved rapidly and precisely in the lateral X / Y directions while being focused to a specific depth within the material relative to the front or rear exterior surface. A pattern or array of such damage spots can be created at that depth. Furthermore, two or more layers of such damage spots can be created. The depth of the laser focus spot is precisely and rapidly controlled with micron depth resolution.

[0054] In this manner, the laser forms a two-dimensional or three-dimensional array of damage spots that can be arranged in any of a wide variety of patterns. A two-dimensional array includes two or more damage spots arranged in a common plane. A three-dimensional array includes two or more two-dimensional arrays. FIG. 10 is a schematic diagram of a portion of an intraocular lens 1210. It should be understood that the portion of the intraocular lens 1210 in FIG. 10 is depicted as a prismatic shape, although the shape may vary. A two-dimensional or three-dimensional array of damage spots 1305 is generally disposed beneath the outer surface of the intraocular lens 1210. The array includes one or more damage spots. In the illustrated embodiment, the damage spots form a rectangular array of equidistant damage spots, although the shape and spatial arrangement of the array, as well as the damage spots within the array, may vary.

[0055] In one example of a manufacturing process for an intraocular lens, the following steps may be performed: First, the intraocular lens is formed, such as on a lathe, from a blank of plastic (or other material) using any known process for forming intraocular lenses. The intraocular lens may be machined from any of a variety of materials with an optical zone in the central portion configured to allow for extended depth of field or monocular focus. In one embodiment, the intraocular lens is configured to have the features described herein with reference to FIGS. 6A-7. Next, the virtual aperture may be formed to have flat posterior and anterior surfaces (i.e., the outer surfaces are not machined or otherwise modified), or the anterior or posterior surfaces may be machined to include desired surface features, such as grooves, ridges, waves, ripples, prisms, or any other surface features. Next, one or more haptics are machined into the substrate blank according to specifications to allow for implantation during surgery and proper placement within the eye.

[0056] The laser system 1205 is used to create a two- or three-dimensional pattern of damage spots within the virtual aperture of the intraocular lens, as described above.

[0057] Alignment processes and / or systems can be used to properly position the intraocular lens and tune it so that the laser damage is done accurately and precisely. The two- or three-dimensional array of damage spots is configured to allow a predetermined or desired amount of light transmission and diffusion. For example, the pattern can be a 5-10 layer pattern of 50 micron spots arranged in a rectangular or annular grid with 50 micron spacing between the damage spots. The pattern can include an offset between the layers so that gaps are filled when viewed axially. Because a uniform distribution of damage spots can lead to visual disturbances when implanted in the eye, the exemplary spot pattern employs a pseudorandom placement strategy.

[0058] In a second exemplary embodiment of sub-surface modification, a femtosecond pulsed laser (FSPL) is configured to interact with the intraocular lens (such as by focusing on a sub-surface location of the intraocular lens) to modify the refractive index of one or more sub-surface locations of the intraocular lens. The femtosecond pulsed laser forms modification loci at the sub-surface locations, the modification loci having a refractive index different from the refractive index of the material before modification. Different patterns of modification loci can provide selected dioptric power, toric adjustment, and / or aspheric adjustment to be provided. The refractive index of the modification loci may be different from the refractive index of the sub-surface locations surrounding the modification loci. The different refractive index may be caused by nonlinear photon absorption due to exposure to focused laser light via the femtosecond pulsed laser.

[0059] Referring again to FIG. 9, the laser system 1205 can be configured to emit a femtosecond pulsed laser 1220. The femtosecond laser is focused on the sub-surface of the intraocular lens 1210 and generates pulses with very specific time and intensity profiles. The laser can be controlled in the XY plane, such as by using a galvano position control device, which allows for very fast and precise positioning of the beam in the XY plane. Additionally, the system is connected to or uses an acoustically controlled focusing mechanism, which allows for very high frequency and precise focus control. This allows the focal spot of the femtosecond laser to be positioned at any depth and at any XY coordinate within the substrate with extremely high speed and precision.

[0060] The femtosecond laser pulses impact the interior region of the intraocular lens, changing the refractive index of certain subsurface regions of the intraocular lens and forming a track. This process can be applied to a variety of intraocular lens materials, for example, glass, hydrophobic acrylic, and hydrophilic acrylic. The mechanism that results in the refractive index change is different for each substrate, but for all substrates mentioned, the laser-effected areas have a lower refractive index than the surrounding material. The drop in refractive index can depend on a variety of factors, including the substrate specifications, the intensity and time of laser exposure, and the thickness of the material. In general, a refractive index change of about 0.06 is consistently achievable. For example, if the original hydrophilic acrylic substrate has a nominal refractive index of 1.459 when fully hydrated, the treated areas after laser exposure can have a refractive index as low as 1.399.

[0061] 11 is a schematic diagram of a portion of an intraocular lens 1210. An array of loci 1405, each having an altered refractive index, is disposed generally beneath the outer surface of the intraocular lens 1210. The array includes one or more loci. In the illustrated example, the loci form a rectangular array of equidistant loci, although the shape and spatial arrangement of the array, as well as the loci within the array, may vary.

[0062] In the sample manufacturing process, a lathe is used to form an intraocular lens with a virtual aperture as described herein. Referring to Figure 9, the intraocular lens is aligned with a femtosecond laser device 1205, which irradiates the lens with a femtosecond laser 1210 focused on the sub-surface location to achieve the desired diffusion, transmission, and beam steering to form the desired sub-surface pattern of modified refractive index zones.

[0063] In either subsurface modification embodiment, multiple layers of damage spots or loci in the array allow for spreading and homogenization of the narrow beam incident on the intraocular lens.

[0064] Optical Zone Optimization / Enhancement

[0065] As previously mentioned, the disclosed systems and methods allow a user to manufacture a lens (such as an intraocular lens) having at least one parameter, such as an optical zone diameter, a radius of curvature, a conic constant, and / or an alpha coefficient, that at least partially defines the lens and maximizes or enhances one or more desired properties of the intraocular lens. Some exemplary properties or characteristics that may be optimized or enhanced include: (1) depth of focus, (2) minimizing or reducing poor performance (e.g., less than 20 / 20) zones, and (3) ensuring robust operation with respect to decentering, tilt, off-axis light source, implantation errors during surgery, and intraocular lens power selection errors. The disclosed process may also be referred to as an optimization process. However, it should be understood that the process is not limited to optimization and may also be used to enhance or modify desired properties. In one embodiment, a lens, such as an intraocular lens, is manufactured according to the optimization process.

[0066] The virtual aperture may be considered a variable transmittance zone in any embodiment, configured as described herein and altered according to the disclosed optimization procedure. The virtual aperture is both a scattering mechanism and a partial (or complete) light attenuation mechanism. That is, the light transmittance of the virtual aperture may range from 0 to 100%. The optimization procedure involves constructing or defining a central optical zone using a reference eye model (e.g., equations defining a lens). Parameters of the model are varied using an optimization routine. The parameters are swept through a range of variations to arrive at an optimal optical zone definition as measured by a merit function configured to meet a predefined criteria. The eye model may be in the form of an equation that defines an aspect, such as a surface of the lens. The lens parameters may be varied, such as spherical, aspheric, higher order polynomial equations, or any mathematical description of a lens surface where the parameters of the equation or formula can be varied. The equation may be any mathematical description with one or more variable parameters that define one or more aspects of the lens shape. Since the lens, e.g., the lens surface, is not defined by a particular formula or equations, any number of locations of the lens surface may be independently optimized. The merit function may be varied.

[0067] One type of scattering mechanism in the virtual aperture is a plurality of holes arranged in the virtual aperture. At least some or all of the holes have a predetermined size and are arranged in a region or throughout the virtual aperture. The holes are configured to allow the passage of light therethrough to produce a diffraction effect and / or to achieve or change a desired opacity. The holes may have a spatial arrangement / pattern, diameter, depth, and / or density of the hole pattern that allows a specific light scattering pattern on the retina (when implanted in the eye) to achieve a desired diffusion effect, such as a homogenous distribution of light and / or scattering of light.

[0068] In an embodiment, the holes are spatially arranged in the virtual aperture with a density across the surface area of ​​the virtual aperture to achieve a light transmission ranging from 10% to 100% across the entire virtual aperture, the holes being arranged to achieve this. As mentioned above, the diameter of the optical zone can vary, and in a non-limiting example, can be as small as 1.5 mm. An optical zone of 1.5 mm diameter has been shown to be at or near the minimum threshold required to allow sufficient light into the eye under mesonic conditions. In another embodiment, the diameter can vary, and is not limited to a particular size, but is sized from 1.5 mm to 2.8 mm or 3 mm in diameter.

[0069] In non-limiting embodiments, the optic zone of the intraocular lens is removable and replaceable relative to the remainder of the intraocular lens, i.e., the optic zone region can be removed and replaced based on prescription or other considerations, while structures of the intraocular lens other than the optic zone (such as haptics) can be implanted and remain in the eye.

[0070] An exemplary optimization or enhancement process will now be described. The optimization process can be performed or implemented using a computing system (such as computing system 500 described below with reference to FIG. 12), which can be communicatively connected directly or indirectly to a lens manufacturing system. In a first step, a user selects or identifies a characteristic of the lens to be optimized. Some exemplary characteristics include depth of focus and / or depth of field. For example, the optimization process may select a lens configuration where the depth of field and / or depth of focus fall within a predetermined range while maintaining the diameter of the virtual aperture. Other lens characteristics are within the scope of this disclosure. An optimization procedure is then performed to achieve the target value.

[0071] In an exemplary method of defining the shape of an ophthalmic lens, a computer and / or user identifies an equation that defines a physical characteristic of the lens, the equation including at least one lens parameter. Then, after obtaining an output of the equation using a first value of the lens parameter, the output is scored using an evaluation function. The value of the lens parameter is iteratively changed using an optimization process or algorithm until the evaluation function achieves an acceptable score. The evaluation function is based on the visual acuity of the lens and may include at least one of a distance visual acuity, an intermediate visual acuity, and a near visual acuity. The evaluation function may also include a sum of the LogMAR visual acuity of the distance visual acuity, the intermediate visual acuity, and the near visual acuity. The evaluation function may be based on or related to the Airy disk, and the Airy disk value may be used as a limit for scoring the focal spot size of the lens. For example, the evaluation function may compare the spot size to an Airy disk value and score negatively if the spot size is smaller or larger than the Airy disk value by a predetermined amount.

[0072] The method achieves a lens with sufficient depth of focus to allow a user of the lens to see distant and near objects at a given visual acuity. The optimization algorithms or functions can vary and include gradient descent, Newton's method, simulated annealing, exhaustive search, brute force search, stochastic optimization, random subset optimization, greedy or non-greedy methods, linear programming optimization, and / or other generation or testing techniques. The equations can define a spherical lens, an aspheric lens, or a freeform lens surface. The lens parameters can include, for example, a radius of curvature and / or a conic constant. Physical characteristics may include an outer surface of the lens or other surfaces of the lens. The lens is manufactured according to the optimization process using any of a variety of lens manufacturing processes.

[0073] The optimization process involves sweeping or providing a range of values ​​corresponding to at least one parameter or feature of the lens (such as the optical zone, where the features may include, for example, at least the radius of curvature and the conic constant), and then inserting the values ​​into an equation describing an aspect or parameter of the lens, such as the following equation (3) describing an aspheric surface: Equations for other shapes, including spheres and freeform surfaces, are also within the scope of this disclosure. TIFF2025514682000002.tif32166

[0074] Where:

[0075] z(r) is the sag or z-component of the displacement of the lens surface from the vertex at a distance r (extending in the z-direction) from the lens optical axis.

[0076] r = radial distance from the axial center of the lens

[0077] R = radius of curvature of the lens

[0078] k = conic constant of the lens

[0079] α = coefficient term (You can also optimize the coefficients in a similar way, but in this example we set them to 0.)

[0080] Freeform optics is not based on simple spherical or aspheric profiles and associated mathematical formulas. Freeform optics can take any shape that works to maximize the metrics of a merit function. Freeform optics does not assume an underlying mathematical description where each point on the lens surface is optimized independently. The collection of all the points constitutes the optical surface.

[0081] In one embodiment, the numerical values ​​of the radius of curvature R and the conic constant k are swept over the range of values ​​in equation (3). For each given radius R and conic constant k, an aspheric lens shape is identified using equation (3). The lens is then assigned a predetermined refractive index that is used in a modeling procedure to achieve a number of defined lens shapes. Each lens shape includes, but is not limited to, an eye model that includes standard accepted eye geometric elements such as:

[0082] - Corneal shape and refractive index

[0083] -Refractive index of aqueous humor

[0084] -Iris and pupil shape and placement

[0085] -Lens arrangement

[0086] -Distance to the retina

[0087] -Retinal shape and curvature

[0088] -Aberrations of the optical system

[0089] -Known abnormalities of the optical system such as cataracts or posterior capsule opacification (PCO)

[0090] Next, "distance" visual acuity is calculated. In a non-limiting example, the "distance" distance is a light source at 4000 mm, which represents the clinical standard definition of "distance". This is in LogMAR units, with 0 representing 20 / 20 and lower values ​​indicating better visual acuity.

[0091] Next, the visual acuity for "near" vision is calculated. In a non-limiting example, the "near" distance is a light source at 400 mm, which represents the clinical standard definition of "near." Again, this is in LogMAR units, with 0 representing 20 / 20 and lower values ​​indicating better visual acuity.

[0092] Acuity for "intermediate" vision is also calculated. In a non-limiting example, the "intermediate" distance is a light source at 660 mm, which represents the clinical standard definition of intermediate. This is in LogMAR units, with 0 representing 20 / 20 and lower values ​​indicating better vision.

[0093] The above modeled visual acuity is then used to find a combination of lens properties, such as lens diameter, lens radius of curvature, and lens conic constant, that have acceptable visual acuity at all three distances, as defined in equation (3).

[0094] The correct selection of the parameters of the evaluation function is important for the optimization process. Any parameters can be included, but the more constrained the evaluation function is, the less likely it is to find an acceptable solution. In one embodiment, the evaluation function includes the diameter of the optical zone (for the virtual aperture version). The larger the optical zone, the higher the evaluation function score. A larger optical zone diameter is more favorable for the overall light gathering ability of the intraocular lens.

[0095] The evaluation function can include a "minimum LogMAR" optimized for a particular focus. This represents the absolute best that an intraocular lens can do for a given pupil size. In one embodiment, the optimum is to go to the edge of the diffractive effect and then stop "improving" performance. The evaluation function can also include the variance (or another measure of variation) of visual acuity between near and distance vision. An example of an optimum in this case would be very even performance across the entire focus range with no sweet spot.

[0096] In one example, the diameter of the optical zone is a minimum of 1.5 mm. An optical zone of 1.5 mm diameter has been shown to be at or near the minimum threshold required to allow sufficient light into the eye under mesonic conditions. In another embodiment, the diameter is as large as 1.5 mm to 2.8 mm or 3 mm.

[0097] The maximum diameter of the optical zone may be limited by the visual acuity achievable using the disclosed process. One example of a criterion is that there must be at least one distance (distance, intermediate, near) where the LogMAR is 0 or less, i.e., visual acuity of 20 / 20 or better. Another example of a criterion is that visual acuity at intermediate distance is 20 / 20 or better, while near and distance visual acuity are within acceptable limits. This may be more difficult to achieve with a larger optical zone diameter.

[0098] An example of this is shown in the table below. The first row represents an optic with a 3mm diameter, 17.7mm radius of curvature, and k=-100. In this example, intermediate vision is better than 20 / 20 and close to 20 / 20 at both distance and near. The second row represents a 4mm diameter optic that does not achieve 20 / 20 vision at any distance.

[0099] Standard mathematical optimization techniques or algorithms are then used to calculate the combination of parameters that achieves the desired result. Examples of optimization techniques include, but are not limited to: gradient descent, Newton's method, simulated annealing, exhaustive search, brute force search, stochastic optimization, random subset optimization, greedy or non-greedy methods, linear programming optimization, and / or generate and test techniques. The evaluation function used in the optimization is flexible, but one example is the sum of the LogMAR visual acuity for distance, intermediate, and near. This sum represents an overall performance metric where lower is better at all three distances. JPEG2025514682000003.jpg60163In the above example, the sum for the 3mm optic is 0.0718, while the sum for the 4.0mm optic is 0.1244. In this case, the 3mm optic is superior and is ranked higher in the optimization. Another example of an evaluation function may include the difference between the near value and the LogMAR value, which indicates the near and far power balance of the lens.

[0100] In an embodiment, the lens optimization procedure achieves a lens that can produce a lens with sufficient depth of focus to allow the lens user to see both distant and near objects with good vision. The optimization utilizes the constraints of the distance, intermediate, and near models to predict the visual acuity at all three constraints. One or more parameters, such as the radius of curvature or the conic constant, are varied until the distance, near, and intermediate vision all achieve the desired performance. Additionally, the alpha coefficient of the formula can be optimized to further improve performance.

[0101] Lenses can be manufactured according to the optimization process described herein and implanted in a human eye.

[0102] FIG. 12 is a block diagram illustrating an example of a computing system 500 consistent with implementations of the present subject matter. The computing system 500 may implement any of the processes described herein. As shown in FIG. 12, the computing system 500 may include a processor 510, a memory 520, a storage device 530, and an input / output device 540. The processor 510, the memory 520, the storage device 530, and the input / output device 540 may be interconnected via a system bus 550. The processor 510 may process instructions that execute within the computing system 500. Such executed instructions may implement one or more components of the processes described herein. In some implementations of the present subject matter, the processor 510 may be a single-threaded processor. Alternatively, the processor 510 may be a multi-threaded processor. The processor 510 may process instructions stored in the memory 520 and / or the storage device 530 to display graphical information of a user interface provided via the input / output device 540.

[0103] Memory 520 is a computer-readable medium, such as volatile or non-volatile, that stores information within computing system 500. Memory 520 may store, for example, a data structure representing a configuration object database. Storage device 530 may provide persistent storage for computing system 500. Storage device 530 may be a floppy disk drive, digital cloud, hard disk drive, optical disk drive, tape drive, or other suitable persistent storage means. Input / output device 540 provides input / output operations to computing system 500. In some implementations of the current subject matter, input / output device 540 includes a keyboard and / or a pointing device. In various embodiments, input / output device 540 includes a display device for displaying a graphical user interface.

[0104] According to some implementations of the current subject matter, I / O devices 540 can provide input and output operations for a network device. For example, I / O devices 540 can include Ethernet ports or other network ports for communicating with one or more wired and / or wireless networks, Bluetooth or digital cloud systems (e.g., a local area network (LAN), a wide area network (WAN), the Internet).

[0105] In some embodiments of the current subject matter, the computing system 500 can be used to execute various interactive computer software applications that can be used to organize, analyze, and / or store data in various (e.g., tabular) formats (e.g., Microsoft Excel®, other software). Alternatively, the computing system 500 can be used to execute any type of software application. These applications can be used to perform various functionalities, such as planning functionality (e.g., creating, managing, editing spreadsheet documents, word processing documents, other objects, etc.), computational functions, communication functions, etc. Applications can include various add-in functions, plug-ins, or may exist as stand-alone computing products and / or functions. When functions are invoked within an application, a user interface can be generated that is provided via the input / output devices 540. The user interface can be generated by the computing system 500 and presented to a user (e.g., a monitor on a computer screen, etc.). The user interface can be integrated with other devices and virtual ecosystems.

[0106] Although many specific details are described herein, these should not be construed as limitations on the scope of the claimed invention or what may be claimed, but rather as descriptions of features specific to a particular embodiment. Certain features described in separate embodiments can also be implemented in combination in one embodiment. Conversely, various features described in one embodiment can also be implemented separately in multiple embodiments or in any suitable subcombination. Furthermore, even if certain features are described as acting in a particular combination and originally claimed as such, one or more features may be excluded from the claimed combination, and the claimed combination may be directed to a subcombination or variations thereof. Similarly, although operations may be illustrated in a particular order, it should not be understood that such operations must be performed in the particular order or sequence shown, nor is it necessary to perform all of the illustrated operations to achieve desirable results. Only some examples and implementations are disclosed. Based on the disclosed content, variations, modifications, and enhancements to the described examples and implementations, as well as other embodiments, may be made. [Explanation of symbols]

[0107] 1 Lens 2 Optical axis 3,3b incident ray 4,4e,4f focus 5 Observation surface 6,6b,6e,6f Blurred Circles 7,7b incident ray 8,8b,8e,8f Blurred Circles 9 Central area 10 Surrounding Areas 21 Lens 22 Optical axis 23 Colored Rays 24 Blue Ray 25 Green Ray 26 Red Ray 27 Observation surface 29 Incident colored rays 34 Lens 36 Incident parallel rays 37 Lens Focus 38 Observation surface 39 Blurred Circles 40,40b Incident parallel ray 41 Blurred Circle 43 Ray of light 46,46b Optical Zone 46b back side 47 First Transition Zone 49 Second Transition Zone 50,50b Haptic 50b back side 500 Computing Systems 510 Processor 520 Memory 530 Storage device 540 I / O device 540 I / O device 550 System Bus 605 Haptic 610 Orientation Structure 709 Optical Zone 710 First Transition Zone 711 Hexagonal Microlens Area 712 Second Transition Zone 713 Haptic 1101 Multi-area Optical Zone 1109 Central area 1110 Surrounding Area 1205 Laser System 1210 Intraocular Lens 1210,1220 Laser 1305 Damage Spot 1405 Trajectory

Claims

1. 1. A method for defining a shape of an ophthalmic lens, comprising the steps of: identifying an equation defining a physical characteristic of the lens, the equation including at least one lens parameter; using first values ​​for said lens parameters to achieve an output of said equation; Scoring the output using a rating function; iteratively varying the value of at least one lens parameter using an optimization algorithm until the evaluation function reaches an acceptable score. A method comprising:

2. The method of claim 1 , wherein the evaluation function is based on the visual acuity of the lens.

3. The method of claim 2 , wherein the evaluation function includes at least one of distance visual acuity, intermediate visual acuity, and near visual acuity.

4. The method of claim 2 , wherein the evaluation function comprises a sum of LogMAR visual acuity for distance, intermediate, and near visual acuity.

5. 10. The method of claim 1, achieving a lens with sufficient depth of focus to enable a lens wearer to see both near and distant objects at a given visual acuity.

6. The method of claim 1 , wherein the optimization algorithm comprises gradient descent, Newton's method, simulated annealing, brute force, random subset optimization, greedy or non-greedy methods, linear programming, and / or generation or testing techniques.

7. The method of claim 1 , wherein the equation defines a spherical lens.

8. The method of claim 1 , wherein the equation defines an aspheric lens.

9. The method of claim 1 , wherein the equation is a high order polynomial equation that defines the surface of the lens.

10. The method of claim 1 , wherein the equation defines a freeform lens surface.

11. The method of claim 1 , wherein the at least one lens parameter is a radius of curvature.

12. The method of claim 1 , wherein the at least one lens parameter is a conic constant.

13. The method of claim 1 , wherein the physical property is an outer surface of the lens.

14. The method of claim 1 further comprising manufacturing the lens.

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