KR20210151875A - High-definition and extended depth-of-field intraocular lens - Google Patents

Abstract

A virtual stop integrated into an intraocular lens is disclosed. Light rays intersecting the virtual stop are scattered widely across the retina, effectively preventing the light from reaching detectable levels in the retina. The use of a virtual aperture helps to remove monochromatic and chromatic aberrations to create high-definition retinal images. For a given sharpness of an acceptable field of view, the depth of field is increased over the large diameter optical zone. Also, as the optical zone can have a smaller diameter, thinner intraocular lenses can be produced. This in turn allows for a smaller corneal incision and easier transplant operation.

Description

High-definition and extended depth-of-field intraocular lens

claim priority

This application claims priority to U.S. Patent Application 16/380,622, filed April 10, 2019, and entitled "HIGH DEFINITION AND EXTENDED DEPTH OF FIELD INTRAOCULAR LENS." The contents of the aforementioned applications are incorporated herein by reference in their entirety.

The human eye often suffers from aberrations such as defocus and astigmatism that must be corrected to provide an acceptable field of view to maintain a high quality of life. Correction of such defocus and astigmatism can be achieved using lenses. Lenses can be placed in the eye in the spectacle plane, in the corneal plane (contact lenses or corneal implants), or as a phakic (intact lens) or aphakic (removal) intraocular lens (IOL). have.

In addition to the basic aberrations of defocus and astigmatism, the eye often has high-order aberrations, such as spherical and other aberrations. Chromatic aberration, which is an aberration due to changes in focus with wavelength across the visible spectrum, is also present in the eye. These high-dimensional aberrations and chromatic aberrations negatively affect the quality of human vision. As the pupil size increases, the negative influence of high-dimensional aberrations and chromatic aberrations increases. A field of view in which this aberration has been removed is often referred to as a high definition (HD) field of view.

Presbyopia is a condition in which the eye loses the ability to focus on objects located at different distances. Aphasic eyes have presbyopia. A standard monofocal IOL implanted in an aphakic eye will restore vision at a single focal length. To provide good vision over a range of distances, various options may be applied, including using monofocal IOLs in combination with bi-focal or progressive glasses. Another option for restoring near and far vision is the monovision IOL system (where one eye is set to a different focal length than the other, thus providing a binocular sum of the two focal points and providing a mixed field of view). to provide).

Monovision is currently used to correct presbyopia by the use of an IOL to achieve glasses-free binocular vision from distance to near by correcting the dominant eye for distance vision and the non-dominant eye for near vision. The most common way. Also, the IOL may be bifocal or multifocal. Most IOLs are designed to have one or more focal areas distributed within a range of additions. However, using elements with distinct sets of foci is not the only possible design strategy: elements with extended depth of field (EDOF), i. can be considered. This method is not entirely acceptable, as stray light from the various focal areas degrades a person's field of vision.

What is needed in the art is improved virtual aperture IOLs to overcome these limitations.

A virtual iris integrated into an intraocular lens (IOL) is disclosed. Such construction and arrangement causes the light rays to intersect the virtual stop and scatter widely across the retina, effectively preventing the light from reaching detectable levels in the retina. The virtual iris eliminates monochromatic and chromatic aberrations to help create high-definition retinal images. For a given sharpness of an acceptable field of view, the depth of field is increased over the large diameter optical zone IOL. Eyes with cataracts may have problems secondary to injury, previous eye surgery, or eye disorders that may not be well corrected with normal IOL design. Examples of eyes with complications include: asymmetric astigmatism, keratoconus, postoperative corneal transplantation, asymmetric pupil, very high degree of astigmatism, and others. Due to their ability to remove unwanted aberrations, such a virtual aperture IOL design can be very effective in providing an improved field of view compared to a typical large optical IOL.

It is an object of the present invention to teach a method for manufacturing a thinner IOL, as the optical zone may have a smaller diameter, which allows for a smaller corneal incision and easier implantation surgery. Eyes with cataracts may have problems secondary to injury, previous eye surgery, or eye disorders that may not be well corrected with normal IOL design. Examples of eyes with complications include: asymmetric astigmatism, keratoconus, postoperative corneal transplantation, asymmetric pupil, very high degree of astigmatism, and others. Due to their ability to remove unwanted aberrations, the disclosed virtual stop IOL design is effective in providing an improved field of view compared to a typical large optical IOL.

Another object of the present invention is to teach a virtual stop IOL that exhibits reduced monochromatic and chromatic aberrations, as well as extended depth of field, while providing sufficient contrast for resolution of the image over a selected distance range.

Another object of the present invention is to teach a virtual stop IOL that provides a smaller central thickness compared to other equal-power IOLs.

Another object of the present invention is to teach a virtual stop that can be realized as alternating high-power positive and negative lens profiles.

Another object of the present invention is to teach a virtual stop that can be realized as a negative lens surface of high refractive power.

Another object of the present invention is to teach a virtual stop that can be realized as a high-power negative lens surface with alternating high-power positive and negative lens profiles.

Another object of the present invention is to teach a virtual stop that can be realized as a prism profile with alternating high-power positive and negative lens profiles.

Another object of the present invention is to overcome these limitations by providing a phakic or aphakic IOL, which at the same time: provides defocus and correction of astigmatism, reduces high-dimensional and chromatic aberrations, and prolongs Provides depth of field to improve field of view quality.

Another object of the present invention is to provide an extended depth of field for use in phakic or aphakic IOLs, corneal implants, contact lenses, or used in corneal laser surgery (LASIK, PRK, etc.) procedures, and/or high-definition To teach a virtual aperture that can provide a field of view.

Another object is to provide an IOL for the eye with complications such as asymmetric astigmatism, keratoconus, post-surgical corneal transplantation, asymmetric pupil, very high degree of astigmatism, and others.

Another object is to provide an IOL capable of eliminating unwanted aberrations, providing an improved field of view compared to a typical large optical IOL.

Another object of the present invention is to teach replacing a virtual stop with a real opaque stop and realizing the same optical advantages as a virtual stop.

Other objects and additional advantages and advantages associated with the present invention will become apparent to those skilled in the art from the following description, examples and claims.

1 shows a basic method for reducing monochromatic aberration using pupil size.
Figure 2 (A and B) shows a basic method for reducing chromatic aberration using pupil size.
Figure 3 (A and B) shows the basic concept of a virtual stop for limiting the effective pupil size.
4 shows a virtual stop as a high-power lens section integrated into an IOL.
5 shows a virtual stop as a negative lens section.
Figure 6 (A and B) shows a virtual stop as a negative lens (or prism) section with a high-power lens section.
Figure 7 (A and B) shows the use of a virtual stop to prevent the negative effect of a small optical zone.
8 shows a lens A embodiment of an elongated shaped optical zone and a lens B example of a circularly shaped optical zone.
9 shows an azimuthally symmetrical radial profile.
10 shows a symmetrical radial profile comparing elements A, B, C, D, and E;
11 shows a two-dimensional lens area.
12 shows the geometry for one of the two-dimensional high-power lenses.

Specific embodiments of the invention are disclosed herein; It will be appreciated that the disclosed embodiments are merely illustrative of the invention, which may be embodied in various forms. Accordingly, the specific functional and structural details disclosed herein are not to be construed as limiting, but merely as a basis for the claims and as a representative basis for teaching those skilled in the art to variously utilize the invention in virtually any suitable specific structure. do.

1 shows a single converging lens 1 centered on an optical axis 2 . The incident ray 3 is parallel to the optical axis and will intersect the focal point 4 of the lens. If the viewing plane 5 is located at a greater distance from the focal point, the incident ray will continue until it intersects the viewing plane. In the case of tracing all incident rays having the same ray height as the incident ray 3 , it will be possible to locate a blur circle 6 on the viewing plane. Any other incident ray having a lower ray height than the incident ray 3 will lie within this blurring circle 6 . One such ray is the incident ray 7 closer to the optical axis than the incident ray 3 . The incident ray 7 also intersects the focal point 4 and then the observation plane 5 . Tracing all incident rays with the same ray height as the incident ray 7 results in a blurring circle 8 smaller than the blurring circle 6 being traced.

The optical principle provided herein is that as the height of the parallel incident rays is reduced, the corresponding blurring circle is also reduced. This simple relationship can be applied to the human eye. Stated differently, for a given amount of defocus (dioptric error) within the eye, as the height of the incident ray is reduced, the field of view is improved. This principle is used when squinting in an attempt to see an out-of-focus object more clearly.

The trace in Figure 1 is for a single wavelength of incident light. In this case, in multi-colored light of three wavelengths, the situation of Figure 2 is obtained. It is well known that in the constituents of the eye and in typical optical materials, when the wavelength is increased, the refractive index decreases. In FIG. 2A , the converging lens 21 has an optical axis 22 . Incident ray 23 consists of three wavelengths for blue (450 nm), green (550 nm), and red (650 nm) light. Due to the different indices of refraction of the three wavelengths, the blue ray 24 is refracted more than the green ray 25 , and the green ray is more refracted than the red ray 26 . When the green ray is focused, it will traverse the viewing plane 27 in the optical axis. The color diffusion of these three rays results in a color blur circle 28 on the viewing plane. In FIG. 2B , the incident chromatic ray 29 has a lower ray height than the chromatic ray 23 in FIG. 2A . This results in a smaller color blur circle 33 in the viewing plane. Thus, as the color ray height is decreased, as in the solid color of FIG. 1 , the color blur is reduced.

1 and 2 show that increasing the beam height (reducing the pupil diameter) reduces both monochromatic and chromatic aberrations in the retina, thus improving the quality of the field of view. Stated another way, as the ray height is reduced, the depth of field increases.

3A shows a converging lens 34 with an optical axis 2 and a stop 35 . Incident ray 36 exits the stop and thus passes through lens focal point 37 and intersects observation plane 38 , where a small circle of blur 39 is traced. The incident ray 40 is blocked by the diaphragm, so the incident ray cannot continue up to the viewing plane, resulting in a larger blurring circle 41 . An iris limiting the incident ray height reduces blur on the viewing plane. In Fig. 3B, what is described as a "virtual stop" is shown. That is, it is not an aperture that actually blocks the light beam, but the optical effect is almost the same. The ray 43 propagating through the virtual stop 42 is spread widely and thus contributes little to stray light (blurring of light) at any one spot on the viewing plane. This is the main mechanism for the operation of the IOL invention. Often months to years after cataract surgery and IOL implantation, a disease called posterior capsule opacity (PCO) develops over the transparent posterior capsule and can interfere with quality vision. The incidence of PCO has been reported to range from 5% to 50% of eyes that have undergone cataract surgery and IOL implantation. Treatment to remove the PCO often involves intervention with an Nd:YAG laser to perform a retrocapsular resection. In this case, the laser is focused through the IOL to perform capsulotomy. If the virtual stop is instead opaque, like a real aperture, then this treatment may be prohibited. The disclosed virtual aperture was intentionally designed to allow for YAG capsulotomy for PCO treatment while providing the benefit of a small aperture.

Figure 4 shows the basic layout of an IOL using a virtual stop. In this figure, the central optical zone 46 provides for defocusing, correction of astigmatism, and any other corrections required in the lens. In general, in IOLs using virtual apertures, the central optical zone diameter is smaller than in conventional IOLs. This results in a smaller median thickness, which allows the IOL to be implanted more easily and allows for a smaller corneal incision during surgery. A virtual stop 48 is additionally located within the periphery, and the IOL haptic 50 is located within the more distal periphery. The virtual stop is connected to the optical zone by a transition region 47 , and the sclera is connected to the virtual stop by a transition region 49 . Transition regions 47 and 49 are designed to ensure zero-order and first-order continuity of the surfaces on either side of the transition region. A common method for porting this is a polynomial function such as a cubic Bezier function. Such transfer methods are well known to those skilled in the art.

In a preferred embodiment, the virtual stop zone 48 is a sequence of high-power positive and negative lens profiles. Thus, light rays intersecting these regions are widely dispersed downstream of the IOL. Such a profile can be a sequential cone, polynomial (eg, Bezier function), rational spline, diffraction profile, or other similar profile, so long as the entire area properly redirects and/or scatters the refracted rays. can be realized with The preferred use is a high-power profile, which is smoother than a diffraction profile, as it simplifies manufacturing the IOL on a high-precision lathe or in a mold. As is known to those skilled in the art, the posterior aspect of the sclera should include a square edge to inhibit cell growth leading to posterior capsule opacification.

FIG. 5 shows another profile for the virtual diaphragm zone 51 , namely a converging lens profile. It should be noted that this requires a thicker edge profile than in FIG. 4 . 6A , a close-up of a preferred high-power alternating positive and negative lens profile is shown, along with the incident and transmitted rays. Fig. 6B shows the effect of combining the profile in Fig. 6A with a basic prism or a negative lens. In this case, the light rays coming out are not only widely scattered, but are directed away from the central viewing section of the retina or macula of the eye, which in turn causes the lens edges to become wider.

7A shows a high-power IOL 60, which generally has a relatively small optical diameter and a thick central thickness. When the pupil of the eye is larger than the optic zone, the incident ray 64 may completely deflect the optic and only intersect the sclera 61 in its path to the retina 63 . This situation can cause significant artifacts in the peripheral vision of the eye. As expected, the incident ray 62 intersecting the optical zone is precisely refracted into the retina's central field of view. 7B , the same, but now shown optic with a virtual stop 65 between the optic and the sclera.

In this case, the incident ray 64 intersecting the lens outside the optical zone is dispersed across the retina and thus does not cause significant artifacts.

Taken together, these properties of an IOL comprising a virtual stop can be accurately described as high definition (HD) and extended depth of field (EDOF).

The basic layout of the virtual aperture IOL is shown in FIG. 4 . In a preferred embodiment, the diameter of the central optical zone 46 is 3.0 mm and the width of the virtual stop 48 is 1.5 mm. Thus, the combination of the central optical zone and the virtual aperture is a 6.0-mm diameter optic, similar to a typical commercially available IOL.

Spherical aberration, toric aberration and zero aberration optical domain. A significant proportion of cataract patients have astigmatism in their cornea. After removal of the lens, the remaining optical system of the astigmatic corneal eye is ideally corrected with a toric or astigmatic lens. In these patients, the central optical zone of the present lens is made toric to provide improved visual field correction. Also, although the optical portion is small, there is still some amount of spherical aberration that can be corrected. Thus, an optimally corrected optical zone will provide spherical aberration correction for all lenses and toric correction for patients with corneal astigmatism.

Toric correction is facilitated by those skilled in the art by providing two fundamental powers in two principal directions that can be aligned with the corneal astigmatism power of the eye.

The spherical aberration of a spherical or toric lens is corrected by using a conical profile on one or more surfaces of the lens. Such a lens can be said to have zero aberration because there is zero monochromatic aberration within the lens for on-axis distant objects. The apex radius of the conical profile is generally calculated for the desired paraxial power of the lens. A cone constant (K) is then selected based on the refractive index of the lens material, the lens center thickness, and the shape of the anterior and posterior surfaces of the lens.

In cases where the correction is to be astigmatic, at least one of the lens surface shapes is biconic, with a conical profile in two orthogonal basic directions. In a preferred embodiment, the toric optic has an equal biconvex surface design with each surface being biconical. Non-toric optics have the same biconvex surface design, with each surface being conical. In both cases of double conical or conical surfaces, the optimal conic constant (K) for the surface is determined using optical ray tracing known to those skilled in the art.

Multifocal point. Some patients may prefer multi-focal optics that provide field correction for specific distances. One example is bifocal optics that generally provide focal power for both near and far vision. Another example is a trifocal optic that provides focal power for near and intermediate distance vision. In either case, to implant a multi-focal point IOL, the optical zone is modified to create these focal zones using either refractive or diffractive optical zones, and the virtual stop is maintained outside the last focal zone.

In some applications, the virtual stop may appear as an annular area with an optical zone on each side of the annular area. The shape of the annular virtual diaphragm may also be free-form, for example to accommodate an astigmatic optical zone or a non-symmetrical scleral region. This is illustrated in FIG. 8 . In this figure, lens A represents an elongated shaped optical zone, so that the inner contour of the virtual stop must be adapted to that shape. The inner scleral zone contour is circular, and thus the external virtual diaphragm contour is circular. In this figure, lens B shows the optical zone as a circle, so that the virtual stop inner contour is circular. The inner sclera contour is elongated, and thus the outer virtual diaphragm contour is elongated. In each case, a transition zone exists between the respective zones in order to seamlessly connect the zones so that no visual artifacts are introduced into the eye. Alternatively, the transition region may have a variable width such that the inner and outer virtual stop contours may have any desired shape.

The IOL designs contemplated herein may be made of any biocompatible optical material commonly used for IOLs, including rigid and flexible materials. They can also be manufactured using CNC machines or other methods used to make molds or IOLs. The virtual stop can be implemented as a one-dimensional profile symmetrical in the azimuth direction or a two-dimensional profile implementing a small lens area.

In Fig. 9, an azimuthally symmetrical radial profile is shown. The profiles can all be the same or can be adjusted in the azimuth direction. This profile may be refractive or diffractive in nature. Although eight distinct radial profiles are shown, the radial profiles are continuous in the azimuthal direction. The radial profile may have alternating high-power positive and negative power sections, all positive power sections, or all negative power sections. The connection between all refractive power areas is smooth to avoid visual artifacts.

In FIG. 10 , another symmetrical radial profile is shown comprising a combination of a planar negative power, and a lamp based shape, in addition to or instead of the high-power curve shown in FIG. 8 . Referring to FIG. 10 , element A shows a simple planar based shape. In FIG. 10 , element B shows a negative power based shape. The profile of this generally negative power curve may be given by a sphere, a cone, or a higher order curve, eg as part of a polynomial. In Figure 10, element C shows the segmented negative power profile of element B, where the curve is segmented similar to a Fresnel lens to keep the overall lens thickness thin. In FIG. 10 , element D shows a ramp-based shape profile, and in FIG. 10 , element E shows a segmented version of the ramp-based shape, wherein the ramp is designed to keep the overall lens thickness thin. segmented similar to the Nell lens. Although the segmented profiles of elements C and E are shown with sharp discontinuities, in practice, the boundary of the segments is a smooth function, such as a fillet or Bezier curve, to avoid observable artifacts caused by sharp discontinuities. is implemented using Also, as described elsewhere in this document, a smooth transition region is disposed between the optical zone and the virtual stop. This shape may be used in conjunction with or instead of high-power features to improve the effectiveness of the virtual stop.

11 shows a two-dimensional lens area oriented with polar sampling. A high-power lens has alternating positive and negative powers in both radial and azimuthal directions. Two positive power lenses and two negative power lenses are shown in the figure. The actual geometry of such a two-dimensional polar lens is approximately a radial profile.

Alternatively, the two-dimensional high-power lens may be an all-positive lens or an all-negative lens. In this case, to prevent visual artifacts, high-power lenses are separated by small smooth transition regions (eg, continuous polynomial interpolators, eg Bezier curves) in the azimuthal direction. When there is more than one lens sample rate, this is the preferred two-dimensional high-power lens structure.In this case, the individual lens looks like a small pillow, and such a pillow is a positive power lens above the base surface for and below the surface for negative power lenses.

12 shows the geometry for one of the two-dimensional high-power lenses. In the upper right part of the drawing, there is shown a front view of a high-power lens. There is a central high-power optical region and a peripheral transition region. The radial extent of this region is given by r, the width of the transition region is given by t, and the azimuthal subtense is given by theta. In the lower left part of the figure, one side view of the profile of the lens is shown. The central part represents the high-refractive power optical zone, and the two side curves represent the transition zone. The interface between the optical zone and the transition zone has zero-order and first-order continuity. At the edge of the lens boundary, the transition coincides with the virtual stop basic shape (typically a vertical line on the IOL). At the edge of the lens, there is also zero-order and first-order continuity between the transition curve (typically a polynomial curve) and the edge. The shape of this small high-power lens region is set such that the radial extent r is approximately equal to the arc-length of the central portion of the region.

The central optical zone may be designed using standard IOL design concepts, thus providing spherical, cylinder, and axial corrections, as well as higher-order corrections such as spherical aberration control. Such design concepts are well known to those skilled in the art.

The preferred virtual aperture profile shown in FIG. 4 has alternating positive and negative lens profiles with focal lengths of about +/- 1.5 mm. Such lens surface profiles can be generated using cones, polynomials (eg, cubic Bezier splines), glass splines, and combinations thereof and other curves. The geometry of the lens profile is chosen to properly distribute the transmitted light rays across the retina and at the same time to be relatively easy to manufacture on a high-precision lathe or in a mold process. It is also possible to place a smooth surface in one profile (eg, anterior surface) and a small high-power lens profile in another surface profile (eg, posterior surface).

When using the preferred virtual aperture profile shown in FIG. 4 , the edge thickness of the IOL and the central thickness of the central optical zone can be very thin, even in high-power IOLs. The material of the lens is the same as that used for other soft or rigid IOL designs.

The IOL design provides very good, high-definition, distance vision, and the range of "clear vision" is about what "clear vision" means (eg 20/40 vision), and the central optic zone. and the relative size of the virtual diaphragm width. A simple equation for estimating visual acuity and spherical refractive error at a given pupil diameter [Smith G, Relation between spherical refractive error and visual acuity, Optometry Vis. Sci. 68, 591-8, 1991] are given in equations (1a and 1b).

(1a)

(1a)

(1b)

(1b)

A = visual acuity in minutes of the arc (A = Sd/20), ie the minimum resolution angle

k = constant determined from clinical studies, mean value of 0.65

D = pupil diameter in mm

E = Spherical refractive error in diopters

Sd = Snellen denominator

Equation 2 is believed to be more accurate for low levels of refractive error and gives reasonable results.

At E = 0, A = 1 min of arc or 20/20.

(1b) is solved for E to obtain Equation (2).

(2)

(2)

Equation (1b) gives the visual acuity (A) over a range of depth of field (E x 2) and pupil diameter (D) in diopters.

Equation (2) gives the range of depth of field in diopters for a given visual acuity (A) and pupil diameter (D). For example:

For a visual acuity of 20/40, A = 40/20 = 2 minute arc

D = 3.0 mm

k = 0.65

Depth of field = 2E = 1.8 D. Using (1b), we get:

The concept of virtual iris can be used in phakic or aphakic IOLs, corneal implants, contact lenses, or used in corneal laser surgery (LASIK, PRK, etc.) procedures to provide extended depth of field and/or high-definition vision can provide In addition, the virtual stop can be replaced with a real opaque stop, and the same optical advantages as the virtual stop can be realized.

While particular forms of the invention have been shown, it will be understood that they are not limited to the particular forms or arrangements described and shown herein. It will be apparent to those skilled in the art that various changes can be made without departing from the scope of the invention and that the invention is not to be considered limited to what has been shown and described in the specification and drawings/figures contained herein.

Those skilled in the art will readily appreciate that the present invention is well configured to carry out its purposes and achieve the stated objects and advantages as well as its own objects and advantages. The embodiments, methods, procedures, and techniques described herein represent preferred embodiments herein, and are intended to be illustrative and not limiting in scope. Modifications and other uses included within the spirit of the invention and defined by the scope of the appended claims will be apparent to those skilled in the art. While the present invention has been described with reference to specific preferred embodiments, it should be understood that the invention as claimed should not be unduly limited to such specific embodiments. Indeed, various modifications of the described modes for carrying out the invention that are apparent to those skilled in the art are intended to be within the scope of the following claims.

Claims (25)

An intraocular lens that provides improved vision by uniformly diffusing defocused rays across the individual's retina, caused by light affecting aberrations in the individual's eye, comprising:
An intraocular lens having a virtual stop disposed within a first periphery of the intraocular lens and connected to an optical zone by a transition region, and a sclera disposed within a second perimeter and connected to the virtual stop by the transition region, wherein the The transition region includes the intraocular lens, with 0-order and 1-order continuity;
The virtual stop can be realized as high-refractive power positive and negative lenses, wherein the light rays intersecting the transition region and the virtual stop are uniformly distributed over the retina using diffraction, thereby resulting in a change in focal length An intraocular lens for reducing defocus and monochromatic and chromatic aberrations, thereby improving an individual's depth of field. The method of claim 1,
wherein the virtual aperture is constructed and arranged to treat posterior capsule opacification using an Nd:YAG laser. According to claim 1,
wherein the optical zone is constructed and arranged to correct for spherical aberration. The method of claim 1,
wherein the optical zone lens surface shape is constructed and arranged as a double cone to correct astigmatism. According to claim 1,
wherein the virtual aperture provides contrast for resolution of the image over a selected distance range. According to claim 1,
wherein the virtual aperture may be realized using a one- or two-dimensional optical profile. The method of claim 1,
and an optical profile positioned on at least one side of the intraocular lens. 8. The method of claim 7,
wherein the optical profile has a positive refractive power. 8. The method of claim 7,
wherein the optical profile has a negative refractive power. 8. The method of claim 7,
wherein the optical profile has alternating positive-negative powers. According to claim 1,
An intraocular lens, wherein the virtual aperture area is shaped to improve light scattering. According to claim 1,
wherein the optical zone provides one or more focal powers. According to claim 1,
wherein the virtual stop comprises a transition zone of variable shape. According to claim 1,
wherein the lens is comprised of a biocompatible material. An intraocular lens that provides improved vision by uniformly diffusing defocused rays across the individual's retina, caused by light affecting aberrations in the individual's eye, comprising:
made of a biocompatible material, having a virtual stop disposed within a first periphery of the intraocular lens and connected to the optical zone by a transition region, and a sclera disposed within a second perimeter and connected to the virtual stop by the transition area an intraocular lens, wherein the transition region has zero-order and first-order continuity;
said virtual stop has an optical profile with alternating high-power positive and negative lens profiles selected from the group consisting of sequential cones, polynomials, glass splines, and diffraction profiles, said transition region and rays intersecting said virtual stop An intraocular lens that uses silver diffraction to be uniformly distributed across the retina, thereby reducing defocusing and monochromatic and chromatic aberrations due to changes in focal length, thereby improving the individual's depth of field. 16. The method of claim 15,
wherein the virtual aperture is constructed and arranged to treat posterior capsule opacification using an Nd:YAG laser. 16. The method of claim 15,
wherein the optical zone is constructed and arranged to correct for spherical aberration. 16. The method of claim 15,
wherein the optical zone lens surface shape is constructed and arranged as a double cone to correct astigmatism. 16. The method of claim 15,
wherein the virtual aperture provides contrast for resolution of the image over a selected distance range. 16. The method of claim 15,
wherein the optical profile is one- or two-dimensional. 16. The method of claim 15,
and the optical profile is located on one side of the intraocular lens. 16. The method of claim 15,
wherein the optical profile is located on both sides of the intraocular lens. 16. The method of claim 15,
wherein the virtual diaphragm region is shaped to improve light scattering. 16. The method of claim 15,
wherein the virtual stop comprises a transition zone of variable shape. 16. The method of claim 15,
wherein the optical zone provides one or more focal powers.

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