High-precision and depth-of-focus extended intraocular lens

Abstract

A virtual aperture incorporated into an intraocular lens is disclosed. Light rays that intersect with the virtual aperture are widely scattered onto the retina, effectively preventing the light rays from reaching detectable levels on the retina. The use of a virtual aperture helps eliminate monochromatic and chromatic aberrations, resulting in a high-resolution retinal image. Given the known definition of acceptable visual acuity, a larger diameter optical zone results in a greater depth of focus. Additionally, the ability to reduce the optical zone diameter allows for the fabrication of a thinner intraocular lens, which in turn allows for a smaller corneal incision and facilitates implantation surgery.

Description

Technical Field

[0001] (Priority Claim) This application claims priority to U.S. Patent Application No. 16 / 380,622, entitled "HIGH DEFINITION AND EXTENDED DEPTH OF FIELD INTRAOCULAR LENS", filed on April 10, 2019. The content of the above-referenced application is hereby incorporated by reference in its entirety.

Background Art

[0002] The human eye often has aberrations such as defocus and astigmatism, and in order to maintain a high quality of life, these must be corrected to provide acceptable vision. Correction of these defocus and astigmatism aberrations can be achieved using lenses. The lenses can be located on the spectacle surface, the corneal surface (contact lens or corneal transplant), or inside the eye, as phakic (intact lens: the lens is not damaged) or aphakic (aphakic: the lens has been removed) intraocular lenses (IOLs).

[0003] In addition to basic aberrations such as defocus and astigmatism, the eye often has higher-order aberrations such as spherical aberration and other aberrations. Also, the eye has chromatic aberration (aberration due to the change in focus depending on the wavelength of visible light). These higher-order aberrations and chromatic aberration have an adverse effect on the quality of human vision. The adverse effect of higher-order aberrations and chromatic aberration becomes greater as the pupil is larger. Vision with these aberrations removed is sometimes referred to as high definition (HD) vision.

[0004] Presbyopia is a condition in which the eye loses its ability to focus on objects at different distances. A presbyopic eye is an aphakic eye. A standard monofocal IOL implanted in an aphakic eye restores vision at a single focal distance. To obtain good vision at various distances, various options can be applied, such as using a monofocal IOL in combination with bifocal glasses or progressive power glasses. The monovision IOL system is another option for restoring near and far vision - by setting one eye to a different focal distance from the other eye, it provides binocular summation at two foci and offers a blended visual field.

[0005] Monovision is the most common current method of presbyopia correction, which uses an IOL to correct the dominant eye for distance vision and the non-dominant eye for near vision in order to achieve binocular vision without glasses from far to near. Also, the intraocular lens may be bifocal or multifocal. Many IOLs are designed to have one or more focal regions distributed within the addition range. However, using only elements with discrete foci is not the only possible design strategy. The use of elements with extended depth of field (EDOF), i.e., elements that generate continuous focal segments over the required addition (or addition range), can also be considered. These methods are not fully acceptable because stray light from various focal regions reduces a person's vision.

[0006] What is needed in this technical field is an improved virtual aperture IOL to overcome these limitations. SUMMARY OF THE INVENTION

[0007] Disclosed is a virtual aperture incorporated in an intraocular lens (IOL). With this structure and arrangement, light rays that cross the virtual aperture and are widely scattered onto the retina are allowed, while it is virtually prevented for the light rays to reach a detectable level on the retina. The virtual aperture helps to remove monochromatic aberration and chromatic aberration, and a high-definition retinal image can be obtained. In known definitions for acceptable vision, an IOL with a larger diameter optical zone has an increased (deeper) depth of field. Cataract eyes may have secondary problems due to injuries, previous eye surgeries, or eye disorders that cannot be well corrected with normal IOL designs. For example, eyes with complications include asymmetric astigmatism, keratoconus, after corneal transplantation, asymmetric pupil, very high astigmatism, etc. The disclosed virtual aperture IOL design can remove unnecessary aberrations and is effective in providing improved vision compared to normal large optical IOLs.

[0008] An object of the present invention is to teach a method of manufacturing a thinner IOL by being able to reduce the diameter of the optical zone, thereby enabling a smaller corneal incision and facilitating the transplantation surgery. Cataract eyes may have secondary problems due to injuries, previous eye surgeries, or eye disorders that cannot be well corrected with normal IOL designs. For example, eyes with complications include asymmetric astigmatism, keratoconus, after corneal transplantation, asymmetric pupil, very high astigmatism, etc. The disclosed virtual aperture IOL design can remove unnecessary aberrations and is effective in providing improved vision compared to normal large optical IOLs.

[0009] Another object of the present invention is to teach a virtual aperture IOL that exhibits reduction of monochromatic aberration and chromatic aberration, and an extended depth of focus, while providing sufficient contrast for the resolution of an image within a selected distance range.

[0010] Yet another object of the present invention is to teach a virtual aperture IOL that provides a thin central thickness as compared to other equal-powered IOLs.

[0011] Another object of the present invention is to teach a virtual aperture that can be realized by profiles of alternately arranged high-power (or high refractive power) positive lenses (or plus lenses) and negative lenses (or minus lenses).

[0012] Yet another object of the present invention is to teach a virtual aperture that can be realized as a high-power negative lens surface.

[0013] Another object of the present invention is to teach a virtual aperture that can be realized as a high-power negative lens surface in combination with profiles of alternately arranged high-power positive and negative lenses (high-power positive-negative alternating lens profiles).

[0014] Yet another object of the present invention is to teach a virtual aperture that can be realized as a prism profile in combination with profiles of alternately arranged high-power positive and negative lenses (high-power positive-negative alternating lens profiles).

[0015] Yet another object of the present invention is to overcome these limitations by providing a phakic (intraocular lens) or aphakic (without intraocular lens) IOL, and at the same time, provide correction of defocus and astigmatism, reduce higher-order aberrations and chromatic aberrations, and provide an extended depth of focus to improve the quality of vision.

[0016] Another object of the present invention is to teach a virtual aperture that can provide an extended depth of focus and / or a high-definition view when employed in a phakic or aphakic IOL, corneal transplantation, contact lenses, or a technique of corneal laser surgery (such as LASIK, PRK, etc.).

[0017] Yet another object is to provide an intraocular lens for eyes with complications such as anisometropic amblyopia, keratoconus, after corneal transplantation, asymmetric pupils, and very high degrees of amblyopia.

[0018] Yet another object is to provide an IOL that can remove unwanted aberrations and provide improved vision compared to conventional large optical IOLs.

[0019] Another object of the present invention is to teach replacing a virtual aperture with an actual opaque aperture to achieve optical advantages similar to those of the virtual aperture.

[0020] Other objects related to the present invention, as well as further advantages and benefits, will become apparent to those skilled in the art from the following description, examples, and claims. BRIEF DESCRIPTION OF THE DRAWINGS

[0021]

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[0022] (Detailed Description of the Preferred Embodiment) Detailed embodiments of the present invention are disclosed herein. However, it should be understood that the disclosed embodiments are merely exemplary of the invention and can be embodied in various forms. Accordingly, the specific functional and structural details disclosed herein should not be construed as limiting, but rather as a representative basis for teaching those skilled in the art to employ the invention in substantially any appropriately detailed structure and as a basis for the claims.

[0023] FIG. 1 shows a single converging lens 1 centered on the optical axis 2. The incident light ray 3 is parallel to the optical axis and intersects the focal point 4 of the lens. When the observation surface 5 is located further away from the focal point, the incident light ray continues until it intersects the observation surface. Tracing all the incident light rays at the same ray height as the incident light ray 3 forms a blur circle 6 on the observation surface. Other incident light rays with a lower ray height than the incident light ray 3 enter inside this blur circle 6. One such ray is the incident light ray 7 closer to the optical axis than the incident light ray 3. The incident light ray 7 also intersects the focal point 4 and further intersects the observation surface 5. Tracing all the incident light rays at the same ray height as the incident light ray 7 traces a blur circle 8 smaller than the blur circle 6.

[0024] The optical principle presented here is that as the height of parallel incident light rays decreases, the corresponding blur circle also becomes smaller. This simple relationship also applies to the human eye. In other words, when there is a certain amount of defocus (dioptric error) in the eye, the visual acuity improves as the height of the incident light rays decreases. This principle is used when narrowing the eyes to see an out-of-focus object more clearly.

[0025] The trace in FIG. 1 is for incident light of a single wavelength. In the case of polychromatic light, which is light of three wavelengths in this case, the situation is as shown in FIG. 2. It is well known that in the components of the eye and typical optical materials, the refractive index decreases as the wavelength increases. In FIG. 2A, the converging lens 21 has an optical axis 22. The incident light ray 23 consists of light of three wavelengths: blue (450 nm), green (550 nm), and red (650 nm). Since the refractive indices of the three wavelengths are different, the blue light ray 24 refracts more than the green light ray 25, and the green light ray refracts more than the red light ray 26. If the green light ray is in focus, the green light ray intersects the observation surface 27 on the optical axis. Due to the color spread of these three light rays, a colored blur circle 28 is formed on the observation surface. In FIG. 2B, the colored incident light ray 29 has a lower ray height than the colored incident light ray 23 in FIG. 2A. As a result, the colored blur circle 33 on the observation surface becomes smaller. Thus, similar to the monochromatic case in FIG. 1, when the height of the colored light ray decreases, the color bleeding becomes smaller.

[0026] FIGS. 1 and 2 show that reducing the ray height (decreasing the pupil diameter) reduces both monochromatic aberration and chromatic aberration in the retina and improves the quality of the appearance. In other words, when the ray height decreases, the depth of focus increases (becomes deeper).

[0027] Figure 3A shows a converging lens 34 having an optical axis 2 and an aperture 35. The incident ray 36 passes through the aperture and then through the lens focus 37, intersects the observation plane 38, and traces a small blur circle 39 there. Since the incident ray 40 is blocked by the aperture, it cannot proceed to the observation plane to produce a large blur circle 41. The aperture that limits the height of the incident rays reduces the blooming (blurring) on the observation plane. Figure 3B shows what is called a "virtual aperture". That is, it is not actually an aperture that blocks the rays, but the optical effect is almost the same. The ray 43 propagating through the virtual aperture 42 is widely diffused (spread), so there is little contribution of blurring light at any point on the observation plane. This is the main operating mechanism of the IOL invention. Several months to several years after cataract surgery or intraocular lens implantation, a condition called posterior capsular opacification (PCO) occurs on the transparent posterior capsule, which may interfere with high-quality vision. The incidence of PCO has been reported to be about 5% - 50% in eyes that have undergone cataract surgery or IOL implantation. Treatments for removing PCO often involve therapeutic intervention using an Nd:YAG laser to perform posterior capsulotomy. In this case, the laser is focused through the intraocular lens to perform the capsulotomy. If the virtual aperture were instead an opaque one such as a true aperture, this treatment would be inhibited. The disclosed virtual aperture is designed to provide the advantages of a small aperture while enabling YAG-based capsulotomy for PCO treatment.

[0028] Figure 4 shows the basic layout of an IOL that employs a virtual aperture. In this figure, the central optical zone 46 performs defocusing (blurring of the focus), astigmatism, and other corrections required of the lens. Generally, an IOL that employs a virtual aperture has a smaller diameter of the central optical zone compared to conventional IOLs. As a result, the central thickness becomes thinner, making the implantation of the IOL easier and allowing the corneal incision during surgery to be reduced. The virtual aperture 48 is further disposed peripherally, and the IOL haptic 50 is disposed in a more distant periphery. The virtual aperture is connected to the optical zone by a transition region 47, and the haptic is connected to the virtual aperture by a transition region 49. The transition regions 47 and 49 are designed to ensure the zero-order and first-order continuity of the surfaces on both sides of the transition region. A common method to achieve this is a polynomial function such as a cubic Bézier function. Such transition methods are known to those skilled in the art.

[0029] In a preferred embodiment, the virtual aperture zone 48 is a series of high-power positive and negative lens profiles. Thus, light rays intersecting this region are widely dispersed downstream of the IOL. These profiles can be realized as a series of conical, polynomial (such as Bézier functions), rational spline, diffractive profiles, or other similar profiles as long as the entire region appropriately redirects and / or disperses the refracted light rays. A preferred usage is a high-power profile that is smoother than a diffractive profile, as this simplifies the manufacture of the IOL using a high-precision lathe or mold. As is known to those skilled in the art, the rear side of the haptic should include a square (or rectangular) edge to inhibit cell growth that leads to posterior capsule opacification.

[0030] Figure 5 shows another profile of the virtual aperture zone 51, namely the diverging lens profile. Note that this requires a thicker edge profile than the approach in Figure 4. In Figure 6A, a close-up of a preferred high-power alternating positive and negative lens profile is shown together with the incident and transmitted light rays. Figure 6B shows the effect when the profile of Figure 6A is combined with a base prism or negative lens. In this case, not only does the emerging light ray scatter widely instead of the lens edge becoming wider, but it is also directed away from the central visual section of the macula or retina of the eye.

[0031] Figure 7A shows a high-power IOL 60, which typically has a relatively small optical diameter and a thick central thickness. When the pupil of the eye is larger than the optical zone, the incident light ray 64 may completely escape the optical system and only intersect the haptic 61 on its way to the retina 63. In such a situation, significant artifacts occur in the peripheral vision of the eye. The incident light ray 62 that intersects the visual zone (or optic zone) as expected is correctly refracted for central vision of the retina. Figure 7B shows the same optical system but with a virtual aperture 65 between the optical system and the haptic. In this case, the incident light ray 64 that intersects the lens outside the optical zone is dispersed on the retina and no obvious artifacts occur.

[0032] Taken together, the characteristics of these IOLs incorporating a virtual aperture can be accurately described as high-definition (HD) and extended depth of focus (EDOF).

[0033] The basic layout of the virtual aperture IOL is shown in Figure 4. In a preferred embodiment, the diameter of the central optical zone 46 is 3.0 mm and the width of the virtual aperture 48 is 1.5 mm. Thus, the combination of the central optical zone and the virtual aperture is an optical component with a diameter of 6.0 mm similar to a common commercially available IOL.

[0034] Spherical, toric (ring-shaped: Toric), and zero aberration visual zones (or optic zones). Most cataract patients have astigmatism in the cornea. After removing the lens, the eye with the astigmatic cornea of the remaining optical system is ideally corrected with a toric lens, i.e., an astigmatism lens. For these patients, by making the central optical part of the lens toric, improved vision correction is provided. Also, even if the optical part is small, a certain degree of spherical aberration can be corrected. Therefore, in the optimally corrected (compensated) optical zone, spherical aberration is corrected for all lenses, and toric correction will be performed for patients with corneal astigmatism.

[0035] Toric correction is easily performed by those skilled in the art by providing two principal powers that will match the astigmatic power of the eye's cornea in two principal directions.

[0036] The spherical aberration of either a spherical lens or a toric lens is corrected by adopting a conical profile on one or more surfaces of the lens. Such a lens is said to have zero aberration since the monochromatic aberration of the lens for a distant object on the axis is zero. The apical radius Ra of the conical profile is calculated in the usual way for the desired paraxial power of the lens. And based on the refractive index of the lens material, the central thickness of the lens, and the shapes of the front and back surfaces of the lens, the conic constant K is selected.

[0037] When the correction is for astigmatism, at least one of the lens surface shapes is biconic, having a conical profile in two orthogonal principal directions. In a preferred embodiment, the toric optical system has an equivalent biconvex surface design where each surface is biconic. The non-toric optical system has an equivalent biconvex surface design where each surface is conical. For both the biconic surface case and the conical surface case, the optimal conic constant K of the surface is determined using optical ray tracing known to those skilled in the art.

[0038] Multifocal. Some patients may prefer a multifocal optical system that provides vision correction at a specific distance. One example is a bifocal optical system that generally provides the ability to focus on both near and far vision. Another example is a trifocal optical system that can focus on near, intermediate, and far vision. In either case, to implement a multifocal IOL, the optical zone is changed using refractive or diffractive optical regions so that these focal zones are obtained, and the virtual aperture is left outside the last focal zone.

[0039] In some applications, the virtual aperture may appear as an annular region with optical zones on both sides of the annular region. Also, the shape of the annular virtual aperture can be a freeform shape, for example, to accommodate an astigmatic optical zone or an asymmetric haptic region. This is shown in FIG. 8. In this figure, since lens A shows an oval (or elliptical) optical zone, the inner contour of the virtual aperture must conform to that shape. Since the contour of the inner haptic zone is circular, the outer contour of the virtual aperture is circular. In this figure, since lens B depicts the optical zone as circular, the inner contour of the virtual aperture is circular. Since the contour of the inner haptic is oval (or elliptical), the outer contour of the virtual aperture is oval (or elliptical). In either case, there is a transition region between each zone, and each region is smoothly connected so that visual artifacts do not enter the eye. Instead, the width of the transition region can be made variable so that the inner and outer contours of the virtual aperture can be of a desired shape.

[0040] The IOL designs contemplated herein can be made from any biocompatible optical material commonly used in IOLs, including hard and soft materials. Also, they can be manufactured using CNC machines, molds, or other methods used in the manufacture of IOLs. The virtual aperture can be realized (or implemented) as a one-dimensional profile symmetric in the azimuthal direction or as a two-dimensional profile realizing a microlens region.

[0041] In FIG. 9, azimuthally symmetric radial profiles (or radial profiles) are shown. The profiles can all be made the same or adjusted in the azimuthal direction. These profiles may be essentially refractive or diffractive. Eight different radial profiles are illustrated, but the radial profiles are continuous in the azimuthal direction. The radial profiles may alternately have positive and negative powers, or may have sections of all positive power (or positive power) or all negative power (or negative power). The connection between all power regions is smooth, preventing visual artifacts.

[0042] FIG. 10 shows other symmetric radial profiles that include, in addition to or instead of, the high-power curves shown in FIG. 8, a combination of a planar, negative power, and ramped basic shape. Referring to FIG. 10, element A depicts a simple planar basic shape. In FIG. 10, element B depicts a negative power basic shape. This general negative power curve shape can be represented by a portion of a sphere, a cone, or a higher-order curve such as a polynomial. Element C of FIG. 10 depicts a segmented, negative power profile of element B, segmenting the curve similar to a Fresnel lens to keep the overall thickness of the lens thin. Element D of FIG. 10 shows a profile of a ramped basic shape, and element E of FIG. 10 shows a segmented version of the ramped basic shape. The ramp is segmented similar to a Fresnel lens to keep the overall thickness of the lens thin. The segmented profiles of elements C and E are shown as having sharp discontinuities, but in reality, to prevent observable artifacts due to the sharp discontinuities, the boundaries of the segments are realized (or implemented) using a smooth function such as a fillet or a Bézier curve. Further, as described in other parts of this specification, a smooth transition region is placed between the visual zone (or optical zone) and the virtual aperture. These basic shapes can be used in combination with or instead of the high-power function to improve the effect of the virtual aperture.

[0043] FIG. 11 shows a two-dimensional lens region oriented with polar sampling. The high-power lens alternates positive and negative power in both the radial and azimuthal directions. The figure shows two positive-power lenses and two negative-power lenses. The actual shape of these two-dimensional polar lenses is similar to the radial profile.

[0044] Alternatively, the two-dimensional high-power lens may be all positive lenses or all negative lenses. In this case, the high-power lenses are separated by small smooth transition regions (e.g., continuous polynomial interpolation such as a Bézier curve) to prevent visual artifacts. This is a preferred two-dimensional high-power lens structure when there are multiple lens sample rates in the azimuthal direction. In this case, the individual lenses appear like small pillows, which are above the reference plane for positive power lenses and below the reference plane for negative power lenses.

[0045] Figure 12 shows one shape of a two-dimensional high-power lens. The upper right part of the figure shows a front view of the high-power lens. There is a central high-power optical region and a transition region surrounding it. Let the radial spread of this region be r, the width of the transition region be t, and the azimuthal subtense be theta (θ). The lower left part of the figure shows a side view of one lens profile. The central part represents the high-power optical zone, and the two side curves (side curves) represent the transition zones. The junction between the optical zone and the transition zone has 0th and 1st order continuity. At the edge of the lens boundary, the transition part coincides with the basic shape of the virtual aperture (typically the vertical line of the IOL). At the edge of the lens, there is also 0th and 1st 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 spread r is approximately equal to the arc length of the central part of the region.

[0046] The central optical zone is designed using standard IOL design concepts and can provide higher-order corrections such as spherical aberration control in addition to correction of sphere, cylinder, and axis. These design concepts are known to those skilled in the art.

[0047] The preferred virtual aperture profile shown in FIG. 4 is an alternating arrangement of positive lens profiles and negative lens profiles (positive-negative alternating lens profiles) with a focal length on the order of + / - 1.5 mm. The profiles of these lens surfaces can be generated using conical shapes, polynomials (such as cubic Bezier splines), rational splines, and combinations of these with other curves. The lens profile shape is selected such that it can appropriately disperse the transmitted light onto the retina while being relatively easy to manufacture using a precision lathe or a molding process. It is also possible to arrange a smooth surface on one profile (e.g., the front surface) and the profile of a small high-power lens on the other profile (e.g., the back surface).

[0048] Using the preferred virtual aperture profile shown in FIG. 4, even for a high-power IOL, the edge thickness of the IOL and the central thickness of the central optical zone can be made considerably thinner. The lens material is the same as that used in other soft or hard IOL designs.

[0049] The IOL design provides very good and high-definition distance vision, and the range of "clear vision" can be controlled by the specifications of what "clear vision" means (e.g., 20 / 40 visual acuity) and by the relative size of the central vision zone (or optical zone) and the virtual aperture width. A simple formula for estimating visual acuity by giving the pupil diameter and spherical refractive error [by G. Smith, "Relation between spherical refractive error and visual acuity", Optometry Vis. Sci. 68, 591-8, 1991] is given by Equations (1a) and (1b).

[0050]

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[0051] Here,[[]]END]] A = Visual acuity (unit: minute of arc) (A = Sd / 20), that is, the minimum angle of resolution. k = A constant determined from clinical studies, and the average value is 0.65. D = Pupil diameter (unit: mm) E = Spherical refractive error (unit: diopter) Sd = Snellen denominator is.

[0052] The second formula is assumed to be more accurate for low levels of refractive error and gives reasonable results. When E = 0, A = 1 minute of arc or 20 / 20. Solving equation (1b) for E gives equation (2).

[0053]

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[0054] Equation (1b) represents the visual acuity A when the range of depth of focus (E×2) (unit: diopter) and pupil diameter D are given. Equation (2) represents the range of depth of focus (unit: diopter) when visual acuity A and pupil diameter D are given. For example, it is as follows. When the visual acuity is 20 / 40, A = 40 / 20 = 2 minutes of arc D = 3.0 mm k = 0.65

[0055]

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[0056] The depth of focus = 2E = 1.8D. Using (1b), the following equation is obtained.

[0057]

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[0058] The concept of a virtual aperture can be employed in a fake or aphakic IOL, corneal transplantation, contact lenses, or used in the techniques of corneal laser surgery (such as LASIK, PRK, etc.) to provide an extended depth of focus and / or a high-definition view. Also, it would be possible to replace the virtual aperture with an actual opaque aperture to achieve optical advantages similar to those of the virtual aperture.

[0059] Although specific forms of the present invention are shown, it should be understood that the present invention is not limited to the specific 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 present invention, and the present invention should not be considered limited to what is shown and described in this specification and any drawings / figures included herein.

[0060] Those skilled in the art will readily understand that the present invention is well adapted to carry out the objectives and obtain the mentioned objectives and advantages, as well as those inherent therein. The embodiments, methods, procedures, and techniques described herein currently represent the preferred embodiments and are intended for illustration and not for limitation of scope. Changes and other uses thereof will occur to those skilled in the art, and they are encompassed by the spirit of the present invention and defined by the scope of the appended claims. Although the present invention has been described in relation to specific preferred embodiments, it should be understood that the present invention as claimed should not be unduly limited to such specific embodiments. Indeed, various changes to the described modes of carrying out the present invention that are obvious to those skilled in the art are intended to be within the scope of the following claims.

Claims

1. An intraocular lens that provides improved vision by evenly spreading defocused light rays caused by aberrations due to the influence of light on an individual's eye over the individual's retina, comprising: an intraocular lens having a virtual aperture connected to an optical zone by a first transition region and a haptic connected to the virtual aperture by a second transition region; wherein the shape of the optical zone is different from the shape of the inner contour of the haptic; the virtual aperture can be realized as a high-power positive lens and a negative lens; light rays intersecting the transition region and the virtual aperture are evenly distributed on the retina using refraction, reducing monochromatic aberration, chromatic aberration, and defocus resulting from changes in focal length, thereby improving the individual's depth of focus; An intraocular lens, wherein the width of the transition zone of the virtual aperture is variable.

2. The intraocular lens according to claim 1, wherein the shape of the optical zone is circular and the shape of the inner contour of the haptic is elliptical.

3. The intraocular lens according to claim 1, wherein the shape of the optical zone is elliptical and the shape of the inner contour of the haptic is circular.

4. The intraocular lens according to any one of claims 1 to 3, wherein the optical profile has a positive power.

5. The intraocular lens according to any one of claims 1 to 3, wherein the optical profile has a negative power.

6. The intraocular lens according to any one of claims 1 to 5, wherein the intraocular lens is composed of a biocompatible material.

7. The intraocular lens according to any one of claims 1 to 6, wherein the high-power positive and negative lenses are selected from the group consisting of a series of conical, polynomial, rational spline, and diffractive profiles.

8. The intraocular lens according to any one of claims 1 to 7, wherein the virtual aperture is configured and arranged such that posterior capsular opacification treatment using a Nd:YAG laser is possible.

9. The intraocular lens according to any one of claims 1 to 8, wherein the optical zone is configured and arranged to correct spherical aberration.

10. The intraocular lens according to any one of claims 1 to 9, wherein the lens surface shape of the optical zone is a biconical shape configured and arranged to correct astigmatism.

11. The intraocular lens according to any one of claims 1 to 10, wherein the optical profile is arranged on the front or back surface of the intraocular lens.

12. The optical profile is disposed on the front and back surfaces of the intraocular lens, the intraocular lens according to any one of claims 1 to 10.

13. The virtual aperture is shaped to promote the occurrence of light scattering, the intraocular lens according to any one of claims 1 to 10.

14. The optical zone provides one or more focal refractive powers, the intraocular lens according to any one of claims 1 to 13.

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