CN113423362A - Intraocular lens design for optimal clinical outcome - Google Patents

Intraocular lens design for optimal clinical outcome Download PDF

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CN113423362A
CN113423362A CN202080015006.XA CN202080015006A CN113423362A CN 113423362 A CN113423362 A CN 113423362A CN 202080015006 A CN202080015006 A CN 202080015006A CN 113423362 A CN113423362 A CN 113423362A
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shape factor
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月爱·刘
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Airui Technology Co.,Ltd.
HENAN UNIVERSE INTRAOCULAR LENS RESEARCH & MANUFACTURE Co.
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/14Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/16Intraocular lenses
    • A61F2/1613Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • A61F2/1637Correcting aberrations caused by inhomogeneities; correcting intrinsic aberrations, e.g. of the cornea, of the surface of the natural lens, aspheric, cylindrical, toric lenses
    • A61F2/164Aspheric lenses
    • GPHYSICS
    • G02OPTICS
    • G02CSPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C2202/00Generic optical aspects applicable to one or more of the subgroups of G02C7/00
    • G02C2202/22Correction of higher order and chromatic aberrations, wave front measurement and calculation
    • GPHYSICS
    • G02OPTICS
    • G02CSPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C7/00Optical parts
    • G02C7/02Lenses; Lens systems ; Methods of designing lenses

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Abstract

An intraocular lens (IOL) for implantation in the posterior chamber of the capsular bag of the human eye, such as but not limited to: single focus, toric, multi-focus, or extended depth of field. The IOL has a generally disc-shaped optic with two flexible haptics projecting outwardly from opposite points of the optic to secure the IOL within the capsular bag. The optic portion has an anterior surface radius of curvature Ra and a posterior surface radius of curvature Rp defining a shape factor (X), wherein X = (Ra + Rp)/(Ra-Rp) such that the IOL's shape factor is less than zero and at least one of the anterior or posterior surfaces has sag to impart a specific spherical aberration to the IOL to compensate for the normal positive spherical aberration of the human cornea.

Description

Intraocular lens design for optimal clinical outcome
Cross Reference to Related Applications
This application claims priority from U.S. provisional patent application No. 62/872, 008, filed on 7/9/2019. The entire disclosure of the prior application is considered to be part of the disclosure of the appended application and is hereby incorporated by reference.
Background
1. Field of the invention
The present disclosure relates generally to intraocular lens designs that reduce adverse effects on the clinical performance of the lens associated with decentration and/or tilt due to surgically induced misalignment of the lens and changes in corneal spherical aberration in a patient population, and more particularly to intraocular lenses having aspherical profiles and exhibiting a certain amount of spherical aberration and a range of shape factors.
2. Description of the related Art
Nicholas was considered the parent of the intraocular lens (IOL) first implanted in 1949. Although complications require removal of the intraocular lens, the next year of surgery succeeds with the implanted intraocular lens remaining permanently in the eye. Ridley continues his work and has enjoyed great success in human implantation of intraocular lenses in the 1960 s. Cataract extraction surgery for intraocular lens implantation is now the most common type of ophthalmic surgery. The success of IOL implantation surgery has led to the rise of more complex surgical procedures and increasingly complex IOL designs that have improved the quality of life for many people. However, there are still some problems with intraocular lens implantation procedures, one of which is misalignment in the form of decentering and tilting of the intraocular lens after implantation. Symptoms of misaligned IOLs can range from ghosting and diplopia of objects to astigmatism. Clinically, the effects of IOL malpositioning can be measured in terms of Visual Acuity (VA) and Contrast Sensitivity (CS).
Decentration occurs when the optical axis of the IOL is offset from the visual axis of the eye, such that the visual axis of the eye and the optical axis of the IOL are parallel to each other but at some offset. Decentration of the IOL may be the result of surgical placement of the lens, and may also occur during post-surgery due to external (e.g., trauma, rubbing of the eye) or internal forces (e.g., scarring or capsular contraction). FIG. 1A schematically illustrates IOL 10 properly positioned in an eye behind cornea 12 such that visual axis 14 of the eye and optical axis 16 of IOL 10 coincide with one another. Fig. 1B shows decentration of IOL 10 at optical axis 16 offset a distance 18 from visual axis 14.
The lens tilt is defined as the angle between the optical axis of the artificial lens and the visual axis of the eye. Tilting of the IOL may be a result of inaccurate IOL surgical positioning, lack of capsular membrane support, scleral tunnel positioning, and the like. Tilt is shown in FIG. 1C, where the optical axis 16 of IOL 10 is at some angular offset 20 from the visual axis 14 of the eye.
IOLs decentered by more than 1mm or tilted by more than 5 degrees significantly reduce VA and CS. In addition, multifocal or toric IOLs can exacerbate the effects of decentration or tilt, and therefore decentration of less than 1mm or tilt of less than 5 degrees can adversely affect VA and CS. While it is becoming more common to place an IOL correctly within the capsular bag as surgical techniques improve, decentration and/or tilt can occur even after surgery is successful. It is therefore important to reduce the amount of decentration and/or tilt of an implanted IOL by not only utilizing improved surgical techniques, but also by incorporating certain design features into the IOL, thereby desensitizing the clinical performance of the IOL from decentration and/or tilt as disclosed herein.
Spherical aberration naturally occurs on the human cornea, with a population mean of about 0.28 mm. By virtue of the aspherical design of the IOL, negative spherical aberration can be generated in the intraocular lens to counteract this corneal aberration, so that the vision of the patient using the intraocular lens is virtually free of spherical aberration.
US patent US5,336,262 to Chu discloses an intraocular lens suitable for scleral fixation having a disk-shaped lens optic with two flexible haptics projecting outwardly from opposite points of the lens optic periphery. Each haptic includes one or more suture holes for suturing the haptic to the ciliary sulcus of the eye during the implantation procedure. The suture holes are positioned such that they are substantially at the apex of the haptics when the lens is implanted and the haptics have been bent inward a predetermined amount. Chu indicates that this configuration minimizes the possibility of lens tilt and decentration. However, the length of the suture increases complications during the procedure. Long-term monitoring of patients with sutured intraocular lenses has identified certain suture-related complications such as scleral and conjunctival erosion, suture-induced inflammation, suture degeneration, and late or subluxation of the intraocular lens following suture rupture. The problems of decentration and tilt are preferably alleviated by the use of a sutureless intraocular lens.
US patent US7,381,221 to Lang et al discloses a multi-zone monofocal intraocular lens comprising an inner zone, a middle zone, and an outer zone. The inner zone has a first optical power. An intermediate zone surrounds the inner zone and has a second optical power that differs from the first optical power by an amount that is less than at least about 0.75 diopters. An outer zone surrounds the intermediate zone and has a third optical power different from the second optical power. Lang states that the intermediate zone may also provide correction in the event of lens decentration or tilt when the correction force of the intermediate zone is less than the correction force of the inner zone. Lang's lens may have inherent tolerances for decentration or tilt, but conceptually it is not a monofocal lens.
What is needed is a suture-free IOL design that provides optimal clinical results through an optimized design of its shape factor and spherical aberration.
Disclosure of Invention
A series of monofocal or equivalent spherical base curve multifocal, toric or extended depth-of-focus IOLs having an optical power for implantation in an eye having a cornea, comprising: a front surface having a front radius; and a posterior surface having a posterior radius, wherein one of the surfaces is aspheric; wherein the anterior and posterior radii and the refractive index of the lens material determine diopters; and wherein the anterior and posterior radii determine a shape factor of the lens that is negative and selected to minimize adverse effects of decentration and/or tilt of the lens.
An embodiment of a previous lens with a surface wherein any number of combinations of shape factors, conic constants and/or aspheric coefficients can be modified to produce a specific spherical aberration that, when combined with the spherical aberration of the cornea, minimizes the overall spherical aberration of the cornea and intraocular lens system. Another embodiment is a series of IOLs ranging from low to high power having a shape factor in the range of-0.45 to-0.8. The variable shape factor in degrees allows sharing of the radius of curvature of one of the two surfaces of the lens. This embodiment shows the front surface radius of curvature shared between several adjacent refractive powers. This sharing strategy can be used to reduce the engineering complexity of lens manufacture.
Further areas of applicability of the present invention will become apparent from the detailed description provided hereinafter. It should be understood that the summary and specific examples, while indicating the preferred embodiment of the invention, are intended for purposes of illustration only and are not intended to limit the scope of the invention.
Neither this summary nor the following detailed description defines or limits the invention. The invention is defined by the claims.
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The present invention will become more fully understood from the detailed description and the accompanying drawings, wherein:
FIG. 1A shows a schematic view of an IOL properly positioned within an eye, showing the cornea of the eye, wherein the optical axis of the IOL is coincident with the visual axis of the eye.
FIG. 1B shows a schematic view of a distributed IOL within an eye showing the cornea of the eye with the IOL's optical axis parallel to the visual axis of the eye.
FIG. 1C shows a schematic view of a tilted IOL in an eye showing the cornea of the eye with the optical axis of the IOL angularly offset from the visual axis of the eye.
FIG. 2 shows a graph depicting the relationship between Zernike Standard Coefficient (Zernike Standard) Z11, which is a type of spherical aberration, and the shape factor of an IOL.
FIG. 3A shows a graph depicting the relationship between the Zernike standard factor Z11 and the IOL's shape factor for a power of 10 diopters.
FIG. 3B shows a graph depicting the relationship between the Zernike standard factor Z11 and the IOL's shape factor for a power of 20 diopters.
FIG. 3C shows a graph depicting the relationship between the Zernike standard factor Z11 and the IOL's shape factor for a power of 30 diopters.
Figure 4 shows a graph depicting the performance of a medium power IOL aspheric design in terms of MTF with a spherical aberration of 0.0mm at a 3mm aperture for ISO model eye 2.
FIG. 5 shows a graph depicting the performance of a medium power IOL aspheric design in terms of MTF with-0.14 mm spherical aberration at a 3mm aperture for ISO model eye 2.
FIG. 6 shows a graph depicting the performance of a medium power IOL aspheric design in terms of MTF with-0.28 mm spherical aberration at a 3mm aperture for ISO model eye 2.
Figure 7 shows a performance graph depicting the MTF of a medium power IOL aspheric design with a spherical aberration of 0.0mm at a 5mm aperture for ISO model eye 2.
FIG. 8 shows a performance graph depicting a moderate-power IOL aspheric design in terms of MTF with-0.14 mm spherical aberration at a 5mm aperture for ISO model eye 2.
FIG. 9 shows a performance graph depicting a moderate-power IOL aspheric design in terms of MTF with-0.28 mm spherical aberration at a 5mm aperture for ISO model eye 2.
Figure 10 shows a table containing relevant lens parameters for the first embodiment of an IOL power series having an aspherical anterior lens and a spherical posterior lens, where Ra and Rp yield a shape factor of-1.5 and a spherical aberration value of-0.19 mm.
Figure 11 shows a table containing relevant lens parameters for a second embodiment of an IOL power series having an aspherical anterior lens and a spherical posterior lens, where Ra and Rp yield a shape factor between-0.45 and-0.75 and a spherical aberration value of-0.12 mm.
Detailed Description
It is to be understood that the figures and descriptions provided herein may have been simplified to illustrate elements that are relevant for a clear understanding of the present invention, while eliminating, for purposes of clarity, other elements found in typical vision correcting lenses, lens systems, and methods. One of ordinary skill in the art may recognize that other elements and/or steps may be required and/or required to implement the apparatus, systems, and methods described herein. However, because such elements and steps are well known in the art, and because they do not facilitate a better understanding of the present invention, a discussion of such elements and steps may not be provided herein. The disclosure is deemed to inherently include all such elements, variations and modifications of the disclosed elements and methods known to those of ordinary skill in the relevant art.
The present invention includes a series of IOL designs that reduce sensitivity to changes in spherical aberration present on a patient's cornea as well as clinical decentration and tilt of the IOL; as depicted in fig. 1A, 1B and 1C; measured by the Modulus Transfer Function (MTF) performance, also known as the modulus of the OTF (optical transfer function). MTF is a measure of visual performance, which can be plotted vertically on a dimensionless scale from a minimum of 0.0 to a maximum of 1.0, relative to the horizontal range of one-dimensional attributes. As the MTF approaches 1.0, the VA or CS of the optical system will also increase. Conversely, as the MTF approaches 0.0, the VA or CS of the optical system also decreases. Theoretically, the MTF of any optical system, including the human eye, never reaches 1.0 at any spatial frequency other than 0. In this disclosure, the MTF will be plotted vertically in millimeters for a property called "focus shift. The focus offset represents the distance between the desired focus (i.e., the retina) and the actual focus in the eye. Negative focus offset indicates that focus is in front of the retina, while positive focus offset indicates that focus is behind the retina. In emmetropia, the focus offset is zero, i.e. an image is formed on the retina, resulting in excellent VA and CS. As the focus of the image moves away from the retina, the MTF decreases, indicating that VA or CS has degenerated. The lens system in the eye of the present disclosure includes the cornea and the IOL, and is also referred to as an pseudophakic eye. However, the principles disclosed herein may also be applied to lens systems including the cornea, IOLs, and phakic eyes known as phakic eyes.
This IOL design, which reduces sensitivity to decentration and tilt of the IOL, is based on the IOL's base lens shape factor. IOLs consist of a disc portion, which is a crystalline lens, typically having two or more side struts, called haptics, extending therefrom. The haptics hold the disc portion within the capsular bag of the eye. The IOL deflects light through the structure of the disk and the structure of any surface effects on the anterior or posterior surface of the disk. For the purposes of this disclosure, a base lens is a lens defined by the structure of the disc and represented as a shape factor. The shape factor is dimensionless and is determined from the radius of the anterior-posterior curvature of the lens according to ISO-11878:1 using the following formula:
Figure 100002_DEST_PATH_IMAGE002
(formula 1)
Where Ra and Rp are the anterior and posterior radii of curvature of the lens, respectively. The shape factor of the lens can also be defined by:
Figure 100002_DEST_PATH_IMAGE004
(formula 2)
Where Ca and Cp are the anterior and posterior curvatures of the lens, respectively. Finally, it can be confirmed that
Figure DEST_PATH_IMAGE006
(formula 3)
In the present disclosure, the shape factor is defined by equation 1.
It is well known that the spherical aberration of spherical single crystals is affected by the lens shape factor. FIG. 2 shows the relationship between Zernike standard factor Z11 for spherical aberration type in the wave and the IOL shape factor. The intraocular lens of fig. 2 has an average optical power, in particular 20D, is made of lens material with n =1.55 and has a medium with n = 1.336. The results are shown in FIG. 2, which shows that IOLs with increasingly negative shape factors produce increasingly positive Zernike (Zernike) spherical aberrations. Conversely, IOLs with increasingly positive shape factors produce increasingly negative Zernike spherical aberrations. The sign of the form factor conforms to the definition in equation (1). The sign of the wavefront aberration also corresponding to Zemax®The wavefront sign convention is consistent. Zemax®A series of optical system design software is sold and can be used for modeling and simulating a lens system in human eyes. Their software was used for the next analysis.
The cornea is the first lens element of the human eye and typically has positive spherical aberration because the human cornea has an oblong shape that produces a negative corneal Q value. In fig. 2, it is shown that a lens with a positive shape factor has essentially negative spherical aberration. It has therefore become natural for an intraocular lens with a certain positive shape factor to be able to compensate for the positive spherical aberration present on the human cornea. An intraocular lens with such a positive form factor will possess an "optimal form" that reduces the overall spherical aberration of an aphakic eye. Prior art, such as U.S. patent publication No. 2006/0227286 to Xinhong entitled "Optimal IOL shape factor for human eye", utilizes lens characteristics with a positive shape factor to reduce spherical aberration. However, the present invention does not take advantage of the shape factor of the lens to reduce spherical aberration. Rather, it is optimized for optimal clinical outcomes of the IOL product.
Another factor to consider is the effect of power and shape factor on the spherical aberration present in the IOL. Fig. 2 shows the effect of the lens shape factor on the spherical aberration lens as discussed above. However, as the lens shape factor changes, the power of the lens also has an effect on spherical aberration. Figures 3A, 3B and 3C show that IOLs having lower powers will exhibit lower absolute Z11 spherical aberration than IOLs having higher powers. These figures show the relationship between the IOL's shape factor and Z11 at a 6mm aperture for a given IOL power, with the solid line showing Z11 in waves and the dashed line showing Z11 in microns and a shape factor in the range of-2.0 to 2.0. Figure 3A shows the absolute value of Z11 at a 6mm aperture in the wave for a 10 diopter IOL, ranging from zero to about 0.025, while figure 3C shows the absolute value of Z11 for a 30 diopter IOL, ranging from zero to about 0.5. FIG. 3B shows the absolute value of Z11 at an intra-wave aperture of 6mm, ranging from zero to about 0.17, for a 20 diopter IOL. Thus, different shape factors and/or aspheric parameters for each lens may be used for the lens power series design for the same spherical aberration correction.
Figures 4-9 show different simulations in graphical form to demonstrate IOL performance with various shape factors under three conditions: when coaxial, the IOL is properly positioned on the capsular bag; at 1.0mm eccentricity, where the eccentricity 20 of FIG. 1B is 1 mm; at a 5 deg. tilt, where the tilt angle 22 shown in fig. 1C is five degrees. For each of the three conditions, nine simulations were run for the following form factors: -2.0, -1.5, -1.0, -0.5, 0, 0.5, 1.0, 1.5 and 2.0. Figures 4 to 9 contain a total of 27 graphs representing 27 simulations. The y-axis of each plot ranges from 0.0 to 1.0 and represents the MTF determined by the simulation. As previously described, as the MTF approaches 1.0VA and CS improves, while as the MTF approaches 0VA and CS degrades. The x-axis of each plot ranges from-0.3 mm to 0.3 mm, representing a focus offset from zero or the retina. The four lines in each graph are defined as follows:
the solid line shows the simulation results for a resolution of 50lp/mm in the sagittal plane.
The dotted line shows the simulation results for a resolution of 100lp/mm in the sagittal plane.
The dotted line shows the simulation results for a resolution of 50lp/mm in the tangential plane.
The dotted line shows the simulation results for a resolution of 100lp/mm in the tangential plane.
The resolution is defined by the frequency measured in pairs of lines per millimeter (lp/mm). The greater the number of pairs per millimeter, the greater the difficulty for the human eye to resolve the pairs, and thus the lower the MTF. When the IOL is properly placed in the capsular bag, as shown by the axial condition, the tangential and sagittal performance are the same, so the simulated coaxial columns only show the solid line of MTF performance at 50lp/mm and the dashed line of MTF performance at 100 lp/mm.
FIG. 4 shows simulations for three conditions for various shape factors of an aspheric medium power IOL for a 3mm aperture and a 0.0mm spherical aberration. FIG. 5 is similar to FIG. 4, but with a spherical aberration of-0.14 millimeters. FIG. 6 is similar to FIG. 4, but with a spherical aberration of-0.28 millimeters. FIG. 7 shows simulations for three conditions for various shape factors for an aspheric medium power IOL with a 5mm aperture and a 0.0mm spherical aberration. FIG. 8 is similar to FIG. 7, but with a spherical aberration of-0.14 millimeters. FIG. 9 is similar to FIG. 7, but with a spherical aberration of-0.28 millimeters. All simulations were performed using an ISO model eye 2 with a spherical aberration match to the IOL.
Through many simulations in fig. 4 through 9, it is shown that MTF performance decreases as the form factor increases. This is particularly evident when comparing the MTF performance with a shape factor of-2.0 to the MTF performance with a shape factor of 2.0. Thus, the simulation results shown in FIGS. 4-9 indicate that IOLs with negative shape factors exhibit better lens dislocation resistance to decentration and tilt than IOLs with positive shape factors. However, as previously described, an intraocular lens having a negative shape factor cannot compensate for positive spherical aberration present on a human cornea, as shown in fig. 2 and 3. Still other attributes of an intraocular lens are to change the spherical aberration of the intraocular lens without changing its form factor, primarily by using an aspheric design, including the conic constants and aspheric parameters of the lens surfaces. The following even aspheric equation is a general form describing lens surface sag that is effective in spherical aberration correction.
Figure DEST_PATH_IMAGE008
(formula 4)
Where r is the lens aperture radius, c is the lens surface coverage, k is the conic constant, and ai is the aspheric coefficient. Thus, there are a number of combinations of shape factors, conic constants, and aspheric coefficients for IOL optical designs to achieve reduced spherical aberration. Accordingly, an aspheric intraocular lens with a negative shape factor can be designed to achieve spherical aberration reduction and performance stability in the case of mild/reasonable clinical misalignments.
As shown in equation 4, a variety of different IOL designs having a common shape factor but different diopters, IOL anterior-posterior radii of curvature or aspheric coefficients can be achieved. The shape factor and aspheric parameters can be optimized for optimal clinical results.
Figure 10 shows a first embodiment in which, for a 5mm model eye, the series of lenses in which the anterior surface is aspherical and the posterior surface is spherical, where the spherical aberration of the IOL cancels out the spherical aberration of the cornea. The aspheric coefficients a4, a6, and A8 were determined so that each lens in the series had a shape factor of-1.5 and a spherical aberration of-0.19 millimeters. The MTF25 shows the MTF value at focus with zero decentration and zero tilt at 25 lp/mm. The MTF50 shows the MTF value at focus with zero decentration and zero tilt at 50 lp/mm. MTF100 shows MTF values at 100lp/mm with zero decentration and zero tilt focus. The refractive index of the lens material is n = 1.483.
Figure 11 shows a second embodiment in which, for a 5mm model eye, the series of lenses in which the anterior surface is spherical and the posterior surface is aspherical, the spherical aberration of the IOL canceling that of the cornea. The aspheric coefficients a4 and a6 were determined so that each lens in the series had a shape factor in the range of-0.75 to-0.45 and a spherical aberration of-0.12 millimeters. The MTF25 shows the MTF value at focus with zero decentration and zero tilt at 25 lp/mm. The MTF50 shows the MTF value at focus with zero decentration and zero tilt at 50 lp/mm. MTF100 shows the MTF value at focus with zero decentration and zero tilt at 100 lp/mm. The refractive index of the lens material is n = 1.483.

Claims (10)

1. An intraocular lens for implantation in an eye of a patient, wherein the natural lens has been removed, the eye having a cornea, the intraocular lens comprising optics, wherein the features comprise:
a front surface and a back surface opposite the front surface, the front and back surfaces intersecting an optical axis, the optic being symmetric about the optical axis and exhibiting a shape factor X defined according to the following formula;
Figure DEST_PATH_IMAGE002
wherein Ra is the radius of curvature of the anterior surface and Rp is the radius of curvature of the posterior surface;
an aspheric surface on at least one of the anterior surface and the posterior surface, wherein the aspheric surface reduces spherical aberration of the cornea; and
the shape factor is less than zero.
2. The intraocular lens of claim 1, wherein the aspheric surface has a sag Z defined by an even aspheric formula:
Figure DEST_PATH_IMAGE004
where r is the lens aperture radius, c is the lens surface coverage, k is the conic constant, ai is the aspheric coefficient.
3. The intraocular lens of claim 1, wherein the shape factor is in a range of-2.0 to 0.
4. A family of intraocular lenses comprising a plurality of individual intraocular lenses for implantation in a patient's eye wherein the natural lens has been removed, the eye having a cornea, the intraocular lenses comprising optics, wherein the features comprise:
a front surface and a back surface opposite the front surface, the front and back surfaces intersecting an optical axis, the optic being symmetric about the optical axis and exhibiting a shape factor X defined according to the following formula;
Figure 120251DEST_PATH_IMAGE002
wherein Ra is the radius of curvature of the anterior surface and Rp is the radius of curvature of the posterior surface;
an aspheric surface on at least one of the anterior surface and the posterior surface, wherein the aspheric surface reduces spherical aberration of the cornea; and
the shape factor is less than zero.
5. The series of intraocular lenses of claim 1, wherein said aspheric surface has a sag Z defined by an even aspheric formula:
Figure DEST_PATH_IMAGE005
where r is the lens aperture radius, c is the lens surface coverage, k is the conic constant, ai is the aspheric coefficient.
6. The series of intraocular lenses of claim 1, wherein the shape factor is in the range of-2.0 to 0.
7. The series of intraocular lenses of claim 4, wherein the shape factor is the same for each of the individual intraocular lenses.
8. The series of intraocular lenses of claim 4, wherein each of the individual intraocular lenses has a different lens power.
9. The series of intraocular lenses of claim 4, wherein the aspherical spherical aberration is the same for each of the individual intraocular lenses.
10. The series of intraocular lenses of claim 4, wherein the refractive index (n) is in the range of 1.4 to 1.5.
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