CA2618021A1 - Accommodating diffractive intraocular lens - Google Patents
Accommodating diffractive intraocular lens Download PDFInfo
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- CA2618021A1 CA2618021A1 CA002618021A CA2618021A CA2618021A1 CA 2618021 A1 CA2618021 A1 CA 2618021A1 CA 002618021 A CA002618021 A CA 002618021A CA 2618021 A CA2618021 A CA 2618021A CA 2618021 A1 CA2618021 A1 CA 2618021A1
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- optical surface
- diffractive optical
- intraocular implant
- lens body
- shape
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/02—Prostheses implantable into the body
- A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
- A61F2/16—Intraocular lenses
- A61F2/1613—Intraocular 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
- A61F2/1624—Intraocular 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 having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside
- A61F2/1635—Intraocular 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 having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside for changing shape
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/02—Prostheses implantable into the body
- A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
- A61F2/16—Intraocular lenses
- A61F2/1613—Intraocular 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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/02—Prostheses implantable into the body
- A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
- A61F2/16—Intraocular lenses
- A61F2/1613—Intraocular 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
- A61F2/1654—Diffractive lenses
Abstract
One disclosed embodiment of an intraocular implant includes a lens body. The lens body comprises a diffractive optical surface (115) having diffractive properties which produce an interference pattern. The lens body is sized and shaped for placement in an anterior portion of a human eye. The lens body is sufficiently flexible to change the shape of the diffractive optical surface in response to ciliary muscle (60) action so that the interference pattern is modified.
Description
ACCOMMODATING DIFFRACTIVE INTRAOCULAR LENS
BACKGROUND
Field [0001] Certain einbodiments disclosed herein relate to intraocular lenses and, more particularly, to intraocular lenses that pen7iit accominodation.
Description of the Related Art
BACKGROUND
Field [0001] Certain einbodiments disclosed herein relate to intraocular lenses and, more particularly, to intraocular lenses that pen7iit accominodation.
Description of the Related Art
[0002] It is a common practice to implant an artificial lens in an eye following such procedures as the removal of a cataract. However, certain currently lcnown artificial lenses suffer from various drawbacks.
SUMMARY
SUMMARY
[0003] In certain embodiments, a metliod coinprises providing an intraocular lens. The intraocular lens conlprises a diffractive optical surface having diffractive properties which produce an interference patteni. The method further coinprises implanting the lens in an eye of a patient such that the diffractive optical surface changes shape in response to action of an ocular structure of the eye. The interference pattern is modified in response to the action of the ocular structure.
[0004] fi1 some einbodiments, an intraocular implant coinprises a lens body.
The lens body comprises a diffractive optical surface having diffractive properties which produce an interference pattein. The lens body is sized and shaped for placement in an anterior portion of a human eye. The lens body is sufficiently flexible to change the shape of the diffractive optical surface in response to ciliaiy niuscle action so that the interference pattenl is modified. In some embodiments, at least about 80 percent of the optical output of the diffractive optical surface is in a single diffraction order.
The lens body comprises a diffractive optical surface having diffractive properties which produce an interference pattein. The lens body is sized and shaped for placement in an anterior portion of a human eye. The lens body is sufficiently flexible to change the shape of the diffractive optical surface in response to ciliaiy niuscle action so that the interference pattenl is modified. In some embodiments, at least about 80 percent of the optical output of the diffractive optical surface is in a single diffraction order.
[0005] Iii some einbodiments, an intraocular iinplant comprises an optical element sized for insertion into a human eye. The optical element has a diffractive optical surface. The diffractive optical surface has an unacconnnodated state in wliich the diffractive optical surface creates a first interference pattenl and an acconunodated state in which the diffractive optical surface creates a second interference pattern which differs fioni the first interference pattern. The optical element is sufficiently flexible to change fioin the unaccominodated state to the accoininodated state in response to ciliary muscle action.
[0006] In some einbodiments, an intraocular iinplant comprises an optical eleinent sized for insertion into a htunan eye. The optical element has a diffractive optical surface. The diffractive optical surface is alterable between a first shape that provides distant vision and a second shape that provides intennediate vision. Iii some embodiments, the diffiactive optical surface is alterable to a third shape that provides near vision.
BRIEF DESCRIPTION OF THE DRAWINGS
BRIEF DESCRIPTION OF THE DRAWINGS
[0007] FIGURE 1 is a cross sectional view of the liuman eye, witll the lens in the unaccoininodated state.
[0008] FIGURE 2 is a cross sectional view of the htunan eye, with the lens in the accoimnodated state.
[0009] FIGURE 3 schematically illtlstrates a cross sectional view of an embodiment of an intraocular lens iinplant having a diffractive optical surface.
[0010] FIGURE 4 scheinatically illustrates a partial cross sectional view of the intraocular lens iinplant of FIGURE 3.
[0011] FIGURE 5 schematically illustrates a perspective view of an intraocular lens unplant in an unacconunodated state.
[0012] FIGURE 6 schematically illustrates a perspective view of the intraocular lens iinplant of FIGURE 5 in an accommodated state.
[0013] FIGURE 7 scheinatically illustrates a cross sectional view of an intraocular lens iinplant coupled with the ciliary muscle of an eye in an unacconunodated state.
[0014] FIGURE 8 schematically illustrates a cross sectional view of the intraocular lens implant of FIGURE 7 coupled with the ciliary muscle of an eye in an accommodated state.
[0015] FIGURE 9 schematically illustrates a cross sectional view of an intraocular lens iinplant comprising two iinplants, one of which is in an unaccoirunodated state.
[0016] FIGURE 10 schematically illustrates a cross sectional view of the intraocular lens iinplant of FIGURE 9 with one of the iinplants in a.n accoininodated state.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0017] Many eye surgeries, such as cataract removals, involve the implantation of artificial lenses. Typically, artificial lenses have a fixed focal length or, in the case of bifocal or inultifocal lenses, have several different fixed focal lengths.
However, such fixed focal-length lenses lack the ability of the natural lens to dynainically change the optical power of the eye. Certain embodiments disclosed herein overcome this limitation, and additionally provide other advantages such as those described below.
However, such fixed focal-length lenses lack the ability of the natural lens to dynainically change the optical power of the eye. Certain embodiments disclosed herein overcome this limitation, and additionally provide other advantages such as those described below.
[0018] FIGURES 1 and 2 illustrate the human eye 50 in section. Of particular relevance to the present disclosure are the conlea 52, the iris 54 and the lens 56, which is situated within the elastic, membranous capsular bag or lens capsule 58. The capsular bag 58 is suiTounded by and suspended within the ciliary inuscle 60 by ligainent-like structures called zonules 62.
[0019] As light enters the anterior portion of the eye 50, the coniea 52 and the lens 56 cooperate to focus the incoming light and fonn an image on the retina 64 at the posterior of the eye, thus facilitating vision. hi the process known as accoiTunodation, the shape of the lens 56 is altered (and its refractive properties thereby adjusted) to allow the eye 50 to focus on objects at varying distances. A typical healthy eye has sufficient accoimnodation to enable focused vision of objects ranging in distance from infinity (e.g., over about 20 feet from the eye) to veiy near (e.g., closer than about 10 inches).
[0020] The lens 56 has a natural elasticity, and in its relaxed state assumes a shape that in cross-section resembles a football. Accommodation occurs when the ciliary inuscle 60 moves the lens from its relaxed or "unaccominodated" state (shown in FIGURE 1) to a contracted or "acconunodated" state (shown in FIGURE 2).
Movement of the ciliary inuscle 60 to the relaxed/unaccommodated state increases tension in the zonules 62 and capsular bag 58, which in tlun causes the lens 56 to take on a thimler (as measured along the optical axis) or taller shape, as shown in FIGLTRE 1. h1 contrast, wllen the ciliaiy muscle 60 is in the contracted/acconunodated state, tension in the zonules 62 and capsular bag 58 is decreased and the lens 56 talces on the fatter or shorter shape shown in FIGURE 2. Wllen the ciliary inuscles 60 contract and the capsular bag 58 and zonules 62 slacken, some degree of tension is maintained in the capsular bag 58 and zonules 62.
Movement of the ciliary inuscle 60 to the relaxed/unaccommodated state increases tension in the zonules 62 and capsular bag 58, which in tlun causes the lens 56 to take on a thimler (as measured along the optical axis) or taller shape, as shown in FIGLTRE 1. h1 contrast, wllen the ciliaiy muscle 60 is in the contracted/acconunodated state, tension in the zonules 62 and capsular bag 58 is decreased and the lens 56 talces on the fatter or shorter shape shown in FIGURE 2. Wllen the ciliary inuscles 60 contract and the capsular bag 58 and zonules 62 slacken, some degree of tension is maintained in the capsular bag 58 and zonules 62.
[0021] FIGURE 3 schematically illustrates an einbodiinent of an intraocular lens implant 100, shown in cross section. In certain embodiments, the iinplant comprises a lens body 110 sized and shaped for placement in an anterior portion of the eye 50, such as in the capsular bag 58. In some einbodiments, the lens body coinprises a diffractive optical surface 115. The diffractive optical surface 115 can have diffractive properties which produce an interference pattern. hi some embodiments, the lens body 110 is sufficiently flexible to change the shape of the diffractive optical surface 115 in response to action of the ciliary inuscle 60 so that the interference patteni is modified. hi furtller embodiments, acconunodation is acliieved by modification of the interference pattenl. In some enzbodinlents, the iinplant 100 comprises one or more haptics 117 configured to couple the lens body 110 with the eye 50.
[0022] L-1 preferred embodiments, the lens body 110 is sufficiently compliant to change shape when the ciliary inuscle 60 changes state for accomnzodation.
In various embodiments, the lens body 110 comprises PMMA, silicone, soft silicone, polyhema, polyainide, polyimide, acrylic (hydrophilic or hydrophobic), or a shape memory material, or any suitable coinbination thereof. Other materials are also possible.
In various embodiments, the lens body 110 comprises PMMA, silicone, soft silicone, polyhema, polyainide, polyimide, acrylic (hydrophilic or hydrophobic), or a shape memory material, or any suitable coinbination thereof. Other materials are also possible.
[0023] hl certain embodiments, the implant 100 is sized and shaped for placement in an anterior portion of the eye 50. Ll some einbodiments, the implant 100 is positioned in the capsular bag 58. In other einbodimelits, the implant 100 is positioned in the vitreous. hi still further embodiments, the iinplant 100 is positioned iu1 other areas of the anterior chainber of the eye 50, such as the sulcus or tlie iris plane.
[0024] With continued reference to FIGURE 3, in various embodiments, a width (or in some einbodimelits, a diaineter) D of the lens body 110 is between about 4 inillimeters and about 8 millimeters, between about 5 millimeters and about 7 millimeters, or between about 5.5 inillimeters and about 6.5 inill'uneters. hi otller einbodimelits, the width D is no more than about 6 millimeters, no more than about 7 millimeters, or no more than about 8 millimeters. Iii still other embodiments, the widtll D is no less than about 4 millimeters, no less than about 5 millimeters, or no less than about 6 millimeters.
hl prefeiTed einbodiments, the width D is about 6 millimeters.
. [0025] h-i certain einbodimelits, the lens body 110 is shaped as a refiactive lens that comprises one or more diffractive optical surfaces 115. For example, in the illustrated einbodiment, the lens body 110 is generally shaped as a convex-concave lens, having a first surface 121 and a second surface 122, shown in phantoni, each of which is substantially spherical. The lens body 110 can be shaped in any suitable configuration, including, without limitation, plano-convex, biconvex, or meniscus. The first and/or second surfaces 121, 122, also can be shaped in any suitable configuration, including, witliout limitation, aspheric configurations such as substantially planar, substantially spherical, substantially parabolic, or substantially hyperbolic. In many enlbodiments, the lens body 110 has refractive power due to the cuivature of the first and second surfaces 121, 122.
[0026] In certain einbodiments, the diffractive optical surface 115 follows a general contour or curvature of a substantially smooth base surface. In the illustrated embodiment, the base surface comprises the second surface 122. hi many embodiments, the diffractive optical surface 115 fitrther coinprises a phase grating 130 that deviates from the contour or curvature of the base surface. As used herein, the tenn "grating" is a broad terin used in its ordinary sense, and includes, without limitation, any feature of an optical eleinent configured to produce an interference pattern. In some embodiments, the grating 130 includes an array, series, or pattern of grating regions 135, such as, for exainple, blaze zones, echelettes, or grooves. In some einbodiments, the grating regions 135 are regularly spaced or periodic. The grating regions 135 can be forined in any suitable manner, such as, for example, by cutting or etching a blaze shape into the base surface (e.g., the second surface 122). In other embodiinents, a layer, fihn, or coating is foilned over the base surface (e.g., the second surface 122) to produce grating regions 135 that are raised with respect to the base surface. In still fiutller einbodiments, the lens body 110 is molded to include the grating regions 135. In some embodiments, the grating regions 135 coinprise a series of concentric, step-like stnictures.
[0027] hi various embodiments, the lens body 110 coinprises a single diffractive optical surface 115. Tii other einbodiments, the lens body 110 coinprises a plurality of diffractive optical surfaces 115. One or more diffractive optical surfaces 115 can follow the general contours of the first and/or second surfaces 121, 122.
[0028] In some embodiments, the iinplant 100 comprises one or more haptics 117 configured to couple the lens body 110 with the eye 50. In prefeiTed einbodinzents, the one or more haptics 117 are configured to couple with the ciliaiy inuscle 60. lii some embodiments, the haptics 117 extend outward from a periphery of the lens body 110, and can extend a sufficient distance fiom the lens body 110 to contact an edge of the capsular bag 58, the zonules 62, and/or the ciliary muscle 60. In certain enlbodiments, the haptics 117 are adhered or otlierwise attached to the ciliary muscle 60 or the zonules 62 such that they move in response to contraction and/or relaxation of the ciliary muscle 60. Iii some einbodiinents, the haptics 117 are configured to abut the iruier surface of the capsular bag 58 along some or all of a perimeter thereof, preferably near the zonules 62.
[0029] With reference to FIGLTRE 4, in certain einbodiinents, light enters the lens body 110 through the first surface 121, as indicated by the aiTow 126.
The light propagates through the lens body 110, as indicated by the aiTow 127, and exits tluougll the diffractive optical surface 115. hl certain embodiments, a periodic array of grating regions 135 scatters the exiting light, resulting in constntctive and destnictive interference of the ligllt. Wliether constructive or destnictive interference occurs at an image plane of the lens body 110 depends on the difference in optical patll length between separate grating regions 135, which is a function of the angles at which the light exits the grating regions 135 and the wavelength of the light.
[0030] In certain einbodiments, the interference pattern created by the diffractive optical surface 115 comprises one or more diffraction orders.
Constntctive interference at a given point can result when portions of light from different gratiulg regions 135 are in phase. Additionally, portions of liglit exiting different grating regions 135 that are phase shifted by a full wavelength, or by any number of full wavelengtlls, will constiuctively interfere. For exainple, in some embodiments, a zero diffraction order corresponds with an area wllere there is zero phase sb.ift between portions of light coining from adjacent grating regions 135, a fn-st diffiaction order corresponds with an area wliere there is a one-wavelength phase shift, a second diffraction order corresponds with an area where there is a two-wavelengtll phase shift, and so on.
[0031] As illustrated in FIGURE 4, in certain embodiments, eacli grating region 135 has a width w aa.ld a height Ia. In some embodiments, the width w of each grating region 135 is substantially the saine. Iii fiirther enlbodiments, the height la of each grating region 135 is substantially the sanle. Accordingly, in some embodiments, the diffiaction grating 130 is periodic, and comprises a plurality of regularly spaced grating regions 135.
[0032] The period of the grating 130,. which in some embodunents is equal to the width w of the grating regions 135, cati affect the focal length or optical power of a given diffiaction order. For exainple, the period of the grating 130 can affect the optical pat11 length between different grating regions 135 and a given point. A
difference in optical path lengtll can result in a difference in phase between portions of light exiting the grating regions 135. As a result, a focal plane at which light constructively interferes (see, e.g., FIGURE 5), and at whicll a diffractive image can be created, can move closer to or fiu-tlier froin the lens body 110 as the period of the grating 130 changes.
Th.us, in certain embodiinents, changing the width w of the grating regions 135 can cliange the distance of the focal plane from the lens body 110.
[0033] h-i certain embodiments, the height h of the grating regions 135 can affect the proportion of light that is directed to a given diffraction order.
In some einbodiments, light is chaiuleled solely to the diffraction orders, and the percentage of total light exiting the lens body 110 that is chamieled to a given order is referred to herein as the diffraction efficiency of this order. In the einbodiment illustrated in FIGLTRE 4, the arrows 141, 142, and 143 illustrate a geometrical model of three diffiaction orders into which light of a given wavelength can be chamleled: arrow 141 represents the -diffraction order; arrow 142 represents the 0 diffraction order; and arrow 143 represents the +1 diffraction order. Arrow 144 illustrates the blaze ray, which is the direction at which light is refracted out of the lens body 110 at the grating region 135.
Ii1 certain einbodiments, it is possible to achieve a diffraction efficiency of approximately 100% for a given diffraction order when the blaze ray 144 and the arrow representing the diffraction order coincide. Accordingly, it is possible to vary the percentage of light directed to a given diffraction order by altering the height h of the grating region 135.
[0034] FIGURE 5 scheinatically illustrates a perspective view of an einbodiment of the intraocular lens iniplant 100. A center of the lens body 110 is shown at the origin of an xyz coordinate system for illustrative purposes. h-i certain einbodiments, an optical axis of the lens body 110 extends through the center of the lens body 110. In the illustrated enlbodinient, the optical axis coincides with the z axis. h-i some embodiments, the lens body 110 has a thiclaiess t, as measured in a direction parallel to the z axis.
[0035] fiz certain einbodinients, the diffractive optical surface 115 comprises a series of concentric grating regions 135. hZ the illustrated embodiinent, the grating regions 135 are circular, as is the periphery of the lens body 110. In various otlier enzbodiments, the grating regions 135 and/or lens body 110 can define other shapes, such as ovals, ellipses, or polygons, for exanlple. The grating regions 135 also can be aiTanged in pattei7ls other than concentric. h-i the illustrated embodinient, each circular grating region 135 has a radius of a different length, as indicated by the aiTows s~r, P2, and r~y. Iii certain einbodiinents, the diffractive optical surface 115 chaimels ligllt into one or more diffractive orders. A single diffractive order is represented in FIGURE 5 by an image plane 150.
[0036] In certain embodiinents, the spacing of the grating regions 135 is defined according to the following equation:
r+f2=(f+jM/L)Z (1) where 7n is the given diffractive order, f is the focal length of the given diffractive order, A
is the wavelength of liglit, and Nj is the radius of a given grating region 135, where j is aal positive integer.
[00371 hl simple paraxial foim, equation (1) can be reduced as follows: ri 2 =
jrn),f. Accordingly, the focal length of the n2t" diffraction order can be approxiinated by the equation:
.f ~~
(2) j [0038] Additionally, a paraxial approximation of the heigllt la of the grating regions 135 that will produce a diffraction efficiency of approxiinately 100%
for the atl' diffraction order in certain embodiments is as follows:
m A (3) h_ (n-ni) where n is the refractive index of the material of the lens body 110 and n' is the refractive index of the material surrounding the lens body 110. hi certain embodiments, the implant 100 is within the capsular bag 58 and the lens body 110 is surrounded by an aqueous material having an index of refraction of about 1.336.
[0039] In certain embodiments, the paraineters rj and h.,,, can be selected to produce a lens body 110 of a given focal length f,,,. For exainple, the focal length f,,, can be determined by the IOL power calculation. Advantageously, in suc11 enibodiments, the focal length f,,, is independent of the thiclaiess t of the lens body 110.
Accordingly, in some embodiments, the lens body 110 can be relatively thin, wliich can permit the diffiactive optical surface 115 to readily change shape in response to movement of the ciliaiy n iuscle 60.
[0040] FIGURE 6 schematically illustrates the implant 100 in a changed configuration in response to movement of the ciliary inuscle 60. In certaiui embodiments, movement of the ciliary inuscle 60 causes the diffractive optical surface 115 to change shape. In many einbodimeiits, the diffractive optical surface 115 is elastically defonned from one shape to another. In some embodiments, a cuivature of the diffractive optical surface 115 changes as the ciliary muscle 60 moves. For example, in some embodiments, the optical surface 115 bends, bows, or arcs in response to the muscle movement, and in other enibodiments, the optical surface 115 stretches, flattens, or compresses, in response to movement of the ciliary muscle 60.
[0041] In certain embodiments, the lens body 110 is in an unaccoinmodated state when the shape of the diffractive optical surface 115 is unchanged and is in an accommodated state when the shape of the diffractive optical surface is changed. In some embodiments, when the ciliary muscle 60 is in a relaxed condition, the lens body 110 and diffractive optical surface 115 generally assume their nati.iral shape. Wlien the ciliary muscle 60 contracts for acconnnodation, it applies force to the haptics 117 and changes the shape of the lens body 110 and the diffractive optical surface 115. hi some enlbodiments, the base surface (e.g., the second surface 122) of the diffractive optical surface 115 is more higlily ctuved when the lens body 110 is in the accon7modated state than is the base surface when the lens body 110 is in the tuiacconnnodated state.
[0042] In other embod'unents, the lens body 110 is in a natural or relatively unstressed state when the ciliary inuscle 60 is contracted for accoimnodation.
In certaiui of such embodiments, as the ciliaiy muscle 60 relaxes, it pulls on the haptics 117 to change the shape of the lens body 110 and the diffractive optical surface 115.
Iii some embodiinents, the base surface of the diffractive optical surface 115 becomes less rounded as the ciliary inuscle 60 relaxes.
[0043] In some embodiments, the change in curvature of the base surface of the diffractive optical surface 115 is substantially unifonn along multiple cross sections of the lens body 110. For example, in some embodiments, when the shape of the diffractive optical surface 115 is unchanged, a cross section of the lens body 110 along the xz plane, as defined in FIGURE 6, reveals a cuivature of the base surface that is substantially the same as the cuivature of the base surface along the yz plane. As the shape of the diffractive optical surface 115 changes, the changing ctuvature of the base stirface along the xz plane and that of the base surface along the yz plane reinain substantially the sanie as each other. Iii fiu-ther einbodinients, the curvature of the base surface along multiple planes that (i) are peipendicular to the xy plane and (ii) extend tlv-ough the optical axis (i.e., the z axis) are substantially the saine throughout a change in shape of the diffractive optical surface 115.
[0044] Iii certain embodiments, the maiuler in which the optical surface 115 changes shape is affected by the material and/or the configLuation of the lens body 110.
In certain einbodiments, the flexibility at a central region of the lens body 110 is different than the flexibility at an outer region of the lens body 110. For exainple, in some en7bodiments, either the stiffiless or the conlpliance of the material of the lens body 110 increases toward the center of the lens body 110. hi ftutlzer einbodiments, the lens body 110 coinprises a first material at an outer region and a second material at a central region, and the first material can be more or less compliant than the second material.
In still fiirtlier einbodiments, the lens body 110 coinprises a plurality of materials having different flexibilities.
[0045] In some einbodiments, the thiclu-iess t varies between a center of the lens body 110 and the periphery thereo~ The tllickness t can increase or decrease toward the center of the lens body 110. In otlier embodiments, the tliicluiess t is substantially constant. hi many embodiments, regions of the lens body 110 that are relatively more compliant and/or are tliiimer can be reshaped to a larger degree than relatively stiffer and/or thicker portions of the lens body 110.
[0046] In some einbodiunents, the mainler in which the lens body 110 is coupled witll the ciliaiy muscle 60 affects the mamier in which the lens body 110 changes shape. In some einbodiments, a plurality of haptics 117 extend from the periphery of the lens body 110. The haptics 117 can be pulled in different directions along a coininon plane such that the curvature of the lens body 110 changes in a substantially uniform maiuzer. Iii some instances, a greater uniforinity in a change of curvature can result from a relatively larger number of haptics 117. In other embodiments, the periphery of the lens body 110 is coupled witll the ciliary muscle 60 via aii asseinbly or mecllanism comprising a spring coil meinber and haptics. Embodiments of such a device are disclosed in U.S.
Patent Application No. 10/016,705, filed Decelnber 10, 2001, titled ACCOMMODATING INTR.AOCULAR LENS, the entire coiitents of which are hereby incorporated by reference herein and made a part of this specification. In certain enzbodiinents, such a device can constrict the lens body 110 about its peripheral edge to effect a relatively unifonn cliange in the shape of the lens body 110 as the ciliary inuscle 60 relaxes and contracts. Otlier systems and nlethods are also possible for coupling the lens body 110 with the ciliary muscle 60.
[0047] As illustrated in FIGURE 6, in certain embodiments, the distance between different grating regions 135 and the optical axis of the lens body 110 changes as the diffiactive optical surface 115 changes shape. In the illustrated embodiment, the radii of the circular grating regions 135 are reduced as coinpared with those in FIGURE 5.
This is indicated by the grating regions 135 shown in phantonl and by the aiTows Y=I', rZ', and rj', which are relatively shorter than the arrows t r, r2, and rj. Iii some enibodiments, the lens body 110 is coinpressed or stretched such that the radii of the grating regions 135 are reduced or expanded, respectively, while the curvature of the diffiactive optical surface 115 does not change significantly. In other embodiments, the cuivature of the diffractive optical surface 115 becomes more or less bowed suc11 that the grating regions 135 move closer to or further from the optical axis of the lens body 110. In some embodiments, the grating regions 135 become more or less closely spaced to each other, as ineasured in a direction perpendicular to the optical axis.
[0048] In certain embodiments, the radii of the grating regions 135 are reduced proportionally to the ainount that the curvature of the base surface of the diffiactive optical surface 115 changes, whicll can shift the image plane 150 toward the diffiactive optical surface 115. Ii1 some einbodiv.nents, the diaineter of the lens body 110 is between about 4 milliuneters and about 8 millimeters. In certain of such einbodiunents, contraction of the ciliaiy muscle 60 urges the periphery of the lens body 110 towards the center of the lens body 110 by about 0.25 millimeters, wllicli produces a relatively small change in the curvature of the base surface of the diffiactive optical surface 115. In some einbodiments, this change in curvature can vary the orientation of the grating regions 135.
For exainple, each grating region 135 can be generally planar in an unchanged state, and can be angled to a slightly frustoconical shape in a changed state. However, in the small range of change effected by moveinent of the ciliaiy inuscle 60, the sniall angle approximation of a sin(a) can apply. Accordingly, the changed diffractive optical surface 115 can still produce distinct diffiactive orders, and the grating regions 135 can still follow equations (1), (2), and (3). As a result, according to equation (2), the focal length fõI of a given diffraction order will be smaller for the changed diffractive optical surface 115, since the radii r1', 1. 2 ', and rj' are smaller tllan the radii ri, 1=2, and r; (sllown in pha.ntom).
[0049] Accordingly, in certain advantageous embodiinents, changing the shape of the diffractive optical surface 115 produces a gain in optical power, thus allowing the iinplant 100 to be used for accoinniodation. As illustrated in FIGURE 6, the image plane 150' of a given diffractive order is closer to the diffiactive optical surface 115 than the iinage plane 150 (shown in phantoin). The focus of the iinplant 100 can thus be sllifted from distant vision to near vision, or vice versa, by changing the shape of the diffractive optical surface 115. Advantageously, in preferred enlbodiments, the iinplant 100 further allows a range of intennediate vision between distant and near vision, and in further enibodiments, the range of intermediate vision is continuous.
[0050] hi certain einbodiinents, the heiglit h and width w of the grating regions 135 are such that approximately 100% of the optical output of the diffractive optical surface 115 is chaiuleled to a single diffraction order, which can be designated as the "design" diffraction order. Accordingly, the diffraction efficiency of the design diffraction order is approximately 100%. As described above, the distance of the image position of the design diffraction order from the diffractive optical surface 115, i.e., the focal length of the diffiactive optical surface 115, can be altered by clianging the shape of the diffractive optical surface 115. However, in certain einbodiments, changing the shape of the diffiactive optical surface 115 can cause minor deformations of the height h and width w and, as noted above, can also change the relative orientation of the grating regions 135. In some embodiments, these changes can clzaiuzel soine of the optical output to other diffraction orders, thereby reducing the diffiaction efficiency of the design diffraction order.
[0051] In many instances, a small reduction in contrast is acceptable for near vision. Accordingly, in preferred embodiments, distant vision is produced by the diffractive optical surface 115 when its shape is tinchanged, and near vision is produced when its shape is changed. hi some embodiments, the diffractive optical surface 115 chanii.els about 100% of the ligllt enteruzg the lens body 110 to the design diffraction order wlien the shape of the diffractive optical surface 115 is unchanged.
[0052] hi preferred embodinlents, a relatively large percentage of the optical output of the diffractive optical surface 115 is directed to the design diffraction order for distant, intennediate, and near vision. In various embodiments, at least about 50%, at least about 60%, at least about 70%, at least about 75%, at least about 80%, at least about 85%, at least about 90%, or at least about 95% of the optical output of the diffiactive optical surface 115 is directed to the design diffiaction order.
[0053] FIGURES 7 and 8 schematically illustrate an embodiment of an intraocular lens implant 200 in an unaccoinmodated state and in an accoininodated state, respectively. The iinplant 200 is similar to the iinplant 100 in many respects.
Accordingly, like features of the iinplants 100, 200 are identified with like numerals. In certain embodinzents, the iinplant 200 coinprises a lens body 110, a diffractive optical surface 115, and a plurality of haptics 117. The optical surface 115 can coinprise a grating 130 having a plurality of grating regions 135.
[0054] Iii certain embodiments, a method coniprises providing the iinplant 200. The method further coinprises implanting the implant 200 in the eye 50.
In certain embodiments, the iinplant 200 is coupled with the ciliary muscle 60. Tii some embodiments, the curvature of the diffractive optical surface 115 changes in response to moveinent of the ciliary muscle 60.
[0055] FIGURES 9 and 10 schematically illustrate an embodiment of an intraocular lens implant 300 in an unacconunodated state and in an accommodated state, respectively. In certain einbodiinents, the implant 300 comprises a first iinplant 313, such as the implants 100 and 200 described above, and a second implant 316. F.i some embodiments, the first iinplant 313 comprises 'a diffractive optical surface 115 configured to change shape. In further embodiments, the first implant 313 comprises one or more haptics 117 for coupling with the ciliary niuscle 60. hl some einbodiments the second implant 316 is configured to change shape in response to action of the ciliary muscle 60, while in other enzbodiments, the second iinplant 316 is not configured to change shape.
In various enlbodinients, the second implant 316 is anterior to or posterior to the first implant 313.
[0056] Ii1 some enzbodiments, the second implant 316 conlprises one or more refractive optical surfaces. hl some einbodiments, the second iinplant 316 comprises a refractive lens. In some advantageous embodiments, the first and second iinplants 313, 316 are configured to move relative to one another wlien the eye accominodates. In certain of such enibodiinents, the first inlplant 313 does not significantly change shape when the eye 50 accolninodates. Accordingly, in some enlbodiments, the diffraction efficiency of the design diffiaction order of the first iinplant 313 can be near 100% for distant, inteinlediate, and near vision.
[0057] In some embodiments, the second iinplant 316 is a diffractive optic. In fiuther advantageous embodiinents, the second implant 316 is a multiphase diffractive optic, which can reduce the iinpact of cluomatic abeiTation from tlle first iinplant 313. In fiu-ther embodiments, two or more optics are coinbined with the first implant 313 in a multi-lens and/or inulti-optic systein.
[0058] Althougll the inventions presented herein have been disclosed in the context of certain preferred einbodiments and exainples, it will be understood by those skilled in the art that the inventions extend beyond the specifically disclosed embodinlents to other alteniative embodiments and/or uses of the inventions and obvious modifications and equivalents thereo~ Thus, it is intended that the scope of the inventions herein disclosed should not be limited by the particular einbodimerits described above, but should be detennined only by a fair reading of the claims that follow.
hl prefeiTed einbodiments, the width D is about 6 millimeters.
. [0025] h-i certain einbodimelits, the lens body 110 is shaped as a refiactive lens that comprises one or more diffractive optical surfaces 115. For example, in the illustrated einbodiment, the lens body 110 is generally shaped as a convex-concave lens, having a first surface 121 and a second surface 122, shown in phantoni, each of which is substantially spherical. The lens body 110 can be shaped in any suitable configuration, including, without limitation, plano-convex, biconvex, or meniscus. The first and/or second surfaces 121, 122, also can be shaped in any suitable configuration, including, witliout limitation, aspheric configurations such as substantially planar, substantially spherical, substantially parabolic, or substantially hyperbolic. In many enlbodiments, the lens body 110 has refractive power due to the cuivature of the first and second surfaces 121, 122.
[0026] In certain einbodiments, the diffractive optical surface 115 follows a general contour or curvature of a substantially smooth base surface. In the illustrated embodiment, the base surface comprises the second surface 122. hi many embodiments, the diffractive optical surface 115 fitrther coinprises a phase grating 130 that deviates from the contour or curvature of the base surface. As used herein, the tenn "grating" is a broad terin used in its ordinary sense, and includes, without limitation, any feature of an optical eleinent configured to produce an interference pattern. In some embodiments, the grating 130 includes an array, series, or pattern of grating regions 135, such as, for exainple, blaze zones, echelettes, or grooves. In some einbodiments, the grating regions 135 are regularly spaced or periodic. The grating regions 135 can be forined in any suitable manner, such as, for example, by cutting or etching a blaze shape into the base surface (e.g., the second surface 122). In other embodiinents, a layer, fihn, or coating is foilned over the base surface (e.g., the second surface 122) to produce grating regions 135 that are raised with respect to the base surface. In still fiutller einbodiments, the lens body 110 is molded to include the grating regions 135. In some embodiments, the grating regions 135 coinprise a series of concentric, step-like stnictures.
[0027] hi various embodiments, the lens body 110 coinprises a single diffractive optical surface 115. Tii other einbodiments, the lens body 110 coinprises a plurality of diffractive optical surfaces 115. One or more diffractive optical surfaces 115 can follow the general contours of the first and/or second surfaces 121, 122.
[0028] In some embodiments, the iinplant 100 comprises one or more haptics 117 configured to couple the lens body 110 with the eye 50. In prefeiTed einbodinzents, the one or more haptics 117 are configured to couple with the ciliaiy inuscle 60. lii some embodiments, the haptics 117 extend outward from a periphery of the lens body 110, and can extend a sufficient distance fiom the lens body 110 to contact an edge of the capsular bag 58, the zonules 62, and/or the ciliary muscle 60. In certain enlbodiments, the haptics 117 are adhered or otlierwise attached to the ciliary muscle 60 or the zonules 62 such that they move in response to contraction and/or relaxation of the ciliary muscle 60. Iii some einbodiinents, the haptics 117 are configured to abut the iruier surface of the capsular bag 58 along some or all of a perimeter thereof, preferably near the zonules 62.
[0029] With reference to FIGLTRE 4, in certain einbodiinents, light enters the lens body 110 through the first surface 121, as indicated by the aiTow 126.
The light propagates through the lens body 110, as indicated by the aiTow 127, and exits tluougll the diffractive optical surface 115. hl certain embodiments, a periodic array of grating regions 135 scatters the exiting light, resulting in constntctive and destnictive interference of the ligllt. Wliether constructive or destnictive interference occurs at an image plane of the lens body 110 depends on the difference in optical patll length between separate grating regions 135, which is a function of the angles at which the light exits the grating regions 135 and the wavelength of the light.
[0030] In certain einbodiments, the interference pattern created by the diffractive optical surface 115 comprises one or more diffraction orders.
Constntctive interference at a given point can result when portions of light from different gratiulg regions 135 are in phase. Additionally, portions of liglit exiting different grating regions 135 that are phase shifted by a full wavelength, or by any number of full wavelengtlls, will constiuctively interfere. For exainple, in some embodiments, a zero diffraction order corresponds with an area wllere there is zero phase sb.ift between portions of light coining from adjacent grating regions 135, a fn-st diffiaction order corresponds with an area wliere there is a one-wavelength phase shift, a second diffraction order corresponds with an area where there is a two-wavelengtll phase shift, and so on.
[0031] As illustrated in FIGURE 4, in certain embodiments, eacli grating region 135 has a width w aa.ld a height Ia. In some embodiments, the width w of each grating region 135 is substantially the saine. Iii fiirther enlbodiments, the height la of each grating region 135 is substantially the sanle. Accordingly, in some embodiments, the diffiaction grating 130 is periodic, and comprises a plurality of regularly spaced grating regions 135.
[0032] The period of the grating 130,. which in some embodunents is equal to the width w of the grating regions 135, cati affect the focal length or optical power of a given diffiaction order. For exainple, the period of the grating 130 can affect the optical pat11 length between different grating regions 135 and a given point. A
difference in optical path lengtll can result in a difference in phase between portions of light exiting the grating regions 135. As a result, a focal plane at which light constructively interferes (see, e.g., FIGURE 5), and at whicll a diffractive image can be created, can move closer to or fiu-tlier froin the lens body 110 as the period of the grating 130 changes.
Th.us, in certain embodiinents, changing the width w of the grating regions 135 can cliange the distance of the focal plane from the lens body 110.
[0033] h-i certain embodiments, the height h of the grating regions 135 can affect the proportion of light that is directed to a given diffraction order.
In some einbodiments, light is chaiuleled solely to the diffraction orders, and the percentage of total light exiting the lens body 110 that is chamieled to a given order is referred to herein as the diffraction efficiency of this order. In the einbodiment illustrated in FIGLTRE 4, the arrows 141, 142, and 143 illustrate a geometrical model of three diffiaction orders into which light of a given wavelength can be chamleled: arrow 141 represents the -diffraction order; arrow 142 represents the 0 diffraction order; and arrow 143 represents the +1 diffraction order. Arrow 144 illustrates the blaze ray, which is the direction at which light is refracted out of the lens body 110 at the grating region 135.
Ii1 certain einbodiments, it is possible to achieve a diffraction efficiency of approximately 100% for a given diffraction order when the blaze ray 144 and the arrow representing the diffraction order coincide. Accordingly, it is possible to vary the percentage of light directed to a given diffraction order by altering the height h of the grating region 135.
[0034] FIGURE 5 scheinatically illustrates a perspective view of an einbodiment of the intraocular lens iniplant 100. A center of the lens body 110 is shown at the origin of an xyz coordinate system for illustrative purposes. h-i certain einbodiments, an optical axis of the lens body 110 extends through the center of the lens body 110. In the illustrated enlbodinient, the optical axis coincides with the z axis. h-i some embodiments, the lens body 110 has a thiclaiess t, as measured in a direction parallel to the z axis.
[0035] fiz certain einbodinients, the diffractive optical surface 115 comprises a series of concentric grating regions 135. hZ the illustrated embodiinent, the grating regions 135 are circular, as is the periphery of the lens body 110. In various otlier enzbodiments, the grating regions 135 and/or lens body 110 can define other shapes, such as ovals, ellipses, or polygons, for exanlple. The grating regions 135 also can be aiTanged in pattei7ls other than concentric. h-i the illustrated embodinient, each circular grating region 135 has a radius of a different length, as indicated by the aiTows s~r, P2, and r~y. Iii certain einbodiinents, the diffractive optical surface 115 chaimels ligllt into one or more diffractive orders. A single diffractive order is represented in FIGURE 5 by an image plane 150.
[0036] In certain embodiinents, the spacing of the grating regions 135 is defined according to the following equation:
r+f2=(f+jM/L)Z (1) where 7n is the given diffractive order, f is the focal length of the given diffractive order, A
is the wavelength of liglit, and Nj is the radius of a given grating region 135, where j is aal positive integer.
[00371 hl simple paraxial foim, equation (1) can be reduced as follows: ri 2 =
jrn),f. Accordingly, the focal length of the n2t" diffraction order can be approxiinated by the equation:
.f ~~
(2) j [0038] Additionally, a paraxial approximation of the heigllt la of the grating regions 135 that will produce a diffraction efficiency of approxiinately 100%
for the atl' diffraction order in certain embodiments is as follows:
m A (3) h_ (n-ni) where n is the refractive index of the material of the lens body 110 and n' is the refractive index of the material surrounding the lens body 110. hi certain embodiments, the implant 100 is within the capsular bag 58 and the lens body 110 is surrounded by an aqueous material having an index of refraction of about 1.336.
[0039] In certain embodiments, the paraineters rj and h.,,, can be selected to produce a lens body 110 of a given focal length f,,,. For exainple, the focal length f,,, can be determined by the IOL power calculation. Advantageously, in suc11 enibodiments, the focal length f,,, is independent of the thiclaiess t of the lens body 110.
Accordingly, in some embodiments, the lens body 110 can be relatively thin, wliich can permit the diffiactive optical surface 115 to readily change shape in response to movement of the ciliaiy n iuscle 60.
[0040] FIGURE 6 schematically illustrates the implant 100 in a changed configuration in response to movement of the ciliary inuscle 60. In certaiui embodiments, movement of the ciliary inuscle 60 causes the diffractive optical surface 115 to change shape. In many einbodimeiits, the diffractive optical surface 115 is elastically defonned from one shape to another. In some embodiments, a cuivature of the diffractive optical surface 115 changes as the ciliary muscle 60 moves. For example, in some embodiments, the optical surface 115 bends, bows, or arcs in response to the muscle movement, and in other enibodiments, the optical surface 115 stretches, flattens, or compresses, in response to movement of the ciliary muscle 60.
[0041] In certain embodiments, the lens body 110 is in an unaccoinmodated state when the shape of the diffractive optical surface 115 is unchanged and is in an accommodated state when the shape of the diffractive optical surface is changed. In some embodiments, when the ciliary muscle 60 is in a relaxed condition, the lens body 110 and diffractive optical surface 115 generally assume their nati.iral shape. Wlien the ciliary muscle 60 contracts for acconnnodation, it applies force to the haptics 117 and changes the shape of the lens body 110 and the diffractive optical surface 115. hi some enlbodiments, the base surface (e.g., the second surface 122) of the diffractive optical surface 115 is more higlily ctuved when the lens body 110 is in the accon7modated state than is the base surface when the lens body 110 is in the tuiacconnnodated state.
[0042] In other embod'unents, the lens body 110 is in a natural or relatively unstressed state when the ciliary inuscle 60 is contracted for accoimnodation.
In certaiui of such embodiments, as the ciliaiy muscle 60 relaxes, it pulls on the haptics 117 to change the shape of the lens body 110 and the diffractive optical surface 115.
Iii some embodiinents, the base surface of the diffractive optical surface 115 becomes less rounded as the ciliary inuscle 60 relaxes.
[0043] In some embodiments, the change in curvature of the base surface of the diffractive optical surface 115 is substantially unifonn along multiple cross sections of the lens body 110. For example, in some embodiments, when the shape of the diffractive optical surface 115 is unchanged, a cross section of the lens body 110 along the xz plane, as defined in FIGURE 6, reveals a cuivature of the base surface that is substantially the same as the cuivature of the base surface along the yz plane. As the shape of the diffractive optical surface 115 changes, the changing ctuvature of the base stirface along the xz plane and that of the base surface along the yz plane reinain substantially the sanie as each other. Iii fiu-ther einbodinients, the curvature of the base surface along multiple planes that (i) are peipendicular to the xy plane and (ii) extend tlv-ough the optical axis (i.e., the z axis) are substantially the saine throughout a change in shape of the diffractive optical surface 115.
[0044] Iii certain embodiments, the maiuler in which the optical surface 115 changes shape is affected by the material and/or the configLuation of the lens body 110.
In certain einbodiments, the flexibility at a central region of the lens body 110 is different than the flexibility at an outer region of the lens body 110. For exainple, in some en7bodiments, either the stiffiless or the conlpliance of the material of the lens body 110 increases toward the center of the lens body 110. hi ftutlzer einbodiments, the lens body 110 coinprises a first material at an outer region and a second material at a central region, and the first material can be more or less compliant than the second material.
In still fiirtlier einbodiments, the lens body 110 coinprises a plurality of materials having different flexibilities.
[0045] In some einbodiments, the thiclu-iess t varies between a center of the lens body 110 and the periphery thereo~ The tllickness t can increase or decrease toward the center of the lens body 110. In otlier embodiments, the tliicluiess t is substantially constant. hi many embodiments, regions of the lens body 110 that are relatively more compliant and/or are tliiimer can be reshaped to a larger degree than relatively stiffer and/or thicker portions of the lens body 110.
[0046] In some einbodiunents, the mainler in which the lens body 110 is coupled witll the ciliaiy muscle 60 affects the mamier in which the lens body 110 changes shape. In some einbodiments, a plurality of haptics 117 extend from the periphery of the lens body 110. The haptics 117 can be pulled in different directions along a coininon plane such that the curvature of the lens body 110 changes in a substantially uniform maiuzer. Iii some instances, a greater uniforinity in a change of curvature can result from a relatively larger number of haptics 117. In other embodiments, the periphery of the lens body 110 is coupled witll the ciliary muscle 60 via aii asseinbly or mecllanism comprising a spring coil meinber and haptics. Embodiments of such a device are disclosed in U.S.
Patent Application No. 10/016,705, filed Decelnber 10, 2001, titled ACCOMMODATING INTR.AOCULAR LENS, the entire coiitents of which are hereby incorporated by reference herein and made a part of this specification. In certain enzbodiinents, such a device can constrict the lens body 110 about its peripheral edge to effect a relatively unifonn cliange in the shape of the lens body 110 as the ciliary inuscle 60 relaxes and contracts. Otlier systems and nlethods are also possible for coupling the lens body 110 with the ciliary muscle 60.
[0047] As illustrated in FIGURE 6, in certain embodiments, the distance between different grating regions 135 and the optical axis of the lens body 110 changes as the diffiactive optical surface 115 changes shape. In the illustrated embodiment, the radii of the circular grating regions 135 are reduced as coinpared with those in FIGURE 5.
This is indicated by the grating regions 135 shown in phantonl and by the aiTows Y=I', rZ', and rj', which are relatively shorter than the arrows t r, r2, and rj. Iii some enibodiments, the lens body 110 is coinpressed or stretched such that the radii of the grating regions 135 are reduced or expanded, respectively, while the curvature of the diffiactive optical surface 115 does not change significantly. In other embodiments, the cuivature of the diffractive optical surface 115 becomes more or less bowed suc11 that the grating regions 135 move closer to or further from the optical axis of the lens body 110. In some embodiments, the grating regions 135 become more or less closely spaced to each other, as ineasured in a direction perpendicular to the optical axis.
[0048] In certain embodiments, the radii of the grating regions 135 are reduced proportionally to the ainount that the curvature of the base surface of the diffiactive optical surface 115 changes, whicll can shift the image plane 150 toward the diffiactive optical surface 115. Ii1 some einbodiv.nents, the diaineter of the lens body 110 is between about 4 milliuneters and about 8 millimeters. In certain of such einbodiunents, contraction of the ciliaiy muscle 60 urges the periphery of the lens body 110 towards the center of the lens body 110 by about 0.25 millimeters, wllicli produces a relatively small change in the curvature of the base surface of the diffiactive optical surface 115. In some einbodiments, this change in curvature can vary the orientation of the grating regions 135.
For exainple, each grating region 135 can be generally planar in an unchanged state, and can be angled to a slightly frustoconical shape in a changed state. However, in the small range of change effected by moveinent of the ciliaiy inuscle 60, the sniall angle approximation of a sin(a) can apply. Accordingly, the changed diffractive optical surface 115 can still produce distinct diffiactive orders, and the grating regions 135 can still follow equations (1), (2), and (3). As a result, according to equation (2), the focal length fõI of a given diffraction order will be smaller for the changed diffractive optical surface 115, since the radii r1', 1. 2 ', and rj' are smaller tllan the radii ri, 1=2, and r; (sllown in pha.ntom).
[0049] Accordingly, in certain advantageous embodiinents, changing the shape of the diffractive optical surface 115 produces a gain in optical power, thus allowing the iinplant 100 to be used for accoinniodation. As illustrated in FIGURE 6, the image plane 150' of a given diffractive order is closer to the diffiactive optical surface 115 than the iinage plane 150 (shown in phantoin). The focus of the iinplant 100 can thus be sllifted from distant vision to near vision, or vice versa, by changing the shape of the diffractive optical surface 115. Advantageously, in preferred enlbodiments, the iinplant 100 further allows a range of intennediate vision between distant and near vision, and in further enibodiments, the range of intermediate vision is continuous.
[0050] hi certain einbodiinents, the heiglit h and width w of the grating regions 135 are such that approximately 100% of the optical output of the diffractive optical surface 115 is chaiuleled to a single diffraction order, which can be designated as the "design" diffraction order. Accordingly, the diffraction efficiency of the design diffraction order is approximately 100%. As described above, the distance of the image position of the design diffraction order from the diffractive optical surface 115, i.e., the focal length of the diffiactive optical surface 115, can be altered by clianging the shape of the diffractive optical surface 115. However, in certain einbodiments, changing the shape of the diffiactive optical surface 115 can cause minor deformations of the height h and width w and, as noted above, can also change the relative orientation of the grating regions 135. In some embodiments, these changes can clzaiuzel soine of the optical output to other diffraction orders, thereby reducing the diffiaction efficiency of the design diffraction order.
[0051] In many instances, a small reduction in contrast is acceptable for near vision. Accordingly, in preferred embodiments, distant vision is produced by the diffractive optical surface 115 when its shape is tinchanged, and near vision is produced when its shape is changed. hi some embodiments, the diffractive optical surface 115 chanii.els about 100% of the ligllt enteruzg the lens body 110 to the design diffraction order wlien the shape of the diffractive optical surface 115 is unchanged.
[0052] hi preferred embodinlents, a relatively large percentage of the optical output of the diffractive optical surface 115 is directed to the design diffraction order for distant, intennediate, and near vision. In various embodiments, at least about 50%, at least about 60%, at least about 70%, at least about 75%, at least about 80%, at least about 85%, at least about 90%, or at least about 95% of the optical output of the diffiactive optical surface 115 is directed to the design diffiaction order.
[0053] FIGURES 7 and 8 schematically illustrate an embodiment of an intraocular lens implant 200 in an unaccoinmodated state and in an accoininodated state, respectively. The iinplant 200 is similar to the iinplant 100 in many respects.
Accordingly, like features of the iinplants 100, 200 are identified with like numerals. In certain embodinzents, the iinplant 200 coinprises a lens body 110, a diffractive optical surface 115, and a plurality of haptics 117. The optical surface 115 can coinprise a grating 130 having a plurality of grating regions 135.
[0054] Iii certain embodiments, a method coniprises providing the iinplant 200. The method further coinprises implanting the implant 200 in the eye 50.
In certain embodiments, the iinplant 200 is coupled with the ciliary muscle 60. Tii some embodiments, the curvature of the diffractive optical surface 115 changes in response to moveinent of the ciliary muscle 60.
[0055] FIGURES 9 and 10 schematically illustrate an embodiment of an intraocular lens implant 300 in an unacconunodated state and in an accommodated state, respectively. In certain einbodiinents, the implant 300 comprises a first iinplant 313, such as the implants 100 and 200 described above, and a second implant 316. F.i some embodiments, the first iinplant 313 comprises 'a diffractive optical surface 115 configured to change shape. In further embodiments, the first implant 313 comprises one or more haptics 117 for coupling with the ciliary niuscle 60. hl some einbodiments the second implant 316 is configured to change shape in response to action of the ciliary muscle 60, while in other enzbodiments, the second iinplant 316 is not configured to change shape.
In various enlbodinients, the second implant 316 is anterior to or posterior to the first implant 313.
[0056] Ii1 some enzbodiments, the second implant 316 conlprises one or more refractive optical surfaces. hl some einbodiments, the second iinplant 316 comprises a refractive lens. In some advantageous embodiments, the first and second iinplants 313, 316 are configured to move relative to one another wlien the eye accominodates. In certain of such enibodiinents, the first inlplant 313 does not significantly change shape when the eye 50 accolninodates. Accordingly, in some enlbodiments, the diffraction efficiency of the design diffiaction order of the first iinplant 313 can be near 100% for distant, inteinlediate, and near vision.
[0057] In some embodiments, the second iinplant 316 is a diffractive optic. In fiuther advantageous embodiinents, the second implant 316 is a multiphase diffractive optic, which can reduce the iinpact of cluomatic abeiTation from tlle first iinplant 313. In fiu-ther embodiments, two or more optics are coinbined with the first implant 313 in a multi-lens and/or inulti-optic systein.
[0058] Althougll the inventions presented herein have been disclosed in the context of certain preferred einbodiments and exainples, it will be understood by those skilled in the art that the inventions extend beyond the specifically disclosed embodinlents to other alteniative embodiments and/or uses of the inventions and obvious modifications and equivalents thereo~ Thus, it is intended that the scope of the inventions herein disclosed should not be limited by the particular einbodimerits described above, but should be detennined only by a fair reading of the claims that follow.
Claims (21)
1. An intraocular implant comprising:
a lens body comprising a diffractive optical surface having diffractive properties which produce an interference pattern, said lens body being sized and shaped for placement in an anterior portion of a human eye, said lens body being sufficiently flexible to change the shape of said diffractive optical surface in response to ciliary muscle action so that said interference pattern is modified.
a lens body comprising a diffractive optical surface having diffractive properties which produce an interference pattern, said lens body being sized and shaped for placement in an anterior portion of a human eye, said lens body being sufficiently flexible to change the shape of said diffractive optical surface in response to ciliary muscle action so that said interference pattern is modified.
2. The intraocular implant of Claim 1, wherein at least about 80 percent of the optical output of said diffractive optical surface is in a single diffraction order.
3. The intraocular implant of Claim 1, wherein said implant is in an unaccomodated state when the shape of said diffractive optical surface is unchanged and is in an accommodated state when the shape of said diffractive optical surface is changed.
4. The intraocular implant of Claim 1, wherein said interference pattern comprises one or more diffraction orders and wherein a distance, along an optical axis of said lens body, between (i) at least one of said one or more diffraction orders and (ii) said lens body changes as the shape of said diffractive optical surface is changed.
5. The intraocular implant of Claim 1, wherein said diffractive optical surface comprises a grating comprising a plurality of grating regions.
6. The intraocular implant of Claim 5, wherein a distance between one or more of the plurality of grating regions and an optical axis of said intraocular implant changes as the shape of said diffractive optical surface is changed.
7. The intraocular implant of Claim 1, further comprising a second lens with a refractive optical surface.
8. The intraocular implant of Claim 1, wherein the curvature of a base surface of said diffractive optical surface is changed when the shape of said diffractive optical surface is changed.
9. The intraocular implant of Claim 8, wherein the curvature is substantially uniform along multiple cross sections of said lens body.
10. The intraocular implant of Claim 1, wherein the flexibility at a central region of said lens body is different than the flexibility at an outer region of said lens body.
11. The intraocular implant of Claim 10, wherein said lens body is thinner at said outer region thereof than at said central region thereof.
12. The intraocular implant of Claim 10, wherein said lens body comprises a first material at said outer region thereof and a second material at said central region thereof, said first material being more compliant than said second material.
13. An intraocular implant comprising:
an optical element sized for insertion into a human eye, said optical element having a diffractive optical surface, said diffractive optical surface having an unaccommodated state in which said diffractive optical surface creates a first interference pattern and an accommodated state in which said diffractive optical surface creates a second interference pattern which differs from the first interference pattern, said optical element being sufficiently flexible to change from said unaccommodated state to said accommodated state in response to ciliary muscle action.
an optical element sized for insertion into a human eye, said optical element having a diffractive optical surface, said diffractive optical surface having an unaccommodated state in which said diffractive optical surface creates a first interference pattern and an accommodated state in which said diffractive optical surface creates a second interference pattern which differs from the first interference pattern, said optical element being sufficiently flexible to change from said unaccommodated state to said accommodated state in response to ciliary muscle action.
14. The intraocular implant of Claim 13, wherein said first interference pattern comprises a first image position of a diffraction order and said second interference pattern comprises a second image position of said diffraction order, said first and second diffractive image positions being spaced from each other.
15. The intraocular implant of Claim 13, wherein a base surface of said diffractive optical surface is more highly curved in said accommodated state than in said unaccommodated state.
16. The intraocular implant of Claim 13, wherein said first and second interference patterns each comprises one or more diffraction orders, said one or more diffraction orders being spaced further from said optical element when said diffractive optical surface is in said unaccommodated state than when said optical element is in said accommodated state.
17. The intraocular implant of Claim 13, wherein said diffractive optical element comprises a plurality of gratings having a uniform grating width.
18. An intraocular implant comprising:
an optical element sized for insertion into a human eye, said optical element having a diffractive optical surface, said diffractive optical surface being alterable between a first shape that provides distant vision and a second shape that provides intermediate vision.
an optical element sized for insertion into a human eye, said optical element having a diffractive optical surface, said diffractive optical surface being alterable between a first shape that provides distant vision and a second shape that provides intermediate vision.
19. The intraocular implant of Claim 18, wherein said diffractive optical surface is alterable to a third shape that provides near vision.
20. The intraocular implant of Claim 18, wherein said diffractive optical surface creates an interference pattern having one or more diffraction orders.
21. The intraocular implant of Claim 20, wherein a single diffraction order provides said distant vision and said intermediate vision.
Applications Claiming Priority (3)
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| US70587605P | 2005-08-05 | 2005-08-05 | |
| US60/705,876 | 2005-08-05 | ||
| PCT/US2006/030606 WO2007019389A1 (en) | 2005-08-05 | 2006-08-07 | Accommodating diffractive intraocular lens |
Publications (2)
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| CA2618021A1 true CA2618021A1 (en) | 2007-02-15 |
| CA2618021C CA2618021C (en) | 2014-08-05 |
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|---|---|---|---|
| CA2618021A Expired - Fee Related CA2618021C (en) | 2005-08-05 | 2006-08-07 | Accommodating diffractive intraocular lens |
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| US (1) | US20070032866A1 (en) |
| EP (1) | EP1924222A1 (en) |
| JP (1) | JP2009503622A (en) |
| CA (1) | CA2618021C (en) |
| WO (1) | WO2007019389A1 (en) |
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| US20070168027A1 (en) * | 2006-01-13 | 2007-07-19 | Brady Daniel G | Accommodating diffractive intraocular lens |
| CA2674018C (en) * | 2006-12-29 | 2015-05-26 | Advanced Medical Optics, Inc. | Multifocal accommodating intraocular lens |
| US20080161914A1 (en) * | 2006-12-29 | 2008-07-03 | Advanced Medical Optics, Inc. | Pre-stressed haptic for accommodating intraocular lens |
| US8608799B2 (en) * | 2007-01-24 | 2013-12-17 | Tekia, Inc. | Umbrella-shaped accommodating artificial ocular lens (AAOL) device |
-
2006
- 2006-08-07 EP EP06800832A patent/EP1924222A1/en not_active Withdrawn
- 2006-08-07 US US11/499,934 patent/US20070032866A1/en not_active Abandoned
- 2006-08-07 JP JP2008525258A patent/JP2009503622A/en active Pending
- 2006-08-07 WO PCT/US2006/030606 patent/WO2007019389A1/en active Application Filing
- 2006-08-07 CA CA2618021A patent/CA2618021C/en not_active Expired - Fee Related
Also Published As
| Publication number | Publication date |
|---|---|
| WO2007019389A1 (en) | 2007-02-15 |
| US20070032866A1 (en) | 2007-02-08 |
| CA2618021C (en) | 2014-08-05 |
| EP1924222A1 (en) | 2008-05-28 |
| JP2009503622A (en) | 2009-01-29 |
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