WO2003009051A2 - Accommodative intraocular lens - Google Patents

Accommodative intraocular lens Download PDF

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Publication number
WO2003009051A2
WO2003009051A2 PCT/US2002/022785 US0222785W WO03009051A2 WO 2003009051 A2 WO2003009051 A2 WO 2003009051A2 US 0222785 W US0222785 W US 0222785W WO 03009051 A2 WO03009051 A2 WO 03009051A2
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WO
WIPO (PCT)
Prior art keywords
lens
component
intraocular lens
eye
optical
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Application number
PCT/US2002/022785
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French (fr)
Other versions
WO2003009051A3 (en
Inventor
Igor Valyunin
Stephen Q. Zhou
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Medennium, Inc.
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Publication date
Application filed by Medennium, Inc. filed Critical Medennium, Inc.
Priority to AU2002355113A priority Critical patent/AU2002355113A1/en
Publication of WO2003009051A2 publication Critical patent/WO2003009051A2/en
Publication of WO2003009051A3 publication Critical patent/WO2003009051A3/en

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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
    • 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
    • A61F2/1624Intraocular 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
    • A61F2/1629Intraocular 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 longitudinal position, i.e. along the visual axis when implanted
    • 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
    • A61F2/1648Multipart lenses
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B29WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
    • B29DPRODUCING PARTICULAR ARTICLES FROM PLASTICS OR FROM SUBSTANCES IN A PLASTIC STATE
    • B29D11/00Producing optical elements, e.g. lenses or prisms
    • B29D11/02Artificial eyes from organic plastic material
    • B29D11/023Implants for natural eyes
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B29WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
    • B29DPRODUCING PARTICULAR ARTICLES FROM PLASTICS OR FROM SUBSTANCES IN A PLASTIC STATE
    • B29D11/00Producing optical elements, e.g. lenses or prisms
    • B29D11/02Artificial eyes from organic plastic material
    • B29D11/023Implants for natural eyes
    • B29D11/026Comprising more than one lens
    • 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
    • A61F2/0077Special surfaces of prostheses, e.g. for improving ingrowth
    • A61F2002/009Special surfaces of prostheses, e.g. for improving ingrowth for hindering or preventing attachment of biological tissue
    • 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
    • A61F2002/1681Intraocular lenses having supporting structure for lens, e.g. haptics

Definitions

  • the present invention relates to accommodative intraocular lenses used to replace the aged human natural lens to provide multiple focuses by bidirectional shift of the lens optics along the eye's optical axis.
  • the design of the present invention also prevents posterior chamber opacification, a condition normally associated with the removal of the natural human lens, which may lead to secondary cataract formation.
  • the effective focal length of the eye In order for the human eye to have clear vision of objects at different distances, the effective focal length of the eye must be adjusted to keep the image of the object focused as sharply as possible on the retina. This change in effective focal length is known as accommodation and is accomplished in the eye by varying the shape of the crystalline lens.
  • the curvature of the lens is such that distant objects are sharply imaged on the retina.
  • near images are not focused sharply on the retina because the focal points of their images lie behind the retinal surface.
  • the curvature of the crystalline lens In order to visualize a near object clearly, the curvature of the crystalline lens must be increased, thereby increasing its refractive power and causing the focal point of the near object to fall on the retina.
  • the change in shape of the crystalline lens is accomplished by the action of certain muscles and structures within the eyeball or globe of the eye.
  • the lens is located in the forward part of the eye, immediately behind the pupil. It has the shape of a biconvex optical lens, i.e., it has a generally circular cross-section of two-convex-refracting surfaces, and is located generally on the optical axis of the eye, i.e., a straight line drawn from the center of the cornea to the macula in the retina at the posterior portion of the globe.
  • the curvature of the posterior surface of the lens i.e., the surface adjacent to the vitreous body, is somewhat greater than that of the anterior surface.
  • the lens is closely surrounded by a membranous capsule that serves as an intermediate structure in the support and actuation of the lens.
  • the lens and its capsule are suspended on the optical axis behind the pupil by a circular assembly of many radially-directed collagenous fibers, the zonules, which are attached at their inner ends to the lens capsule and at their outer ends to the ciliary body, a muscular ring of tissue located just within the outer supporting structure of the eye, the sclera.
  • the ciliary body is relaxed in the unaccommodated eye and therefore assumes its largest diameter.
  • the relatively large diameter of the ciliary body in this condition causes a tension on the zonules which in turn pull radially outward on the lens capsule, causing the equatorial diameter of the lens to increase slightly, and decreasing the anterior-posterior dimension of the lens at the optical axis.
  • the tension on the lens capsule causes the lens to assume a flattened state wherein the curvature of the anterior surface, and to some extent of the posterior surface, is less than it would be in the absence of the tension.
  • the refractive power of the lens is relatively low and the eye is focused for clear vision of distant objects, i.e., the unaccommodated state.
  • zonules work like a spring with one end attached to the elastic lens and the other end attached to ciliary muscles.
  • the spring In an unaccommodated state, the spring is pulled taut by the ciliary muscles to force the elastic lens to become thin; in an accommodated state, the spring relaxes to relieve the elastic lens so that it becomes thick (see Figures la and lb).
  • the elastic lens In a young and healthy eye, the elastic lens can become thin (low diopter) or thick (high diopter) with about 3 diopters difference. Starting at age mid-forty, a typical eye begins to gradually lose its near distance vision (presbyopia). There are multiple reasons for loss of accommodation. One of them is that the human lens becomes too hard to change back and forth from a thin lens to a thick lens.
  • the change in lens focus power measured in diopter is achieved by a bi-directional shift of the IOL guided by the hinge, along the optical axis.
  • the more the shifting distance toward the anterior chamber the more the focus power for the lens.
  • Gwon, in US Patent 6,176,878 (issued January 23, 2001), discloses an accommodating lens design which is adapted to cooperate with the eye to move the optic body bi- directionally, that is anteriorly or posteriorly in the eye.
  • Israel in US Patent 6,013,101 (issued January 11, 2000), discloses another accommodating lens design with haptics in engagement with zonule movement to achieve a bi-directional shift of the lens along the optical axis.
  • all of these prior art patents utilize various mechanisms to move the optical body of the IOL either anteriorly or posteriorly to achieve near vision, or far vision respectively.
  • Sarfarazi in US Patent 5,275,623, issued January 4, 1994, discloses an elliptical accommodating IOL with two optical bodies positioned in the anterior surface and posterior surface respectively.
  • the lens is a closed cell containing fluids. The accommodation is achieved by adjusting the distance between the two optical bodies of the elliptical IOL.
  • Figure 2 is derived from US Patent 6,197,059, where the IOL is in the backward and forward positions, respectively.
  • the gap between the IOL and posterior surface of the capsular bag in the forward position may invite the growth of epithelial cells so that eventually epithelial cells will occupy any existing space in the capsular bag. Consequently, that structure could lead to secondary cataract formation.
  • the epithelial cell's in-growth into the gap may hinder and eventually prevent the IOL from shifting along the optical axis, thus resulting in a loss in accommodation once again.
  • the present invention discloses a family of accommodating lenses designed to avoid secondary cataract formation while providing accommodating capabilities.
  • the present invention provides an accommodative intraocular lens for replacing the aged human natural lens.
  • the lens provides multiple focuses utilizing a bi-directional shift of the lens optics along the eye's optical axis.
  • the lenses of the present invention also prevent posterior chamber opacification, a condition normally associated with the removal of the natural human lens which may lead to secondary cataract formation.
  • These intraocular lenses comprise:
  • a first component which consists of an optical body and a haptic body adjacent and attached to said optical body;
  • a second component located posterior to said first component, which is structurally adapted to maintain substantial contact with the posterior surface of the capsular bag when implanted in the eye;
  • the lens being configured so as to allow the first component to move forward and back relative to the second component, along the optical axis of the optical body.
  • the accommodative lens structures may optimally include additional optional features, such as guiding grooves for assisting the bi-directional shift of the first component of the lens.
  • the present invention also encompasses the method of implanting these accommodative lenses in the eye.
  • Figure 1(a) is a schematic cutaway view of an eye in its unaccommodated state and Figure 1(b) is a schematic cutaway view of an eye in its accommodated state.
  • Figure 2 is a side view of an example of an accommodative lens design from the prior art.
  • Figure 3 is a schematic cutaway view of one embodiment of the present invention.
  • Figure 4 is the isometric view of the lens of Figure 3.
  • Figure 5(a) and Figure 5(b) are isometric views of a lens of the present invention in its accommodated state and unaccommodated state respectively.
  • Figures 5(c) and 5(d) are schematic views showing placement of the lens in the eye.
  • Figure 6 is an isometric view of an embodiment of the present invention similar to Figure 4 except that there are fenestration holes in the haptic body.
  • Figure 7 is an isometric view of an embodiment of the present invention similar to Figure 6 except the optical body in Figure 7 is a negative lens while Figure 6 has a positive optical body.
  • Figures 8 and 9 are isometric views of embodiments of the present invention including a groove in the transition zone.
  • Figure 10 is a perspective view of an embodiment of the present invention showing the groove in the haptic area.
  • Figure 11 is a perspective view of an embodiment of the present invention showing that part of the dioptic power may be provided by the second component of the lens.
  • Figures 12 and 13 are isometric views of two additional embodiments of the present invention.
  • Figure 14 shows the mold used for making the lenses of the present invention.
  • the present invention provides an accommodating lens for patients whose natural lens has been removed. It also provides an accommodating lens which can avoid secondary cataract formation. These and other additional objects are achieved by providing an accommodating lens which has two main components. The first component is for providing the optical function as the lens and the second component is for preventing PCO. Additional optional lens structure features include a guiding function which directs the optical body of the lens in its bi-directional movement, i.e., towards the anterior or posterior chambers along the eye's optical axis, corresponding to the contraction or relaxation of the ciliary muscle via the zonules.
  • One embodiment in accordance with the present invention is an accommodating lens design as illustrated in Figure 3 and its isometric view in Figure 4.
  • the lens has two components 1 and 2 as well as a transition zone (3).
  • Component 1 is the anterior portion of the lens containing an optical body (4) with an optical diameter in the range of from about 4 to about 7 mm and a haptic body(5).
  • the haptic bodies (5) extend outward from opposite edges of the optical body (4).
  • the optical body can be designed to be a positive or negative lens with any optical configurations, such as biconvex, biconcave, plano-convex, or plano-concave.
  • Component 1 also has a first radius of curvature (Rl in Fig.
  • the lens' overall central thickness (T in Fig. 3) is in the range of about 2 to about 5 mm, preferably from about 3 to about 4 mm.
  • the overall length (L in Fig. 3) of the lens is in the range of from about 8 to about 13 mm, preferably from about 8 to about 11 mm.
  • Component 2 is the posterior portion of the lens with the second radius of curvature (R2 in Figure 3) which approximately matches with that of the human capsule, such as from about 5 to about 9 mm, preferably from about 6 to about 7.5 mm. In this way, component 2 maintains a tight contact with the posterior bag tissue.
  • the main purpose for component 2 is to provide a means to prevent epithelial cells from growing into the central lens area so that the PCO can be avoided. Since this second component is located posterior to the optical body, it must allow light to pass through it (for example, by being optically transparent or by having a cut-out section along the line of the optical axis of the first component).
  • the transition zone (3) connects component 1 with component 2 and blends the two radii of curvature in a smooth way.
  • the transition zone begins at the end of the haptics and continues until the beginning of the radius of curvature of component 2 is reached.
  • the main function of the transition zone is to assist the accommodative lens to change focus by axial shift (forward and back) of the optic body.
  • an accommodative IOL can be made from elastomeric polymers having appropriate shape memory properties.
  • elastomeric polymers include, but are not limited to, silicones, acrylic polymers, and hydrogels.
  • the materials used to make the lenses of the present invention are optically clear and of sufficient purity and biocompatibility to permit placement in the eye.
  • the IOL comprises component 1 (optical body + haptics), component 2 (the posterior portion of the lens), and a transition zone.
  • Component 1 is the optical body with a first radius of curvature and component 2 has a second radius of curvature, connected by a transitional area which blends components 1 and 2 in a smooth way.
  • the IOL is made in its accommodated state, with the first radius (Rl) being larger than the second radius (R2).
  • the accommodating lens maintains its initial shape, i.e., when the ciliary muscle relaxes.
  • ciliary muscle contracts, it tightens up the zonules. This stretches the accommodative IOL so that component 1, i.e., the optical lens, will move along the optical axis toward the posterior chamber.
  • the optical power of the lens is reduced due to the shift of the lens along the optical axis, thereby providing far distance vision (see Figures 5(b) and 5(d)).
  • the accommodative IOL returns to its initial accommodative lens state due to its material shape memory or elasticity (see Figures 5(a) and 5(c)). Note that in Figures 5(c) and 5(d), when the lens is implanted in the eye, component 2 is in contact with the posterior surface of the capsular bag. This contact prevents or minimizes secondary cataract formation, and helps transmit ciliary muscle force to the lens.
  • Additional design features include the selection of different thicknesses for the first component and second component.
  • the second component has a larger thickness than the haptics of the first component, the second component has a stronger mechanical strength than the first component.
  • the second component works as an arch to support the first component.
  • the first component will shift its position toward the posterior chamber, equivalent to a change from an accommodated state to an unaccommodated state (See Figure 5).
  • a 1 mm axial shift is equivalent to a change of about 1 - 2 diopters in optical power.
  • a portion of the diopter power can be provided by the second component.
  • An example of this design is illustrated in Figure 11. In any event, after implantation, component 2 must remain in a substantially close contact with the posterior surface of the capsular bag.
  • the present invention may include guiding structures to help the lens shift in response to ciliary muscle movement.
  • These guiding structures may, for example, be a groove in the transition zone, such as illustrated in Figures 8, 9, or in the haptic body of component 1, as shown in Figure 10.
  • the zonules are tightened up. This flattens the IOL (particularly at the location of the guiding groove) and the optical body shifts toward the posterior chamber. This posterior shift is equivalent to the decrease of the optical power of the IOL.
  • zonules are relaxed and the capsule recovers back to its un-stretched shape.
  • This relaxation of zonules allows the first component of the accommodating lens to shift forward, i.e., move toward the anterior chamber, resuming its initial lens shape and optic power. This shape recovery is further assisted by a forward pushing force caused by a pressure increase due to the vitreous outflow from the posterior chamber to the interior chamber. This vault toward the anterior chamber is equivalent to an increase in the IOL's optical power, thereby, providing an improvement in near distance vision.
  • the present invention provides a novel lens design which includes a second component having a radius of curvature similar to that of a human natural lens in the range of from about 5 to about 9 mm, preferably from about 6 to about 7.5 mm. This way, the second component usually maintains a close contact with the posterior surface of the capsular bag, preventing endothelial cells from growing into the space in between the implant and the capsular bag.
  • Intraocular lenses with designs similar to that shown in Figure 2 have been successfully made as follows: In a three-piece (bottom piece, top piece, and the insert piece, see Figure 14) stainless steel mold, was added an appropriate amount of medical grade silicone (NuSil Silicone Technology, MED 6820) onto the bottom piece. The insert piece was carefully placed on the center of the bottom piece followed by the top piece with appropriate lining. The closed mold was tightly clamped and placed in a pre-heated oven at a temperature in the range of 110-140°C for about 30 to 60 minutes. When the mold cooled down to the room temperature, the top piece was removed.
  • medical grade silicone NuSil Silicone Technology, MED 6820
  • aqueous lubricant such as Healon (manufactured by Pharmacia) was used to wet the space between the insert piece and the intraocular lens. After the majority of the space was lubricated, the insert piece of the mold was pushed out while the lens remained on the bottom piece. The lens was carefully removed from the bottom piece.

Abstract

An accommodative intraocular lens is disclosed. The lens provides multiple focuses as the result of a bi-directional shift along the eye's optical axis, and also minimizes or prevents posterior chamber opacification. The lens includes a first component which consists of an optical body and a haptic body, a second component which is structurally adapted to maintain substantial contact with the posterior surface of the capsular bag of the eye (when implanted in the eye), and a transition zone connecting the first and second components. The method of implanting the lens in the eye and the method of making the lens are also disclosed.

Description

ACCOMMODATIVE INTRAOCULAR LENS
Igor Valyunin Stephen Q. Zhou
CROSS-REFERENCE TO RELATED APPLICATION
[001] This application claims priority from U.S. Provisional Patent
Application No. 60/306,031, filed July 17, 2001.
TECHNICAL FIELD
[002] The present invention relates to accommodative intraocular lenses used to replace the aged human natural lens to provide multiple focuses by bidirectional shift of the lens optics along the eye's optical axis. The design of the present invention also prevents posterior chamber opacification, a condition normally associated with the removal of the natural human lens, which may lead to secondary cataract formation.
BACKGROUND OF THE INVENTION
[003] In order for the human eye to have clear vision of objects at different distances, the effective focal length of the eye must be adjusted to keep the image of the object focused as sharply as possible on the retina. This change in effective focal length is known as accommodation and is accomplished in the eye by varying the shape of the crystalline lens. Generally, in the unaccommodated emmetropic eye, the curvature of the lens is such that distant objects are sharply imaged on the retina. In the unaccommodated eye, near images are not focused sharply on the retina because the focal points of their images lie behind the retinal surface. In order to visualize a near object clearly, the curvature of the crystalline lens must be increased, thereby increasing its refractive power and causing the focal point of the near object to fall on the retina.
The change in shape of the crystalline lens is accomplished by the action of certain muscles and structures within the eyeball or globe of the eye. The lens is located in the forward part of the eye, immediately behind the pupil. It has the shape of a biconvex optical lens, i.e., it has a generally circular cross-section of two-convex-refracting surfaces, and is located generally on the optical axis of the eye, i.e., a straight line drawn from the center of the cornea to the macula in the retina at the posterior portion of the globe. Generally, the curvature of the posterior surface of the lens, i.e., the surface adjacent to the vitreous body, is somewhat greater than that of the anterior surface. The lens is closely surrounded by a membranous capsule that serves as an intermediate structure in the support and actuation of the lens. The lens and its capsule are suspended on the optical axis behind the pupil by a circular assembly of many radially-directed collagenous fibers, the zonules, which are attached at their inner ends to the lens capsule and at their outer ends to the ciliary body, a muscular ring of tissue located just within the outer supporting structure of the eye, the sclera. The ciliary body is relaxed in the unaccommodated eye and therefore assumes its largest diameter. According to the classical theory of accommodation, the relatively large diameter of the ciliary body in this condition causes a tension on the zonules which in turn pull radially outward on the lens capsule, causing the equatorial diameter of the lens to increase slightly, and decreasing the anterior-posterior dimension of the lens at the optical axis. Thus, the tension on the lens capsule causes the lens to assume a flattened state wherein the curvature of the anterior surface, and to some extent of the posterior surface, is less than it would be in the absence of the tension. In this state, the refractive power of the lens is relatively low and the eye is focused for clear vision of distant objects, i.e., the unaccommodated state. [005] In an accommodative state, however, the eye is intended to be focused on a near object, the muscles of the ciliary body contract. This contraction causes the ciliary body to move forward and inward, thereby relaxing the outward pull of the zonules on the equator of the lens capsule. This reduced zonular tension allows the elastic capsule of the lens to contract causing an increase in the anterior-posterior diameter of the lens (i.e., the lens becomes more spherical) resulting in an increase in the optical power of the lens. Because of topographical differences in the thickness of the lens capsule, the central anterior radius of curvature decreases more than the central posterior radius of curvature. This is the accommodated condition of the eye wherein the image of near objects falls sharply on the retina. See Koretz, et al., Scientific American, July, 1988, pages 64-71.
[006] In a simplified model, zonules work like a spring with one end attached to the elastic lens and the other end attached to ciliary muscles. In an unaccommodated state, the spring is pulled taut by the ciliary muscles to force the elastic lens to become thin; in an accommodated state, the spring relaxes to relieve the elastic lens so that it becomes thick (see Figures la and lb). In a young and healthy eye, the elastic lens can become thin (low diopter) or thick (high diopter) with about 3 diopters difference. Starting at age mid-forty, a typical eye begins to gradually lose its near distance vision (presbyopia). There are multiple reasons for loss of accommodation. One of them is that the human lens becomes too hard to change back and forth from a thin lens to a thick lens.
[007] The common approach for addressing the problem of the loss of accommodation is to wear reading glasses. However, various attempts have been made to solve presbyopia by implanting an accommodating IOL. A number of US Patents disclose various means for moving the optical body of an IOL along the optical axis anteriorly or posteriorly so that optical power of the IOL can be adjusted to provide either near vision or far vision. For example, Gumming, in his US Patents 6,197,059 (issued March 6, 2001) and 5,476,514 (issued December 19, 1995), discloses an accommodating intraocular lens design similar to a plate IOL except that there is a guiding hinge on each side of the haptics (see Figure 2). The guiding hinge is intended to facilitate the lens in vaulting anteriorly for near vision or posteriorly for distance vision. In other words, the change in lens focus power measured in diopter is achieved by a bi-directional shift of the IOL guided by the hinge, along the optical axis. The more the shifting distance toward the anterior chamber, the more the focus power for the lens. Gwon, in US Patent 6,176,878 (issued January 23, 2001), discloses an accommodating lens design which is adapted to cooperate with the eye to move the optic body bi- directionally, that is anteriorly or posteriorly in the eye. Similarly, Israel, in US Patent 6,013,101 (issued January 11, 2000), discloses another accommodating lens design with haptics in engagement with zonule movement to achieve a bi-directional shift of the lens along the optical axis. In summary, all of these prior art patents utilize various mechanisms to move the optical body of the IOL either anteriorly or posteriorly to achieve near vision, or far vision respectively.
[008] Sarfarazi, in US Patent 5,275,623, issued January 4, 1994, discloses an elliptical accommodating IOL with two optical bodies positioned in the anterior surface and posterior surface respectively. The lens is a closed cell containing fluids. The accommodation is achieved by adjusting the distance between the two optical bodies of the elliptical IOL.
[009] Although accommodating IOL's are known, there is one common complication associated with the IOL implantation: that is posterior chamber opacification (PCO), where cells migrate from equatorial peripheries towards the center of the capsular bag. These cells block incoming light from reaching the retina. Consequently, PCO will cause gradual vision loss, and in some cases complete vision loss, if untreated. This cell migration after cataract surgery is also known as secondary cataract formation. [010] None of the prior art patents on accommodative lenses includes a feature designed for addressing the PCO problem. In fact, some of the designs disclosed in the prior art may invite the epithelial cells in-growth. For example, Figure 2 is derived from US Patent 6,197,059, where the IOL is in the backward and forward positions, respectively. The gap between the IOL and posterior surface of the capsular bag in the forward position may invite the growth of epithelial cells so that eventually epithelial cells will occupy any existing space in the capsular bag. Consequently, that structure could lead to secondary cataract formation. Furthermore, the epithelial cell's in-growth into the gap may hinder and eventually prevent the IOL from shifting along the optical axis, thus resulting in a loss in accommodation once again.
[oil] It has been estimated that about one-third of the patients who undergo cataract surgery with IOL implantation will eventually develop PCO or secondary cataract formation. The common procedure for treating PCO is using a Yag laser. The laser beam burns cells situated in its pathway to allow images to reach and focus on the retina again so patients regain their vision. This laser treatment is not only a costly procedure but also involves significant risks for the patient. For example, if the laser beam is focused on any part of the eye tissue by mistake, it will cause unnecessary permanent tissue damage or possibly even permanent vision loss.
[012] Accordingly, there is a great need to provide an accommodating lens which can avoid or reduce the possibility of forming a secondary cataract. The present invention discloses a family of accommodating lenses designed to avoid secondary cataract formation while providing accommodating capabilities.
SUMMARY OF THE INVENTION
[013] The present invention provides an accommodative intraocular lens for replacing the aged human natural lens. The lens provides multiple focuses utilizing a bi-directional shift of the lens optics along the eye's optical axis. The lenses of the present invention also prevent posterior chamber opacification, a condition normally associated with the removal of the natural human lens which may lead to secondary cataract formation. These intraocular lenses comprise:
i. a first component which consists of an optical body and a haptic body adjacent and attached to said optical body;
ii. a second component, located posterior to said first component, which is structurally adapted to maintain substantial contact with the posterior surface of the capsular bag when implanted in the eye; and
iii. a transition zone which smoothly connects the first and the second components;
the lens being configured so as to allow the first component to move forward and back relative to the second component, along the optical axis of the optical body.
[014] The accommodative lens structures may optimally include additional optional features, such as guiding grooves for assisting the bi-directional shift of the first component of the lens.
[015] The present invention also encompasses the method of implanting these accommodative lenses in the eye.
[016] Lastly, because of the complexity of the lens structure in the present invention, a novel method of molding such lenses in a three-piece mold is also disclosed. BRIEF DESCRIPTION OF THE DRAWINGS
[017] Figure 1(a) is a schematic cutaway view of an eye in its unaccommodated state and Figure 1(b) is a schematic cutaway view of an eye in its accommodated state.
[018] Figure 2 is a side view of an example of an accommodative lens design from the prior art.
[019] Figure 3 is a schematic cutaway view of one embodiment of the present invention.
[020] Figure 4 is the isometric view of the lens of Figure 3.
[021] Figure 5(a) and Figure 5(b) are isometric views of a lens of the present invention in its accommodated state and unaccommodated state respectively. Figures 5(c) and 5(d) are schematic views showing placement of the lens in the eye.
[022] Figure 6 is an isometric view of an embodiment of the present invention similar to Figure 4 except that there are fenestration holes in the haptic body.
[023] Figure 7 is an isometric view of an embodiment of the present invention similar to Figure 6 except the optical body in Figure 7 is a negative lens while Figure 6 has a positive optical body.
[024] Figures 8 and 9 are isometric views of embodiments of the present invention including a groove in the transition zone.
[025] Figure 10 is a perspective view of an embodiment of the present invention showing the groove in the haptic area.
[026] Figure 11 is a perspective view of an embodiment of the present invention showing that part of the dioptic power may be provided by the second component of the lens. [027] Figures 12 and 13 are isometric views of two additional embodiments of the present invention.
[028] Figure 14 shows the mold used for making the lenses of the present invention.
DETAILED DESCRIPTION OF THE INVENTION
[029] The present invention provides an accommodating lens for patients whose natural lens has been removed. It also provides an accommodating lens which can avoid secondary cataract formation. These and other additional objects are achieved by providing an accommodating lens which has two main components. The first component is for providing the optical function as the lens and the second component is for preventing PCO. Additional optional lens structure features include a guiding function which directs the optical body of the lens in its bi-directional movement, i.e., towards the anterior or posterior chambers along the eye's optical axis, corresponding to the contraction or relaxation of the ciliary muscle via the zonules.
[030] One embodiment in accordance with the present invention is an accommodating lens design as illustrated in Figure 3 and its isometric view in Figure 4. The lens has two components 1 and 2 as well as a transition zone (3). Component 1 is the anterior portion of the lens containing an optical body (4) with an optical diameter in the range of from about 4 to about 7 mm and a haptic body(5). The haptic bodies (5) extend outward from opposite edges of the optical body (4). The optical body can be designed to be a positive or negative lens with any optical configurations, such as biconvex, biconcave, plano-convex, or plano-concave. Component 1 also has a first radius of curvature (Rl in Fig. 3) similar to that of a human natural lens usually in the range of from about 8 to about 13 mm, preferably from about 9 to about 11 mm. The main function of component 1 is that its optical powers measured in diopters can be changed by shifting the optical element along the optical axis towards or away from the posterior chamber. Typically, the lens' overall central thickness (T in Fig. 3) is in the range of about 2 to about 5 mm, preferably from about 3 to about 4 mm. The overall length (L in Fig. 3) of the lens is in the range of from about 8 to about 13 mm, preferably from about 8 to about 11 mm.
[031] Component 2 is the posterior portion of the lens with the second radius of curvature (R2 in Figure 3) which approximately matches with that of the human capsule, such as from about 5 to about 9 mm, preferably from about 6 to about 7.5 mm. In this way, component 2 maintains a tight contact with the posterior bag tissue. The main purpose for component 2 is to provide a means to prevent epithelial cells from growing into the central lens area so that the PCO can be avoided. Since this second component is located posterior to the optical body, it must allow light to pass through it (for example, by being optically transparent or by having a cut-out section along the line of the optical axis of the first component). The transition zone (3) connects component 1 with component 2 and blends the two radii of curvature in a smooth way. Thus, the transition zone begins at the end of the haptics and continues until the beginning of the radius of curvature of component 2 is reached. The main function of the transition zone is to assist the accommodative lens to change focus by axial shift (forward and back) of the optic body.
[032] This axial shift of the optical body of the IOL can be achieved as a result of its material's shape memory properties or its structural configurations, or both. For example, an accommodative IOL can be made from elastomeric polymers having appropriate shape memory properties. Such elastomeric polymers are known in the art and include, but are not limited to, silicones, acrylic polymers, and hydrogels. The materials used to make the lenses of the present invention are optically clear and of sufficient purity and biocompatibility to permit placement in the eye. Structurally, the IOL comprises component 1 (optical body + haptics), component 2 (the posterior portion of the lens), and a transition zone. Component 1 is the optical body with a first radius of curvature and component 2 has a second radius of curvature, connected by a transitional area which blends components 1 and 2 in a smooth way. Generally, the IOL is made in its accommodated state, with the first radius (Rl) being larger than the second radius (R2). When implanted in the eye (see Figures 5(c) and (d)), the accommodating lens maintains its initial shape, i.e., when the ciliary muscle relaxes. When ciliary muscle contracts, it tightens up the zonules. This stretches the accommodative IOL so that component 1, i.e., the optical lens, will move along the optical axis toward the posterior chamber. As a result, the optical power of the lens is reduced due to the shift of the lens along the optical axis, thereby providing far distance vision (see Figures 5(b) and 5(d)). When the zonule stretching force is absent, the accommodative IOL returns to its initial accommodative lens state due to its material shape memory or elasticity (see Figures 5(a) and 5(c)). Note that in Figures 5(c) and 5(d), when the lens is implanted in the eye, component 2 is in contact with the posterior surface of the capsular bag. This contact prevents or minimizes secondary cataract formation, and helps transmit ciliary muscle force to the lens.
[033] Additional design features include the selection of different thicknesses for the first component and second component. For example, when the second component has a larger thickness than the haptics of the first component, the second component has a stronger mechanical strength than the first component. In other words, the second component works as an arch to support the first component. When the zonules pull the accommodative lens, the arch will extend outwardly while still maintaining close contact with the posterior surface of the capsular bag. The first component will shift its position toward the posterior chamber, equivalent to a change from an accommodated state to an unaccommodated state (See Figure 5). Approximately, a 1 mm axial shift is equivalent to a change of about 1 - 2 diopters in optical power.
[034] It is also within the scope of the present invention that a portion of the diopter power can be provided by the second component. An example of this design is illustrated in Figure 11. In any event, after implantation, component 2 must remain in a substantially close contact with the posterior surface of the capsular bag.
[035] The present invention may include guiding structures to help the lens shift in response to ciliary muscle movement. These guiding structures may, for example, be a groove in the transition zone, such as illustrated in Figures 8, 9, or in the haptic body of component 1, as shown in Figure 10. In a non- accommodative state, the zonules are tightened up. This flattens the IOL (particularly at the location of the guiding groove) and the optical body shifts toward the posterior chamber. This posterior shift is equivalent to the decrease of the optical power of the IOL. On the other hand, in an accommodative state, zonules are relaxed and the capsule recovers back to its un-stretched shape. This relaxation of zonules allows the first component of the accommodating lens to shift forward, i.e., move toward the anterior chamber, resuming its initial lens shape and optic power. This shape recovery is further assisted by a forward pushing force caused by a pressure increase due to the vitreous outflow from the posterior chamber to the interior chamber. This vault toward the anterior chamber is equivalent to an increase in the IOL's optical power, thereby, providing an improvement in near distance vision.
[036] It is well known that when an intraocular lens is implanted in place of the natural lens, whether a cataract lens or a clear lens, there is always a possibility for PCO. The lens of the present invention minimizes or prevents PCO by always maintaining close contact with the capsular bag. This leaves no space for epithelial cells to grow into. To solve this PCO problem, the present invention provides a novel lens design which includes a second component having a radius of curvature similar to that of a human natural lens in the range of from about 5 to about 9 mm, preferably from about 6 to about 7.5 mm. This way, the second component usually maintains a close contact with the posterior surface of the capsular bag, preventing endothelial cells from growing into the space in between the implant and the capsular bag.
Example - Molding of the Accommodative Lens
Intraocular lenses with designs similar to that shown in Figure 2 have been successfully made as follows: In a three-piece (bottom piece, top piece, and the insert piece, see Figure 14) stainless steel mold, was added an appropriate amount of medical grade silicone (NuSil Silicone Technology, MED 6820) onto the bottom piece. The insert piece was carefully placed on the center of the bottom piece followed by the top piece with appropriate lining. The closed mold was tightly clamped and placed in a pre-heated oven at a temperature in the range of 110-140°C for about 30 to 60 minutes. When the mold cooled down to the room temperature, the top piece was removed. An aqueous lubricant, such as Healon (manufactured by Pharmacia), was used to wet the space between the insert piece and the intraocular lens. After the majority of the space was lubricated, the insert piece of the mold was pushed out while the lens remained on the bottom piece. The lens was carefully removed from the bottom piece.

Claims

What is claimed is:
1. An intraocular lens comprising: i. a first component which consists of an optical body and a haptic body adjacent and attached to said optical body; ii. a second component, located posterior to said first component, which is structurally adapted to maintain substantial contact with the posterior surface of the capsular bag when implanted in the eye; and iii. a transition zone which smoothly connects the first component with the second component; the lens being configured so as to allow the first component to move forward and back relative to the second component, along the optical axis of the optical body.
2. The intraocular lens of Claim 1 wherein its overall diameter is from about 8 to about 13 mm.
3. The intraocular lens of Claim 1 having a central lens thickness of from about 2 to about 5 mm.
4. The intraocular lens of Claim 1 wherein said optical body has a diameter of from about 4 to about 7 mm.
5. The intraocular lens of Claim 1 wherein said first component has a radius of curvature of from about 8 to about 13 mm.
6. The intraocular lens of Claim 1 wherein said second component has a radius of curvature of from about 5 to about 9 mm.
7. The intraocular lens of Claim 4 having an overall diameter of from about 9 to about 11 mm, a central lens thickness of from about 3 to about 4 mm, a first component radius of curvature from about 9 to about 11 mm, and a second component radius of from about 6 to about 7.5 mm.
8. The intraocular lens of Claim 1 which further comprises at least one guiding structure structurally adapted to assist the optical body of said first component in shifting bi-directionally along optical axis.
9. The intraocular lens of Claim 8 wherein said at least one guiding structure is a groove.
10. The intraocular lens of Claim 9 wherein said at least one guiding structure is on the haptic body.
11. The intraocular lens of Claim 9 wherein said at least one guiding structure is on the transition zone.
12. The intraocular lens of Claim 1 wherein said lens is made from optically clear elastomeric materials.
13. The intraocular lens of Claim 12 wherein the elastomeric material is selected from silicones, acrylic materials, hydrogels, and mixtures thereof.
14. The method of implanting the intraocular lens of Claim 1 into the eye of a patient wherein the second component is placed in the eye so as to be posterior to said first component and is in substantial contact with the posterior surface of the capsular bag of the eye.
15. The method of molding the intraocular lens of Claim 1 using a mold comprising a bottom piece , a top piece, and an insertion piece which is placed inside and between said bottom and top pieces during the molding process to form the hollow center of said intraocular lens.
16. The method of molding the intraocular lens of Claim 1 comprising placing an optically clear elastomeric material selected from silicones, acrylics materials, hydrogels, and mixtures thereof, in a flowable state, inside a mold comprising a bottom piece, a top piece and an insertion piece which is placed in said elastomeric material between said bottom and top pieces during said molding process to form the hollow center of said intraocular lens; allowing said elastomeric material to harden in the mold; removing the insertion piece from the lens; and removing the lens from the mold.
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Cited By (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2004106045A1 (en) * 2003-05-27 2004-12-09 Faezeh Mona Sarfarazi Mold for intraocular lens
WO2008079671A1 (en) * 2006-12-22 2008-07-03 Bausch & Lomb Incorporated Multi-element accommodative intraocular lens
US7780729B2 (en) 2004-04-16 2010-08-24 Visiogen, Inc. Intraocular lens
US8182531B2 (en) 2006-12-22 2012-05-22 Amo Groningen B.V. Accommodating intraocular lenses and associated systems, frames, and methods
US8486140B2 (en) 2001-01-30 2013-07-16 Timothy R. Willis Refractive intraocular implant lens and method
US8579970B1 (en) 2005-06-27 2013-11-12 Visiogen, Inc. Magnifying intraocular lens
US9011532B2 (en) 2009-06-26 2015-04-21 Abbott Medical Optics Inc. Accommodating intraocular lenses
US9039760B2 (en) 2006-12-29 2015-05-26 Abbott Medical Optics Inc. Pre-stressed haptic for accommodating intraocular lens
EP2805694A4 (en) * 2012-01-19 2015-09-30 Eyebright Medical Technology Beijing Co Ltd Posterior chamber-type intraocular lens
US9198752B2 (en) 2003-12-15 2015-12-01 Abbott Medical Optics Inc. Intraocular lens implant having posterior bendable optic
US9271830B2 (en) 2002-12-05 2016-03-01 Abbott Medical Optics Inc. Accommodating intraocular lens and method of manufacture thereof
US9504560B2 (en) 2002-01-14 2016-11-29 Abbott Medical Optics Inc. Accommodating intraocular lens with outer support structure
US9603703B2 (en) 2009-08-03 2017-03-28 Abbott Medical Optics Inc. Intraocular lens and methods for providing accommodative vision
US9636213B2 (en) 2005-09-30 2017-05-02 Abbott Medical Optics Inc. Deformable intraocular lenses and lens systems
US9814570B2 (en) 1999-04-30 2017-11-14 Abbott Medical Optics Inc. Ophthalmic lens combinations
US9968441B2 (en) 2008-03-28 2018-05-15 Johnson & Johnson Surgical Vision, Inc. Intraocular lens having a haptic that includes a cap
US9987125B2 (en) 2012-05-02 2018-06-05 Johnson & Johnson Surgical Vision, Inc. Intraocular lens with shape changing capability to provide enhanced accomodation and visual acuity
US10695166B2 (en) 2015-08-14 2020-06-30 Timothy R. Willis Intraocular lenses (IOLs) and related assemblies and intraocular attachment methods
US11707354B2 (en) 2017-09-11 2023-07-25 Amo Groningen B.V. Methods and apparatuses to increase intraocular lenses positional stability

Families Citing this family (95)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040015236A1 (en) * 1991-11-18 2004-01-22 Sarfarazi Faezeh M. Sarfarazi elliptical accommodative intraocular lens for small incision surgery
US8556967B2 (en) 1999-04-09 2013-10-15 Faezeh Mona Sarfarazi Interior bag for a capsular bag and injector
US7662179B2 (en) 1999-04-09 2010-02-16 Sarfarazi Faezeh M Haptics for accommodative intraocular lens system
US20030060881A1 (en) 1999-04-30 2003-03-27 Advanced Medical Optics, Inc. Intraocular lens combinations
US8062361B2 (en) * 2001-01-25 2011-11-22 Visiogen, Inc. Accommodating intraocular lens system with aberration-enhanced performance
US20030078657A1 (en) * 2001-01-25 2003-04-24 Gholam-Reza Zadno-Azizi Materials for use in accommodating intraocular lens system
US20060184244A1 (en) * 2005-02-14 2006-08-17 Nguyen Tuan A Biasing system for intraocular lens
US6818158B2 (en) 2001-01-25 2004-11-16 Visiogen, Inc. Accommodating intraocular lens system and method of making same
US20030078658A1 (en) * 2001-01-25 2003-04-24 Gholam-Reza Zadno-Azizi Single-piece accomodating intraocular lens system
US6884261B2 (en) * 2001-01-25 2005-04-26 Visiogen, Inc. Method of preparing an intraocular lens for implantation
US6786934B2 (en) 2001-01-25 2004-09-07 Visiogen, Inc. Biasing element for intraocular lens system
US20030060878A1 (en) 2001-08-31 2003-03-27 Shadduck John H. Intraocular lens system and method for power adjustment
US20070100445A1 (en) * 2003-02-03 2007-05-03 Shadduck John H Intraocular lenses and business methods
US20050021139A1 (en) * 2003-02-03 2005-01-27 Shadduck John H. Ophthalmic devices, methods of use and methods of fabrication
US7261737B2 (en) * 2002-12-12 2007-08-28 Powervision, Inc. Accommodating intraocular lens system and method
US8048155B2 (en) 2002-02-02 2011-11-01 Powervision, Inc. Intraocular implant devices
US6935743B2 (en) * 2002-02-06 2005-08-30 John H. Shadduck Adaptive optic lens and method of making
CA2849167C (en) * 2002-07-25 2016-06-28 Visiogen, Inc. Intraocular lenses and methods of preparing or making same
US7682141B2 (en) * 2002-09-30 2010-03-23 3Dm Worldwide Plc Production apparatus for forming plastic molded articles
US7637947B2 (en) * 2002-12-12 2009-12-29 Powervision, Inc. Accommodating intraocular lens system having spherical aberration compensation and method
EP1569581A4 (en) * 2002-12-12 2006-09-20 Powervision Lens system for power adjustment using micropumps
US8328869B2 (en) 2002-12-12 2012-12-11 Powervision, Inc. Accommodating intraocular lenses and methods of use
US7217288B2 (en) * 2002-12-12 2007-05-15 Powervision, Inc. Accommodating intraocular lens having peripherally actuated deflectable surface and method
US8361145B2 (en) 2002-12-12 2013-01-29 Powervision, Inc. Accommodating intraocular lens system having circumferential haptic support and method
US10835373B2 (en) 2002-12-12 2020-11-17 Alcon Inc. Accommodating intraocular lenses and methods of use
US7247168B2 (en) * 2002-12-12 2007-07-24 Powervision, Inc. Accommodating intraocular lens system and method
CA2507694C (en) * 2002-12-12 2012-07-31 Victor Esch Accommodating intraocular lens system and method
US7615056B2 (en) 2003-02-14 2009-11-10 Visiogen, Inc. Method and device for compacting an intraocular lens
WO2004090611A2 (en) * 2003-03-31 2004-10-21 Bausch & Lomb Incorporated Intraocular lens and method for reducing aberrations in an ocular system
US7905917B2 (en) 2003-03-31 2011-03-15 Bausch & Lomb Incorporated Aspheric lenses and lens family
US7645300B2 (en) * 2004-02-02 2010-01-12 Visiogen, Inc. Injector for intraocular lens system
US20060001186A1 (en) * 2004-06-30 2006-01-05 Richardson Gary A IOL and method of manufacturing an IOL
US8057217B2 (en) 2004-09-30 2011-11-15 Bausch + Lomb Incorporated Apparatus and method for injection molding an intraocular lens device
US9872763B2 (en) 2004-10-22 2018-01-23 Powervision, Inc. Accommodating intraocular lenses
US8377123B2 (en) 2004-11-10 2013-02-19 Visiogen, Inc. Method of implanting an intraocular lens
NL1029403C2 (en) * 2005-07-01 2007-01-04 Medical Device Production B V Multi focal intraoccular lens, has lens part with two optical fields and deformable and non deformable haptics
WO2007019389A1 (en) * 2005-08-05 2007-02-15 Visiogen, Inc. Accommodating diffractive intraocular lens
US20070088433A1 (en) * 2005-10-17 2007-04-19 Powervision Accommodating intraocular lens system utilizing direct force transfer from zonules and method of use
US7985253B2 (en) * 2005-12-07 2011-07-26 C&C Vision International Limited Hydrolic accommodating intraocular lens
US20070168027A1 (en) * 2006-01-13 2007-07-19 Brady Daniel G Accommodating diffractive intraocular lens
US20070260309A1 (en) * 2006-05-08 2007-11-08 Richardson Gary A Accommodating intraocular lens having a recessed anterior optic
WO2007134019A2 (en) * 2006-05-08 2007-11-22 Bausch & Lomb Incorporated Accommodative intraocular lens having defined axial compression characteristics
US8403984B2 (en) 2006-11-29 2013-03-26 Visiogen, Inc. Apparatus and methods for compacting an intraocular lens
WO2008103798A2 (en) * 2007-02-21 2008-08-28 Powervision, Inc. Polymeric materials suitable for ophthalmic devices and methods of manufacture
US20080306587A1 (en) * 2007-02-21 2008-12-11 Jingjong Your Lens Material and Methods of Curing with UV Light
KR100807940B1 (en) * 2007-03-08 2008-02-28 박경진 Intraocular lens
KR100807939B1 (en) * 2007-03-08 2008-02-28 박경진 Lens assembly
US20090228101A1 (en) * 2007-07-05 2009-09-10 Visiogen, Inc. Intraocular lens with post-implantation adjustment capabilities
EP2647353B1 (en) * 2007-07-23 2014-12-31 PowerVision, Inc. Lens delivery system
US8968396B2 (en) 2007-07-23 2015-03-03 Powervision, Inc. Intraocular lens delivery systems and methods of use
WO2009015226A2 (en) 2007-07-23 2009-01-29 Powervision, Inc. Accommodating intraocular lenses and methods of use
US8668734B2 (en) 2010-07-09 2014-03-11 Powervision, Inc. Intraocular lens delivery devices and methods of use
US8314927B2 (en) 2007-07-23 2012-11-20 Powervision, Inc. Systems and methods for testing intraocular lenses
EP2178462B1 (en) * 2007-07-23 2014-04-02 PowerVision, Inc. Post-implant lens power modification
US8414646B2 (en) 2007-12-27 2013-04-09 Forsight Labs, Llc Intraocular, accommodating lens and methods of use
US8167941B2 (en) 2008-01-03 2012-05-01 Forsight Labs, Llc Intraocular, accommodating lens and methods of use
US20090198326A1 (en) * 2008-01-31 2009-08-06 Medennium Inc. Accommodative intraocular lens system
US8425595B2 (en) 2008-03-12 2013-04-23 Visiogen, Inc. Method for inserting an intraocular lens
NZ592645A (en) 2008-11-20 2013-01-25 Insight Innovations Llc Biocompatible biodegradable intraocular implant system
US20120232649A1 (en) 2008-11-20 2012-09-13 Insight Innovations, Llc Intraocular Lens Cell Migration Inhibition System
US9943402B2 (en) 2008-11-20 2018-04-17 Insight Innovations, Llc Micropatterned intraocular implant
EP2358306B1 (en) * 2008-12-18 2013-10-23 Novartis AG Intraocular lens with extended depth of focus
US10299913B2 (en) 2009-01-09 2019-05-28 Powervision, Inc. Accommodating intraocular lenses and methods of use
EP2384167A4 (en) * 2009-01-09 2016-02-17 Powervision Inc Intraocular lenses and methods of accounting for capsule size variability and post-implant changes in the eye
US8447086B2 (en) 2009-08-31 2013-05-21 Powervision, Inc. Lens capsule size estimation
JP2013520291A (en) 2010-02-23 2013-06-06 パワーヴィジョン・インコーポレーテッド Liquid for accommodation type intraocular lens
CN102883681A (en) * 2010-03-04 2013-01-16 安伦科技股份有限公司 System for forming and modifying lenses and lenses formed thereby
US10736732B2 (en) 2010-06-21 2020-08-11 James Stuart Cumming Intraocular lens with longitudinally rigid plate haptic
US9585745B2 (en) 2010-06-21 2017-03-07 James Stuart Cumming Foldable intraocular lens with rigid haptics
US8734512B2 (en) 2011-05-17 2014-05-27 James Stuart Cumming Biased accommodating intraocular lens
US9918830B2 (en) 2010-06-21 2018-03-20 James Stuart Cumming Foldable intraocular lens with rigid haptics
US8523942B2 (en) 2011-05-17 2013-09-03 James Stuart Cumming Variable focus intraocular lens
US9295544B2 (en) 2012-06-05 2016-03-29 James Stuart Cumming Intraocular lens
US9295545B2 (en) 2012-06-05 2016-03-29 James Stuart Cumming Intraocular lens
US9351825B2 (en) 2013-12-30 2016-05-31 James Stuart Cumming Semi-flexible posteriorly vaulted acrylic intraocular lens for the treatment of presbyopia
US9295546B2 (en) 2013-09-24 2016-03-29 James Stuart Cumming Anterior capsule deflector ridge
WO2012129407A2 (en) 2011-03-24 2012-09-27 Powervision, Inc. Intraocular lens loading systems and methods of use
US10433949B2 (en) 2011-11-08 2019-10-08 Powervision, Inc. Accommodating intraocular lenses
CN103211665B (en) * 2012-01-19 2016-01-13 爱博诺德(北京)医疗科技有限公司 Posterior chamber intraocular lens
CN103211664B (en) * 2012-01-19 2015-06-24 爱博诺德(北京)医疗科技有限公司 Posterior chamber type artificial crystal
US8900300B1 (en) 2012-02-22 2014-12-02 Omega Ophthalmics Llc Prosthetic capsular bag and method of inserting the same
US10258462B2 (en) * 2012-12-26 2019-04-16 Rainbow Medical Ltd. Accommodative intraocular lens
US9925039B2 (en) 2012-12-26 2018-03-27 Rainbow Medical Ltd. Accommodative intraocular lens
EP3785668A1 (en) 2013-03-15 2021-03-03 Alcon Inc. Intraocular lens storage and loading devices and methods of use
US9615916B2 (en) 2013-12-30 2017-04-11 James Stuart Cumming Intraocular lens
CA2952809C (en) 2014-06-19 2019-11-26 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods
US9358103B1 (en) 2015-02-10 2016-06-07 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods
WO2017079733A1 (en) 2015-11-06 2017-05-11 Powervision, Inc. Accommodating intraocular lenses and methods of manufacturing
US10327886B2 (en) 2016-06-01 2019-06-25 Rainbow Medical Ltd. Accomodative intraocular lens
CA3026494C (en) 2016-06-06 2022-06-07 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods
EP3954326A1 (en) 2016-10-21 2022-02-16 Omega Ophthalmics LLC Prosthetic capsular device
US10441411B2 (en) 2016-12-29 2019-10-15 Rainbow Medical Ltd. Accommodative intraocular lens
AU2019249216A1 (en) 2018-04-06 2020-10-01 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods
AU2020357870A1 (en) 2019-10-04 2022-04-28 Alcon Inc. Adjustable intraocular lenses and methods of post-operatively adjusting intraocular lenses
WO2022082170A1 (en) 2020-10-12 2022-04-21 Omega Ophthalmics Llc Prosthetic capsular devices, systems, and methods

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0337390B1 (en) * 1988-04-11 1993-02-17 Ceskoslovenska Akademie Ved Intraocular optical system
FR2681524A1 (en) * 1991-09-25 1993-03-26 Mnao CRYSTALLINE IMPLANT.
US5275623A (en) * 1991-11-18 1994-01-04 Faezeh Sarfarazi Elliptical accommodative intraocular lens for small incision surgery
WO2000061036A1 (en) * 1999-04-09 2000-10-19 Faezeh Mona Sarfarazi Open chamber, elliptical, accommodative intraocular lens system
WO2001019289A1 (en) * 1999-09-17 2001-03-22 Allergan Sales, Inc. Intraocular lens with a translational zone
US6217612B1 (en) * 1999-09-10 2001-04-17 Randall Woods Intraocular lens implant having eye accommodating capabilities

Family Cites Families (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4950290A (en) * 1989-02-09 1990-08-21 William Kamerling Posterior chamber intraocular lens
US5476514A (en) * 1990-04-27 1995-12-19 Cumming; J. Stuart Accommodating intraocular lens
US6197059B1 (en) * 1990-04-27 2001-03-06 Medevec Licensing, B.V. Accomodating intraocular lens
US5152787A (en) * 1990-12-19 1992-10-06 Eastman Kodak Company Intraocular gradient-index lenses used in eye implantation
US5326347A (en) * 1991-08-12 1994-07-05 Cumming J Stuart Intraocular implants
US6013101A (en) * 1994-11-21 2000-01-11 Acuity (Israel) Limited Accommodating intraocular lens implant
US5685894A (en) * 1995-09-13 1997-11-11 Electrolux Corporation Filter and accessory mount for upright vacuum cleaner exhaust port
WO1997026842A1 (en) * 1996-01-26 1997-07-31 Vision Pharmaceuticals L.P. Primary and supplemental intraocular lens system
IL121417A0 (en) * 1997-07-28 1998-01-04 Israel Henry M Intraocular ring
US6231603B1 (en) * 1998-11-10 2001-05-15 Allergan Sales, Inc. Accommodating multifocal intraocular lens
US6176878B1 (en) * 1998-12-17 2001-01-23 Allergan Sales, Inc. Accommodating intraocular lens
US6506212B2 (en) * 2000-07-07 2003-01-14 Medennium, Inc. Anatomically compatible posterior chamber phakic refractive lenses
US6558420B2 (en) * 2000-12-12 2003-05-06 Bausch & Lomb Incorporated Durable flexible attachment components for accommodating intraocular lens
US6786934B2 (en) * 2001-01-25 2004-09-07 Visiogen, Inc. Biasing element for intraocular lens system

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0337390B1 (en) * 1988-04-11 1993-02-17 Ceskoslovenska Akademie Ved Intraocular optical system
FR2681524A1 (en) * 1991-09-25 1993-03-26 Mnao CRYSTALLINE IMPLANT.
US5275623A (en) * 1991-11-18 1994-01-04 Faezeh Sarfarazi Elliptical accommodative intraocular lens for small incision surgery
WO2000061036A1 (en) * 1999-04-09 2000-10-19 Faezeh Mona Sarfarazi Open chamber, elliptical, accommodative intraocular lens system
US6217612B1 (en) * 1999-09-10 2001-04-17 Randall Woods Intraocular lens implant having eye accommodating capabilities
WO2001019289A1 (en) * 1999-09-17 2001-03-22 Allergan Sales, Inc. Intraocular lens with a translational zone

Cited By (26)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9814570B2 (en) 1999-04-30 2017-11-14 Abbott Medical Optics Inc. Ophthalmic lens combinations
US8486140B2 (en) 2001-01-30 2013-07-16 Timothy R. Willis Refractive intraocular implant lens and method
US8551164B2 (en) 2001-01-30 2013-10-08 Timothy R. Willis Refractive intraocular implant lens and method
US9504560B2 (en) 2002-01-14 2016-11-29 Abbott Medical Optics Inc. Accommodating intraocular lens with outer support structure
US10206773B2 (en) 2002-12-05 2019-02-19 Johnson & Johnson Surgical Vision, Inc. Accommodating intraocular lens and method of manufacture thereof
US9271830B2 (en) 2002-12-05 2016-03-01 Abbott Medical Optics Inc. Accommodating intraocular lens and method of manufacture thereof
WO2004106045A1 (en) * 2003-05-27 2004-12-09 Faezeh Mona Sarfarazi Mold for intraocular lens
US9198752B2 (en) 2003-12-15 2015-12-01 Abbott Medical Optics Inc. Intraocular lens implant having posterior bendable optic
US7780729B2 (en) 2004-04-16 2010-08-24 Visiogen, Inc. Intraocular lens
US8579970B1 (en) 2005-06-27 2013-11-12 Visiogen, Inc. Magnifying intraocular lens
US9636213B2 (en) 2005-09-30 2017-05-02 Abbott Medical Optics Inc. Deformable intraocular lenses and lens systems
US8496701B2 (en) 2006-12-22 2013-07-30 Amo Groningen B.V. Accommodating intraocular lenses and associated systems, frames, and methods
US8182531B2 (en) 2006-12-22 2012-05-22 Amo Groningen B.V. Accommodating intraocular lenses and associated systems, frames, and methods
WO2008079671A1 (en) * 2006-12-22 2008-07-03 Bausch & Lomb Incorporated Multi-element accommodative intraocular lens
US8613766B2 (en) 2006-12-22 2013-12-24 Bausch-Lomb Incorporated Multi-element accommodative intraocular lens
US9039760B2 (en) 2006-12-29 2015-05-26 Abbott Medical Optics Inc. Pre-stressed haptic for accommodating intraocular lens
US9968441B2 (en) 2008-03-28 2018-05-15 Johnson & Johnson Surgical Vision, Inc. Intraocular lens having a haptic that includes a cap
US9011532B2 (en) 2009-06-26 2015-04-21 Abbott Medical Optics Inc. Accommodating intraocular lenses
US10052194B2 (en) 2009-06-26 2018-08-21 Johnson & Johnson Surgical Vision, Inc. Accommodating intraocular lenses
US10105215B2 (en) 2009-08-03 2018-10-23 Johnson & Johnson Surgical Vision, Inc. Intraocular lens and methods for providing accommodative vision
US9603703B2 (en) 2009-08-03 2017-03-28 Abbott Medical Optics Inc. Intraocular lens and methods for providing accommodative vision
US9855136B2 (en) 2012-01-19 2018-01-02 Eyebright Medical Technology (Beijing) Co., Ltd. Posterior chamber intraocular lens
EP2805694A4 (en) * 2012-01-19 2015-09-30 Eyebright Medical Technology Beijing Co Ltd Posterior chamber-type intraocular lens
US9987125B2 (en) 2012-05-02 2018-06-05 Johnson & Johnson Surgical Vision, Inc. Intraocular lens with shape changing capability to provide enhanced accomodation and visual acuity
US10695166B2 (en) 2015-08-14 2020-06-30 Timothy R. Willis Intraocular lenses (IOLs) and related assemblies and intraocular attachment methods
US11707354B2 (en) 2017-09-11 2023-07-25 Amo Groningen B.V. Methods and apparatuses to increase intraocular lenses positional stability

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