CA2401972C - Accommodating intraocular lens - Google Patents
Accommodating intraocular lens Download PDFInfo
- Publication number
- CA2401972C CA2401972C CA002401972A CA2401972A CA2401972C CA 2401972 C CA2401972 C CA 2401972C CA 002401972 A CA002401972 A CA 002401972A CA 2401972 A CA2401972 A CA 2401972A CA 2401972 C CA2401972 C CA 2401972C
- Authority
- CA
- Canada
- Prior art keywords
- optic
- intraocular lens
- movement
- region
- enlarged distal
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Classifications
-
- 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
- A61F2/1616—Pseudo-accommodative, e.g. multifocal or enabling monovision
-
- 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
- A61F2/1629—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 longitudinal position, i.e. along the visual axis when implanted
-
- 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
- A61F2/1694—Capsular bag spreaders therefor
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
- B29D—PRODUCING PARTICULAR ARTICLES FROM PLASTICS OR FROM SUBSTANCES IN A PLASTIC STATE
- B29D11/00—Producing optical elements, e.g. lenses or prisms
- B29D11/02—Artificial eyes from organic plastic material
- B29D11/023—Implants for natural eyes
- B29D11/026—Comprising more than one lens
-
- 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
- A61F2/1648—Multipart lenses
-
- 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
- A61F2002/1681—Intraocular lenses having supporting structure for lens, e.g. haptics
Abstract
An intraocular lens includes an optic (12) for focusing light and a movement assembly (14) coupled to the optic. The movement assembly is adapted to cooperate with the eye to effect accommodating movement of the optic. The movement assembly includes a plurality of movement members (16) each with a proximal region (18) coupled to the optic and an enlarged distal region (20). The enlarged distal region may be integral with the proximal region, or may be mechanically coupled thereto.
Description
2 PCT/US01/07062 ACCOMMODATING INTRAOCULAR LENS
Background of the Invention The present invention relates to intraocular lenses (IOLs). More particularly, the present invention relates to IOLs which are adapted to provide accommodating movement in the eye.
The human visual system includes the eyes, the extraocular muscles which control eye position within the eye socket, the optic and other nerves that connect the eyes to the brain, and particular areas of the brain that 1o are in neural communication with the eyes. The visual system is particularly well adapted for the rapid and precise extraction of spatial information from a field of view which is accomplished by analyzing the continuously changing patterns of radiant flux impinging upon the surfaces of the eyes.
Image formation is greatly complicated by the movement of the eyes within the head, as well as by the movement of both eyes and the head relative to the external sea of radiant energy. Visual input is ordinarily sampled by discrete momentary pauses of the eyes called fixations, interrupted by very rapid ballistic motions known as saccades which bring the eye from one fixation position to the next. Smooth movements of the eyes can occur when an object having a predictable motion is available to be followed.
Each eye forms an image upon a vast array of light sensitive photoreceptors of the retina. The cornea is the primary refracting surface which admits light through the anterior part of the outer surface of the eye. The iris contains muscles which alter the size of the entrance port of the eye, or pupil. The crystalline lens has a variable shape, under the indirect control of the ciliary muscle.
Having a refractive index higher than the surrounding media, the crystalline lens gives the eye a variable focal length, allowing accommodation to objects at varying distances from the eye.
Much of the remainder of the eye is filled with fluids and materials under pressure which help the eye maintain its shape. For example, the aqueous humor fills the anterior chamber between the cornea and the iris, and the vitreous humor fills the majority of the volume of the eye in the vitreous chamber. The crystalline lens is contained within a third chamber of the eye, the posterior chamber, which is positioned between the anterior and vitreous chambers.
The human eye is susceptible to a score or more of disorders and diseases, a number of which attack the crystalline lens. For example, cataracts mar vision through cloudy or opaque discoloration of the lens of the eye. Cataracts often result in partial or complete blindness. If this is the case, the crystalline lens can be removed and replace with an intraocular lens, or IOL.
While restoring vision, conventional IOLs have limited ability for accommodation (i.e., the focusing on near objects). This condition is known as presbyopia. To overcome presbyopia of an IOL, a patient may be prescribed eyeglasses. Alternative attempts in the art to overcome presbyopia focus on providing IOLs with accommodation ability. Accommodation may be accomplished by either changing the shape of the IOL, e.g., to become more convex to focus on near objects, or by moving the IOL along its optical axis. For example, a number of these approaches bias an IOL to be located in the most posterior position of the posterior chamber of the eye under rest conditions.
When near focus is required, the ciliary muscle contracts, and the IOL moves forwardly, which is known as positive accommodation. In the absence of ciliary muscle contraction, the IOL is biased rearwardly to the most
Background of the Invention The present invention relates to intraocular lenses (IOLs). More particularly, the present invention relates to IOLs which are adapted to provide accommodating movement in the eye.
The human visual system includes the eyes, the extraocular muscles which control eye position within the eye socket, the optic and other nerves that connect the eyes to the brain, and particular areas of the brain that 1o are in neural communication with the eyes. The visual system is particularly well adapted for the rapid and precise extraction of spatial information from a field of view which is accomplished by analyzing the continuously changing patterns of radiant flux impinging upon the surfaces of the eyes.
Image formation is greatly complicated by the movement of the eyes within the head, as well as by the movement of both eyes and the head relative to the external sea of radiant energy. Visual input is ordinarily sampled by discrete momentary pauses of the eyes called fixations, interrupted by very rapid ballistic motions known as saccades which bring the eye from one fixation position to the next. Smooth movements of the eyes can occur when an object having a predictable motion is available to be followed.
Each eye forms an image upon a vast array of light sensitive photoreceptors of the retina. The cornea is the primary refracting surface which admits light through the anterior part of the outer surface of the eye. The iris contains muscles which alter the size of the entrance port of the eye, or pupil. The crystalline lens has a variable shape, under the indirect control of the ciliary muscle.
Having a refractive index higher than the surrounding media, the crystalline lens gives the eye a variable focal length, allowing accommodation to objects at varying distances from the eye.
Much of the remainder of the eye is filled with fluids and materials under pressure which help the eye maintain its shape. For example, the aqueous humor fills the anterior chamber between the cornea and the iris, and the vitreous humor fills the majority of the volume of the eye in the vitreous chamber. The crystalline lens is contained within a third chamber of the eye, the posterior chamber, which is positioned between the anterior and vitreous chambers.
The human eye is susceptible to a score or more of disorders and diseases, a number of which attack the crystalline lens. For example, cataracts mar vision through cloudy or opaque discoloration of the lens of the eye. Cataracts often result in partial or complete blindness. If this is the case, the crystalline lens can be removed and replace with an intraocular lens, or IOL.
While restoring vision, conventional IOLs have limited ability for accommodation (i.e., the focusing on near objects). This condition is known as presbyopia. To overcome presbyopia of an IOL, a patient may be prescribed eyeglasses. Alternative attempts in the art to overcome presbyopia focus on providing IOLs with accommodation ability. Accommodation may be accomplished by either changing the shape of the IOL, e.g., to become more convex to focus on near objects, or by moving the IOL along its optical axis. For example, a number of these approaches bias an IOL to be located in the most posterior position of the posterior chamber of the eye under rest conditions.
When near focus is required, the ciliary muscle contracts, and the IOL moves forwardly, which is known as positive accommodation. In the absence of ciliary muscle contraction, the IOL is biased rearwardly to the most
3 posterior position. While these approaches may provide limited accommodation, the posterior bias and the configuration of the IOL prevent sufficient forward axial movement required for full-range accommodation.
In view of the foregoing, it would be beneficial in the art to provide IOLs adapted for sufficient accommodation to reduce significantly or to overcome the effects of presbyopia.
Summarv of the Invention New intraocular lenses (IOLs) effective to provide accommodation have been discovered. The present IOLs provide effective accommodation using one or more optics.
The IOLs of the invention also inhibit cell growth, particularly epithelial cell growth, onto the optics of the IOLs. The IOLs of the present invention are configured, and preferably promote cellular and fibrous growth to desired regions of the IOL, to increase the amount of force exerted by the eye against the IOLs to increase the amount of accommodation achieved. The present IOLs are relatively straightforward in design, can be produced using conventional IOL manufacturing procedures and can be inserted or implanted in eyes, e.g., human eyes, using surgical techniques which are the same as or analogous to such techniques used with conventional IOLs.
According to one aspect of the invention, an intraocular lens is provided which includes an optic for focusing light on a retina and a movement assembly coupled to the optic. The movement assembly is adapted to cooperate with the eye to effect accommodating movement of the optic. The movement assembly includes a movement member with a proximal region coupled to the optic. The movement member, and in particular the proximal region of the movement member, extends radially outwardly from the
In view of the foregoing, it would be beneficial in the art to provide IOLs adapted for sufficient accommodation to reduce significantly or to overcome the effects of presbyopia.
Summarv of the Invention New intraocular lenses (IOLs) effective to provide accommodation have been discovered. The present IOLs provide effective accommodation using one or more optics.
The IOLs of the invention also inhibit cell growth, particularly epithelial cell growth, onto the optics of the IOLs. The IOLs of the present invention are configured, and preferably promote cellular and fibrous growth to desired regions of the IOL, to increase the amount of force exerted by the eye against the IOLs to increase the amount of accommodation achieved. The present IOLs are relatively straightforward in design, can be produced using conventional IOL manufacturing procedures and can be inserted or implanted in eyes, e.g., human eyes, using surgical techniques which are the same as or analogous to such techniques used with conventional IOLs.
According to one aspect of the invention, an intraocular lens is provided which includes an optic for focusing light on a retina and a movement assembly coupled to the optic. The movement assembly is adapted to cooperate with the eye to effect accommodating movement of the optic. The movement assembly includes a movement member with a proximal region coupled to the optic. The movement member, and in particular the proximal region of the movement member, extends radially outwardly from the
4 optic and includes an enlarged distal region with a contact surface adapted to be in contact with a peripheral region of a capsular bag of an eye.
One of the advantages of the present invention is that the IOL is held within, preferably attached to, the capsular bag. More specifically, the contact surface of the enlarged distal region may have an axial length of at least about 1 mm. Therefore, depending upon the radius of the IOL, the contact surface has a relatively large surface area with which to contact the capsular bag.
The contact of the IOL with the capsular bag is further enhanced by disposing the enlarged distal region in an angled manner relative to the proximal region of the member. Preferably, the contact surface is substantially parallel to the optical axis of the IOL. The relatively large contact surface is effective in maintaining the position of the IOL particularly directly following implantation and, on a long term basis, is effective in increasing the amount of accommodation provided by the IOL.
The relatively large surface area of the contact surface also promotes cellular and fibrous growth to or onto this region of the IOL, which further holds and retains the IOL within the capsular bag and increases the amount of force that may be exerted through the capsular bag onto the IOL to provide accommodation, as desired.
Post-operative cellular and fibrous growth of the interior of the capsular bag to the enlarged distal region of the movement assembly may, and preferably does, enable the IOLs of the present invention to function substantially analogous to a natural crystalline lens.
To further facilitate this post-operative cellular growth, the enlarged distal region may include a plurality of depressions or through holes. Each of the through holes preferably provides increased growth of cells and fibrin onto the enlarged distal region or regions of the IOL.
Accordingly, the IOL is very effectively attachable, preferably substantially permanently attachable, to the capsular bag. This attachment of the IOL to the capsular bag facilitates the axial movement of the IOL in direct
One of the advantages of the present invention is that the IOL is held within, preferably attached to, the capsular bag. More specifically, the contact surface of the enlarged distal region may have an axial length of at least about 1 mm. Therefore, depending upon the radius of the IOL, the contact surface has a relatively large surface area with which to contact the capsular bag.
The contact of the IOL with the capsular bag is further enhanced by disposing the enlarged distal region in an angled manner relative to the proximal region of the member. Preferably, the contact surface is substantially parallel to the optical axis of the IOL. The relatively large contact surface is effective in maintaining the position of the IOL particularly directly following implantation and, on a long term basis, is effective in increasing the amount of accommodation provided by the IOL.
The relatively large surface area of the contact surface also promotes cellular and fibrous growth to or onto this region of the IOL, which further holds and retains the IOL within the capsular bag and increases the amount of force that may be exerted through the capsular bag onto the IOL to provide accommodation, as desired.
Post-operative cellular and fibrous growth of the interior of the capsular bag to the enlarged distal region of the movement assembly may, and preferably does, enable the IOLs of the present invention to function substantially analogous to a natural crystalline lens.
To further facilitate this post-operative cellular growth, the enlarged distal region may include a plurality of depressions or through holes. Each of the through holes preferably provides increased growth of cells and fibrin onto the enlarged distal region or regions of the IOL.
Accordingly, the IOL is very effectively attachable, preferably substantially permanently attachable, to the capsular bag. This attachment of the IOL to the capsular bag facilitates the axial movement of the IOL in direct
5 response to changes in the capsular bag, therefore providing effective accommodation, analogous to a natural crystalline lens.
The IOLs of the present invention preferably inhibit unwanted posterior capsule opacification (PCO) of the optic. Thus, the distal region or regions of the movement assembly preferably is or are joined to the proximal region or regions so that one or more sharp edges, that is preferably edges which occur at discontinuities (rather than at smooth, continuous transitions) when viewed by the 1s naked human eye, are present between the joined proximal and distal regions. Such sharp edges have been found to advantageously inhibit PCO by inhibiting the growth of cells, for example, epithelial cells, from the capsular bag onto the optic of the present IOLs.
To further enhance the accommodating movement of the present IOLs in cooperation with the eye, the movement assembly preferably is positioned relative to the optic so that, with the IOL at rest, that is with no forces acting on the IOL to effect accommodation, the proximal region of the movement member is positioned at an angle other than 900 relative to the central optical axis of the optic. In a very useful embodiment, the optic, in the rest position as noted. above, is anteriorly vaulted. Also, the movement member or members preferably include a hinge, or a plurality of hinges, located on the proximal region or regions of the movement members, more preferably closer to the optic than to the distal region or regions. Each of these features, either individually or any combination thereof, is effective to further facilitate the movement of the optic to provide the desired amount of accommodation.
The IOLs of the present invention preferably inhibit unwanted posterior capsule opacification (PCO) of the optic. Thus, the distal region or regions of the movement assembly preferably is or are joined to the proximal region or regions so that one or more sharp edges, that is preferably edges which occur at discontinuities (rather than at smooth, continuous transitions) when viewed by the 1s naked human eye, are present between the joined proximal and distal regions. Such sharp edges have been found to advantageously inhibit PCO by inhibiting the growth of cells, for example, epithelial cells, from the capsular bag onto the optic of the present IOLs.
To further enhance the accommodating movement of the present IOLs in cooperation with the eye, the movement assembly preferably is positioned relative to the optic so that, with the IOL at rest, that is with no forces acting on the IOL to effect accommodation, the proximal region of the movement member is positioned at an angle other than 900 relative to the central optical axis of the optic. In a very useful embodiment, the optic, in the rest position as noted. above, is anteriorly vaulted. Also, the movement member or members preferably include a hinge, or a plurality of hinges, located on the proximal region or regions of the movement members, more preferably closer to the optic than to the distal region or regions. Each of these features, either individually or any combination thereof, is effective to further facilitate the movement of the optic to provide the desired amount of accommodation.
6 According to another aspect of the invention, the movement assembly includes a plurality of movement members, preferably spaced apart, for example, radially or circumferentially spaced apart, from each other. Each movement member includes a proximal region coupled to the optic and an enlarged distal region, for example, as described elsewhere herein. The enlarged distal regions each have a contact surface adapted to be in contact with a peripheral region of a capsular bag of an eye. In addition, the enlarged distal regions may be configured such that the contact surfaces are substantially coaxial with the optical axis of the optic.
A plurality of spacer or cut-out regions preferably are located between radially or circumferentially adjacent movement members. Such cut-out regions are effective to prevent buckling of the IOL during accommodating movement in the eye. Such spacers or cut-out regions may be open.
In one useful embodiment each of such regions is at least partially covered with or by a structural material having increased flexibility relative to the movement members.
Thus, the IOL is prevented from buckling while, at the same time the structural material is effective to at least inhibit cell growth from the capsular bag onto the optic.
This structural material may have the same chemical make-up as the proximal regions of the movement members and have a reduced thickness relative to the proximal regions to provide the increased flexibility.
Another advantage of the present IOLs is that a second optic may be provided. According to this multi-optic embodiment, the secondary optic may be coupled to the enlarged distal region or regions with one or more secondary movement members.
In one useful embodiment, the enlarged distal region or regions of the movement member or members are provided with a groove or grooves. The secondary movement member or
A plurality of spacer or cut-out regions preferably are located between radially or circumferentially adjacent movement members. Such cut-out regions are effective to prevent buckling of the IOL during accommodating movement in the eye. Such spacers or cut-out regions may be open.
In one useful embodiment each of such regions is at least partially covered with or by a structural material having increased flexibility relative to the movement members.
Thus, the IOL is prevented from buckling while, at the same time the structural material is effective to at least inhibit cell growth from the capsular bag onto the optic.
This structural material may have the same chemical make-up as the proximal regions of the movement members and have a reduced thickness relative to the proximal regions to provide the increased flexibility.
Another advantage of the present IOLs is that a second optic may be provided. According to this multi-optic embodiment, the secondary optic may be coupled to the enlarged distal region or regions with one or more secondary movement members.
In one useful embodiment, the enlarged distal region or regions of the movement member or members are provided with a groove or grooves. The secondary movement member or
7 members are adapted to fit into the groove or grooves, thereby holding the second optic in position in the eye.
Alternately, the second optic and secondary movement members may be formed integrally with the optic/movement assembly combination.
In a further useful embodiment of present invention, the enlarged distal region or regions of the movement member or members are mechanically coupled to the perspective proximal regions. In one particular embodiment, an intraocular lens comprises a plurality of arcuate segments mechanically coupled (e.g., adhered) to an integrally formed optic and radially outward movement members. The arcuate segments may have one or more grooves for receiving one or more movement members, thus forming either a one-optic or a two-optic system.
The second optic preferably has an optical power, or even substantially no optical power. The combination of the optic and second optic together preferably provides the optical power required or desired by the patient in whose eye the IOL is to be implanted. For example, the second optic can have a plano or substantially plano optical power or a relatively highly negative optical power, for example, between about -30 diopters to about -10 diopters, as desired. The second optic preferably is located posterior of the optic. In one useful embodiment, the second optic, in the eye, is substantially maintained in contact with the inner posterior wall of the capsular bag. This feature inhibits or reduces the risk of cell growth or migration from the capsular bag into the second optic. The second optic in such a posterior position often has only a relatively restricted, if any, amount of axial movement.
Such a posterior second optic preferably is posteriorly vaulted, with the IOL in the rest position as described elsewhere herein, to facilitate maintaining the posterior face of the second optic in contact with the inner
Alternately, the second optic and secondary movement members may be formed integrally with the optic/movement assembly combination.
In a further useful embodiment of present invention, the enlarged distal region or regions of the movement member or members are mechanically coupled to the perspective proximal regions. In one particular embodiment, an intraocular lens comprises a plurality of arcuate segments mechanically coupled (e.g., adhered) to an integrally formed optic and radially outward movement members. The arcuate segments may have one or more grooves for receiving one or more movement members, thus forming either a one-optic or a two-optic system.
The second optic preferably has an optical power, or even substantially no optical power. The combination of the optic and second optic together preferably provides the optical power required or desired by the patient in whose eye the IOL is to be implanted. For example, the second optic can have a plano or substantially plano optical power or a relatively highly negative optical power, for example, between about -30 diopters to about -10 diopters, as desired. The second optic preferably is located posterior of the optic. In one useful embodiment, the second optic, in the eye, is substantially maintained in contact with the inner posterior wall of the capsular bag. This feature inhibits or reduces the risk of cell growth or migration from the capsular bag into the second optic. The second optic in such a posterior position often has only a relatively restricted, if any, amount of axial movement.
Such a posterior second optic preferably is posteriorly vaulted, with the IOL in the rest position as described elsewhere herein, to facilitate maintaining the posterior face of the second optic in contact with the inner
8 posterior face of the capsular bag.
Any and all of the features described herein and combinations of such features are included within the scope of the present invention provided that the features of any such combination are not mutually inconsistent.
Additional aspects, features, and advantages of the present invention are set forth in the following description and claims, particularly when considered in conjunction with the accompanying drawings in which like parts bear like reference numbers.
Brief Description of the Drawincis Fig. 1 is a perspective of an intraocular lens (IOL) according to an exemplary embodiment of the present invention, particularly illustrating an anterior side of i5 the IOL.
Fig. 2 is a fragmentary cross-sectional view of an eye in which an IOL configured in accordance with the present invention has been implanted.
Fig. 3 is a plan view of an intraocular lens (IOL) of the invention, particularly illustrating a posterior side of the IOL.
Fig. 4 is a plan view of an alternate embodiment of an intraocular lens (IOL) of the invention, illustrating the use of flexible structural material between movement members.
Fig. 5 is an enlarged view of a two-lens system and a circumferential groove for receiving and retaining a posterior lens.
Fig. 6 is a plan view of and alternative embodiment of an intraocular lens (IOL) of the invention constructed of mechanically coupled lens and peripheral regions.
Fig. 7A is a plan view of one segment of a peripheral region of the IOL of Fig. 6.
Any and all of the features described herein and combinations of such features are included within the scope of the present invention provided that the features of any such combination are not mutually inconsistent.
Additional aspects, features, and advantages of the present invention are set forth in the following description and claims, particularly when considered in conjunction with the accompanying drawings in which like parts bear like reference numbers.
Brief Description of the Drawincis Fig. 1 is a perspective of an intraocular lens (IOL) according to an exemplary embodiment of the present invention, particularly illustrating an anterior side of i5 the IOL.
Fig. 2 is a fragmentary cross-sectional view of an eye in which an IOL configured in accordance with the present invention has been implanted.
Fig. 3 is a plan view of an intraocular lens (IOL) of the invention, particularly illustrating a posterior side of the IOL.
Fig. 4 is a plan view of an alternate embodiment of an intraocular lens (IOL) of the invention, illustrating the use of flexible structural material between movement members.
Fig. 5 is an enlarged view of a two-lens system and a circumferential groove for receiving and retaining a posterior lens.
Fig. 6 is a plan view of and alternative embodiment of an intraocular lens (IOL) of the invention constructed of mechanically coupled lens and peripheral regions.
Fig. 7A is a plan view of one segment of a peripheral region of the IOL of Fig. 6.
9 Fig. 7B is an elevational view of the peripheral region segment of Fig. 7A.
Fig. 7C is an enlarged view of a portion of Fig. 7B.
Fig. 8 is a perspective view of a ring formed during the process of making the peripheral region of the IOL of Fig. 6.
Detailed Description of the Drawinqs Referring to the drawings in more detail, an intraocular lens (IOL) 10 according to an exemplary embodiment of the present invention is illustrated in Fig.
1. Exemplary IOL 10 includes an optic 12 and a movement assembly 14 coupled to the optic 12. The optic 12, which has an optical axis 0, is adapted to focus light on a retina of an eye. The movement assembly 14 of exemplary IOL 10 is adapted to cooperate with an eye to effect accommodating movement of the optic 12, which is discussed in detail below.
Exemplary movement assembly 14 includes a member 16 with a proximal region 18 and an enlarged distal region 20.
The terms "proximal" and "distal" are used herein with respect to the distance from the optical axis O. The proximal region 18 is coupled to the optic 12 at a periphery 22 of the optic. The member 16 extends radially outwardly from the optic 12 and the proximal region 18 to the enlarged distal region 20. With additional reference to Fig. 2, the enlarged distal region 20 has a contact surface 24 which is adapted to be in contact with a peripheral region 26 of a capsular bag 28 of an eye 30.
Briefly describing the anatomy of the eye 30 with reference to Fig. 2, the capsular bag 28 is connected to a ciliary muscle 32 by suspensory ligaments or zonules 34.
The ciliary muscle 32 is the prime mover in accommodation, i.e., in adjusting the eye 30 to focus on near objects.
The zonules 34 retain the lens in position and are relaxed by the contraction of the ciliary muscle 32, thereby allowing a natural crystalline lens to become more convex.
Applying this anatomy to the present invention, 5 exemplary IOL 10 is configured to facilitate movement of the optic 12 in response to the action of the ciliary muscle 32 and the zonules 34. When near vision is needed, the ciliary muscle 32 contracts, and the zonules 34 relax and reduce the equatorial diameter of the capsular bag 28,
Fig. 7C is an enlarged view of a portion of Fig. 7B.
Fig. 8 is a perspective view of a ring formed during the process of making the peripheral region of the IOL of Fig. 6.
Detailed Description of the Drawinqs Referring to the drawings in more detail, an intraocular lens (IOL) 10 according to an exemplary embodiment of the present invention is illustrated in Fig.
1. Exemplary IOL 10 includes an optic 12 and a movement assembly 14 coupled to the optic 12. The optic 12, which has an optical axis 0, is adapted to focus light on a retina of an eye. The movement assembly 14 of exemplary IOL 10 is adapted to cooperate with an eye to effect accommodating movement of the optic 12, which is discussed in detail below.
Exemplary movement assembly 14 includes a member 16 with a proximal region 18 and an enlarged distal region 20.
The terms "proximal" and "distal" are used herein with respect to the distance from the optical axis O. The proximal region 18 is coupled to the optic 12 at a periphery 22 of the optic. The member 16 extends radially outwardly from the optic 12 and the proximal region 18 to the enlarged distal region 20. With additional reference to Fig. 2, the enlarged distal region 20 has a contact surface 24 which is adapted to be in contact with a peripheral region 26 of a capsular bag 28 of an eye 30.
Briefly describing the anatomy of the eye 30 with reference to Fig. 2, the capsular bag 28 is connected to a ciliary muscle 32 by suspensory ligaments or zonules 34.
The ciliary muscle 32 is the prime mover in accommodation, i.e., in adjusting the eye 30 to focus on near objects.
The zonules 34 retain the lens in position and are relaxed by the contraction of the ciliary muscle 32, thereby allowing a natural crystalline lens to become more convex.
Applying this anatomy to the present invention, 5 exemplary IOL 10 is configured to facilitate movement of the optic 12 in response to the action of the ciliary muscle 32 and the zonules 34. When near vision is needed, the ciliary muscle 32 contracts, and the zonules 34 relax and reduce the equatorial diameter of the capsular bag 28,
10 thereby moving the optic 12 anteriorly as indicated by arrow A in Fig. 2. This anterior movement of the optic 12 increases or amplifies the amount of positive (i.e., near) accommodation of the optic 12. Conversely, when the ciliary muscle 32 relaxes, the zonules 34 constrict and increase the equatorial diameter of the capsular bag 28, thus moving the optic posteriorly as indicated by arrow P.
For human implantation, exemplary IOL 10 may be configured such that the amount of positive or near accommodation is preferably at least about 1 diopter and may range up to 3.5 diopters or more. Further, exemplary IOL 10 may be configured to provide at least about 1.5 mm or 2 mm of axial movement anteriorly in the eye with about a reduction of about 1 mm in the equatorial diameter of the capsular bag 28 caused by the ciliary muscle 32 and the zonules 34.
As mentioned, the enlarged distal region 20 of the movement assembly 14 is adapted to be in contact with the peripheral region 26 of the capsular bag 28. In accordance with the invention, the contact surface 24 of the enlarged distal region 20 has a relatively large surface area. In other words, it is preferable to maximize the surface area of the contact surface 24 while maintaining the ability of the IOL 10 to be received within the capsular bag 28. By maximizing the surface area with which the IOL 10 contacts the capsular bag 28, the IOL 10 of the present invention
For human implantation, exemplary IOL 10 may be configured such that the amount of positive or near accommodation is preferably at least about 1 diopter and may range up to 3.5 diopters or more. Further, exemplary IOL 10 may be configured to provide at least about 1.5 mm or 2 mm of axial movement anteriorly in the eye with about a reduction of about 1 mm in the equatorial diameter of the capsular bag 28 caused by the ciliary muscle 32 and the zonules 34.
As mentioned, the enlarged distal region 20 of the movement assembly 14 is adapted to be in contact with the peripheral region 26 of the capsular bag 28. In accordance with the invention, the contact surface 24 of the enlarged distal region 20 has a relatively large surface area. In other words, it is preferable to maximize the surface area of the contact surface 24 while maintaining the ability of the IOL 10 to be received within the capsular bag 28. By maximizing the surface area with which the IOL 10 contacts the capsular bag 28, the IOL 10 of the present invention
11 effectively responds to changes in force exerted by the capsular bag 26 on the lens 10, thereby maximizing axial movement of the optic 12. In addition to the advantage of maximizing axial movement, the contact surface 24 of the enlarged distal region 20 also provides a large surface area to be subject to cellular and fibrous growth, which will be discussed in more detail below.
According to the exemplary embodiment of the invention shown in Fig. 1, the enlarged distal region 20 may be described as a plurality of peripheral arcuate bands with the contact surface 24 comprising the distal surface of each band. Each of the arcuate bands of the enlarged distal region 20 extends axially and has a length 1, which will be discussed in more detail below. Each of the enlarged distal regions 20 may extend axially in a substantially parallel relationship with the optical axis O or, alternatively, may be arcuate in the axial direction such that the length 1 is an arc length X (both symbols illustrated in Fig. 1 on one of the contact surfaces 24).
Regarding exemplary IOL 10 in more detail, the movement assembly 14 may include a plurality of cut-out regions 36 (e.g., four), thereby defining a corresponding plurality of spokes or haptic members 38. Each of the haptic members 38 includes a respective portion of the enlarged distal region 20 of the member 16 of the assembly 14. The cut-out regions 36 provide spatial relief when the ciliary muscle 32 contracts, thereby preventing buckling of the optic 12 during accommodation. To prevent posterior capsule opacification (PCO), each of the cut-out regions 36 may be filled with the same material from which the optic
According to the exemplary embodiment of the invention shown in Fig. 1, the enlarged distal region 20 may be described as a plurality of peripheral arcuate bands with the contact surface 24 comprising the distal surface of each band. Each of the arcuate bands of the enlarged distal region 20 extends axially and has a length 1, which will be discussed in more detail below. Each of the enlarged distal regions 20 may extend axially in a substantially parallel relationship with the optical axis O or, alternatively, may be arcuate in the axial direction such that the length 1 is an arc length X (both symbols illustrated in Fig. 1 on one of the contact surfaces 24).
Regarding exemplary IOL 10 in more detail, the movement assembly 14 may include a plurality of cut-out regions 36 (e.g., four), thereby defining a corresponding plurality of spokes or haptic members 38. Each of the haptic members 38 includes a respective portion of the enlarged distal region 20 of the member 16 of the assembly 14. The cut-out regions 36 provide spatial relief when the ciliary muscle 32 contracts, thereby preventing buckling of the optic 12 during accommodation. To prevent posterior capsule opacification (PCO), each of the cut-out regions 36 may be filled with the same material from which the optic
12 is made.
Regarding the haptic members 38 in more detail, the haptic members 38 as shown in the exemplary embodiment of Fig. 1 may be substantially flat in configuration, flaring outwardly like pieces of a pie. The haptic members 38 desirably lie in planes angled with respect to the optical axis 0 to promote anterior movement, as further explained below. As mentioned, it is preferable to include four haptic members 38, such that each haptic member 38 may extend through nearly 90 , which extent is dependent upon the size of the cut-out regions 36.
To further enhance axial movement and accommodation, the haptic members 38 of exemplary movement assembly 14 may be angulated such that the optic 12 is positioned anterior to respective intersections 40 of the haptic members 38 and the enlarged distal regions 20, which is particularly shown in Fig. 2. For the purposes of this description, this angled configuration of the haptic members 38 is called "anterior angulation." By angulating the haptic members 38 in this anterior manner, the movement assembly 14 is biased to move the optic 12 toward the anterior of the eye 30 when the ciliary muscle 32 contracts. Furthermore, the anterior angulation of the haptic members 38 ensures that the optic 12 moves in the anterior direction when the ciliary muscle 32 contracts.
With continued reference to Figs. 1 and 2 and additional reference to Fig. 3, accommodation may be further enhanced by providing each of the haptic members 38 with a groove 41 formed in a posterior side thereof. The grooves 41 define an area of reduced thickness of each haptic member 38, thereby biasing the haptic members 38 to flex or pivot at the grooves 41. With such a construction, the grooves 41 accommodate flexing of the haptic members 38 in the anterior direction. As an alternative to the linear embodiment shown in Fig. 3, the grooves 41 may be arcuate and concentric with respective contact surfaces 24.
Axial movement may be further facilitated by providing a hinge 42 at the interior intersection 40 of each haptic member 38 with the respective portion of the enlarged
Regarding the haptic members 38 in more detail, the haptic members 38 as shown in the exemplary embodiment of Fig. 1 may be substantially flat in configuration, flaring outwardly like pieces of a pie. The haptic members 38 desirably lie in planes angled with respect to the optical axis 0 to promote anterior movement, as further explained below. As mentioned, it is preferable to include four haptic members 38, such that each haptic member 38 may extend through nearly 90 , which extent is dependent upon the size of the cut-out regions 36.
To further enhance axial movement and accommodation, the haptic members 38 of exemplary movement assembly 14 may be angulated such that the optic 12 is positioned anterior to respective intersections 40 of the haptic members 38 and the enlarged distal regions 20, which is particularly shown in Fig. 2. For the purposes of this description, this angled configuration of the haptic members 38 is called "anterior angulation." By angulating the haptic members 38 in this anterior manner, the movement assembly 14 is biased to move the optic 12 toward the anterior of the eye 30 when the ciliary muscle 32 contracts. Furthermore, the anterior angulation of the haptic members 38 ensures that the optic 12 moves in the anterior direction when the ciliary muscle 32 contracts.
With continued reference to Figs. 1 and 2 and additional reference to Fig. 3, accommodation may be further enhanced by providing each of the haptic members 38 with a groove 41 formed in a posterior side thereof. The grooves 41 define an area of reduced thickness of each haptic member 38, thereby biasing the haptic members 38 to flex or pivot at the grooves 41. With such a construction, the grooves 41 accommodate flexing of the haptic members 38 in the anterior direction. As an alternative to the linear embodiment shown in Fig. 3, the grooves 41 may be arcuate and concentric with respective contact surfaces 24.
Axial movement may be further facilitated by providing a hinge 42 at the interior intersection 40 of each haptic member 38 with the respective portion of the enlarged
13 distal region 20. The hinges 42 enhance the pivoting of the haptic members 38 relative to the enlarged distal region 20 when the ciliary muscle 32 contracts. In addition, each hinge 42 may be configured as a discontinuity, preferably a sharp edge, to retard or prevent cellular growth onto the haptic members 38 and the optic 12, thereby preventing PCO.
As mentioned above, the contact surface 24 of the enlarged distal region 20 has a large surface area, thereby providing a large surface area subject to cellular and fibrous growth. For example, each of the contact surfaces 24 of the enlarged distal region 20 may have an axial length 1 (or arcuate span A) of at least about 1 mm and preferably on the order of about 2 mm. Therefore, depending upon the radius of the IOL 10, each of the contact surfaces 24 may have a surface area of the product of the axial length 1 and the arc length a.
Contact of the IOL 10 with the capsular bag 28 is further enhanced by disposing the enlarged distal region 20 in a perpendicular manner to the haptic members 38.
Accordingly, the contact surface 24 is substantially parallel to the optical axis 10 of the IOL 10. The axial disposition of the enlarged contact surface 24 within the capsular bag 28 increases the retention of the IOL 10 therewithin, particularly immediately following implantation.
Post-operative cellular and fibrous growth of the interior of the capsular bag 28 to the enlarged distal region 20 of the movement assembly 14 enables the IOL 10 of the present invention to essentially fully function like a natural crystalline lens. The cellular and fibrous growth is facilitated by the close proximity of the contact surface 24 with the capsular bag 28.
To further facilitate this growth, the enlarged distal
As mentioned above, the contact surface 24 of the enlarged distal region 20 has a large surface area, thereby providing a large surface area subject to cellular and fibrous growth. For example, each of the contact surfaces 24 of the enlarged distal region 20 may have an axial length 1 (or arcuate span A) of at least about 1 mm and preferably on the order of about 2 mm. Therefore, depending upon the radius of the IOL 10, each of the contact surfaces 24 may have a surface area of the product of the axial length 1 and the arc length a.
Contact of the IOL 10 with the capsular bag 28 is further enhanced by disposing the enlarged distal region 20 in a perpendicular manner to the haptic members 38.
Accordingly, the contact surface 24 is substantially parallel to the optical axis 10 of the IOL 10. The axial disposition of the enlarged contact surface 24 within the capsular bag 28 increases the retention of the IOL 10 therewithin, particularly immediately following implantation.
Post-operative cellular and fibrous growth of the interior of the capsular bag 28 to the enlarged distal region 20 of the movement assembly 14 enables the IOL 10 of the present invention to essentially fully function like a natural crystalline lens. The cellular and fibrous growth is facilitated by the close proximity of the contact surface 24 with the capsular bag 28.
To further facilitate this growth, the enlarged distal
14 region 20 may include a plurality of depressions or holes 44. Each of the holes 44 provides a purchase on which cells and fibrin may grow. It is anticipated that this cellular and fibrous growth may take place within the first few weeks after the IOL 10 is implanted in an eye.
Accordingly, the IOL 10 is permanently attachable to the capsular bag 28. This vigorous attachment of the IOL 10 to the capsular bag 28 ensures that the IOL 10 moves axially in direct response to changes in the capsular bag 28, io therefore accommodating near vision, analogous to that of a natural crystalline lens.
With continued reference to Figs. 2 and 3 and additional reference to Fig. 4, the IOL 10 of the present invention may be configured as a two-optic IOL. More is specifically, exemplary IOL 10 may include a secondary optic 46 coupled to a secondary member 48. Analogous to member 16 described above, the secondary member 48 may include a proximal region coupled to the secondary optic 46 and a distal region, which distal region is either the 20 enlarged distal region 20 described above, or a separate enlarged distal region, as indicated in the region 49.
Further, the plurality of cut-out regions 36 may extend through the secondary member 48, thereby defining a plurality of secondary haptic members 50.
25 The secondary member 48 with secondary optic 46 may be integral with the enlarged distal region 20 or, alternatively, may be mechanically attached to the enlarged distal region 20 or member 16 to function as an auxiliary IOL. In one useful embodiment, the enlarged distal region 30 20 of the first movement member 10 is provided with a groove or channel (not shown). The secondary movement member 48 is adapted to fit into the groove, thereby holding the second optic 46 in position in the eye.
More specifically, the distal regions 49 of the 35 secondary haptic members 50 may be adapted to attach to or be retained by the movement assembly 14 of the IOL 10. For example, a groove may be formed either on a posterior side of member 16 or, alternatively, on an interior side of the enlarged distal region 24. The latter type of groove is 5 seen at 52 in Fig. 5. The groove 52 is sized so that ends of the distal regions 49 of the secondary haptic members 50 are receivable therein. The distal regions 49 may be permanently received within the groove 52 such as with adhesive or, alternatively, releasably received so that the lo secondary optic 46 may be replaced if needed or desired.
Analogous to the haptic members 38 described above, secondary haptic members 50 are angulated such that the secondary optic 46 is positioned posterior to respective intersections of the haptic members and the enlarged distal
Accordingly, the IOL 10 is permanently attachable to the capsular bag 28. This vigorous attachment of the IOL 10 to the capsular bag 28 ensures that the IOL 10 moves axially in direct response to changes in the capsular bag 28, io therefore accommodating near vision, analogous to that of a natural crystalline lens.
With continued reference to Figs. 2 and 3 and additional reference to Fig. 4, the IOL 10 of the present invention may be configured as a two-optic IOL. More is specifically, exemplary IOL 10 may include a secondary optic 46 coupled to a secondary member 48. Analogous to member 16 described above, the secondary member 48 may include a proximal region coupled to the secondary optic 46 and a distal region, which distal region is either the 20 enlarged distal region 20 described above, or a separate enlarged distal region, as indicated in the region 49.
Further, the plurality of cut-out regions 36 may extend through the secondary member 48, thereby defining a plurality of secondary haptic members 50.
25 The secondary member 48 with secondary optic 46 may be integral with the enlarged distal region 20 or, alternatively, may be mechanically attached to the enlarged distal region 20 or member 16 to function as an auxiliary IOL. In one useful embodiment, the enlarged distal region 30 20 of the first movement member 10 is provided with a groove or channel (not shown). The secondary movement member 48 is adapted to fit into the groove, thereby holding the second optic 46 in position in the eye.
More specifically, the distal regions 49 of the 35 secondary haptic members 50 may be adapted to attach to or be retained by the movement assembly 14 of the IOL 10. For example, a groove may be formed either on a posterior side of member 16 or, alternatively, on an interior side of the enlarged distal region 24. The latter type of groove is 5 seen at 52 in Fig. 5. The groove 52 is sized so that ends of the distal regions 49 of the secondary haptic members 50 are receivable therein. The distal regions 49 may be permanently received within the groove 52 such as with adhesive or, alternatively, releasably received so that the lo secondary optic 46 may be replaced if needed or desired.
Analogous to the haptic members 38 described above, secondary haptic members 50 are angulated such that the secondary optic 46 is positioned posterior to respective intersections of the haptic members and the enlarged distal
15 regions 20, which is particularly shown in Fig. 2. For the purposes of this description, this angled configuration of the secondary haptic members 50 will be called "posterior angulation." By angulating the secondary haptic members 50 in this anterior manner, the movement assembly 14 is biased to move the secondary optic 46 toward the posterior of the eye 30 when the ciliary muscle 32 contracts.
In one useful embodiment each of the plurality of cut-out regions 36 in the secondary member 48 is at least partially filled with or covered by a structural material 51 having increased flexibility relative to the movement member. Thus, the second IOL is prevented from buckling while, at the same time the structural material 51 is effective to at least inhibit cell growth from the capsular bag onto the optic. This structural material 51 may have the same chemical make-up as the proximal regions of the movement members and have a reduced thickness relative to the proximal regions to provide the increased flexibility.
In particular, the cut-out regions 36 may be filled with the same material from which the optic 46 is made.
Fig. 6 illustrates an alternative embodiment of the
In one useful embodiment each of the plurality of cut-out regions 36 in the secondary member 48 is at least partially filled with or covered by a structural material 51 having increased flexibility relative to the movement member. Thus, the second IOL is prevented from buckling while, at the same time the structural material 51 is effective to at least inhibit cell growth from the capsular bag onto the optic. This structural material 51 may have the same chemical make-up as the proximal regions of the movement members and have a reduced thickness relative to the proximal regions to provide the increased flexibility.
In particular, the cut-out regions 36 may be filled with the same material from which the optic 46 is made.
Fig. 6 illustrates an alternative embodiment of the
16 present invention in which an intraocular lens (IOL) 60 comprises an inner lens portion mechanically coupled to an outer peripheral region 62. In Fig. 6, the inner lens portion is shown in phantom and includes an optic 64 and a plurality of movement members 66 extending radially outwardly therefrom. As with the earlier embodiments, there are four such movement members 66 extending radially outward evenly about the optic 64, and each defining an included angle of nearly 90 .
As seen in Figs. 6 and 7A-C, the outer peripheral region 62 comprises a plurality of individual arcuate segments 62a-d disposed around the periphery of the IOL and each mechanically coupled to a movement member 66. In the illustrated embodiment, the movement member 66 are substantially pie-shaped and each of the arcuate segments 62 has a length that matches the outer circumferential arc of the respectively coupled movement member. Desirably, the included angle of each movement member 66 and coupled peripheral segment 62 is less than 90 so that cut-outs or spacer regions 68 are defined therebetween. In addition, the arc of the each segment 62 is desirably centered at the optical axis of the optic 64. As previously described, the spacer regions 68 each extend from the peripheral region 62 to the optic 64, and terminate at a radially inner curved end.
Various dimensions of each segment 62 are illustrated in the drawings and exemplary values provided herein. In a preferred embodiment, each of the arcuate segments 62 defines an included angle a of between 70-85 , and more particularly about 78 . Consequently, the angle (3 defined between the segments is between about 5-20 , and more particularly about 12 . The exemplary embodiment has an outer radius r of about 5.27 mm (0.2075 inches) and an inner radius ri of about 4.76 mm (0.187 inches).
As seen in Figs. 6 and 7A-C, the outer peripheral region 62 comprises a plurality of individual arcuate segments 62a-d disposed around the periphery of the IOL and each mechanically coupled to a movement member 66. In the illustrated embodiment, the movement member 66 are substantially pie-shaped and each of the arcuate segments 62 has a length that matches the outer circumferential arc of the respectively coupled movement member. Desirably, the included angle of each movement member 66 and coupled peripheral segment 62 is less than 90 so that cut-outs or spacer regions 68 are defined therebetween. In addition, the arc of the each segment 62 is desirably centered at the optical axis of the optic 64. As previously described, the spacer regions 68 each extend from the peripheral region 62 to the optic 64, and terminate at a radially inner curved end.
Various dimensions of each segment 62 are illustrated in the drawings and exemplary values provided herein. In a preferred embodiment, each of the arcuate segments 62 defines an included angle a of between 70-85 , and more particularly about 78 . Consequently, the angle (3 defined between the segments is between about 5-20 , and more particularly about 12 . The exemplary embodiment has an outer radius r of about 5.27 mm (0.2075 inches) and an inner radius ri of about 4.76 mm (0.187 inches).
17 With reference particularly to Figs. 7B and 7C, each of the arcuate segments 62 includes a rounded outer surface 70 and a pair of grooves 72a and 72b defined on the inner surface. Each groove 72 is defined by a side wall 74, and a peripheral wall 76. The side walls 74 of the two grooves diverge but generally face each other, and the peripheral walls 76 are angled with respect one another and meet at an apex 78, desirably at the axial midplane of the segment 62.
Again, particular dimensions are shown in the drawings, with certain exemplary values provided herein.
In particular, the axial thickness t of each arcuate segment 62 is about 1.02 mm (0.04 inches), while the outer peripheral radius rP is desirably about the same as the thickness t, namely about 1.02 mm (0.04 inches). The overall radial thickness A of each segment 62 is about 0.51 mm (0.02 inches), while the radial depth B of each of the grooves 72 is about 0.23 mm (0.009 inches). The axial width w of the two grooves 72 together is about 0.51 mm (0. 02 inches ), and the peripheral surface 76 of each groove defines an angle y of about 10 at any one point with respect to a plane tangent to the entire arcuate segment 62 at that point. Finally, the included angle 6 defined by the divergent side walls 74 of the two grooves 72 is about 20 .
Because there are two grooves 72a,b, each arcuate segment 62 receives movement members 66 extending outward from two different optics 64. More particularly, Fig. 7C
illustrates two movement members 66a and 66b disposed, respectively, within the grooves 72a and 72b and diverging at the included angle 6 of the side walls 74. In other words, one of the optics is anteriorly vaulted and the other optic is posteriorly vaulted. The two movement members 66a,b are desirably sized to precisely fit within
Again, particular dimensions are shown in the drawings, with certain exemplary values provided herein.
In particular, the axial thickness t of each arcuate segment 62 is about 1.02 mm (0.04 inches), while the outer peripheral radius rP is desirably about the same as the thickness t, namely about 1.02 mm (0.04 inches). The overall radial thickness A of each segment 62 is about 0.51 mm (0.02 inches), while the radial depth B of each of the grooves 72 is about 0.23 mm (0.009 inches). The axial width w of the two grooves 72 together is about 0.51 mm (0. 02 inches ), and the peripheral surface 76 of each groove defines an angle y of about 10 at any one point with respect to a plane tangent to the entire arcuate segment 62 at that point. Finally, the included angle 6 defined by the divergent side walls 74 of the two grooves 72 is about 20 .
Because there are two grooves 72a,b, each arcuate segment 62 receives movement members 66 extending outward from two different optics 64. More particularly, Fig. 7C
illustrates two movement members 66a and 66b disposed, respectively, within the grooves 72a and 72b and diverging at the included angle 6 of the side walls 74. In other words, one of the optics is anteriorly vaulted and the other optic is posteriorly vaulted. The two movement members 66a,b are desirably sized to precisely fit within
18 grooves 72a,b and contact at juxtaposed corners coincident with the apex 78. The resulting two-optic system can be customized to suit a wide variety of patient needs.
In a preferred manufacturing process, the segments 62a-d are formed from a circular ring 80 as seen in Fig.
8. In particular, the ring 80 is molded using conventional means, and the segments 62 are then machined therefrom.
Subsequently, the segments 62 are mechanically coupled to the respective movement members 66 using a suitable adhesive, or the like. Those of skill in the art will understand that there are various means other than adhesives for attaching movement members to peripheral structures. As a result, the IOL 60 has the benefit of an enlarged outer peripheral region 62 which helps distribute forces imparted by the ciliary muscles to the movement members 66, and thereafter to the optic 64. Such a force distribution system helps improve accommodation of the IOL
60.
The optics 12 and 46 may be constructed of rigid biocompatible materials such as polymethyl methacrylate (PMMA) or deformable materials such as silicone polymeric materials, acrylic polymeric materials, hydrogel polymeric materials, and the like. The deformable materials allow the IOL 10 to be rolled or folded for insertion through a small incision into the eye. Although the optic 12 as shown is a refractive lens body, the present IOLs may include a diffractive lens body, and such embodiment is included within the scope of the present invention.
The optic 12 may be either integral with or mechanically coupled to the member 16. The member 16 may be constructed of the same or different biocompatible materials as the optic 12, and is preferably made of polymeric materials such as polypropylene, silicone polymeric materials, acrylic polymeric materials, and the like. The movement assembly 14 is preferably deformable in
In a preferred manufacturing process, the segments 62a-d are formed from a circular ring 80 as seen in Fig.
8. In particular, the ring 80 is molded using conventional means, and the segments 62 are then machined therefrom.
Subsequently, the segments 62 are mechanically coupled to the respective movement members 66 using a suitable adhesive, or the like. Those of skill in the art will understand that there are various means other than adhesives for attaching movement members to peripheral structures. As a result, the IOL 60 has the benefit of an enlarged outer peripheral region 62 which helps distribute forces imparted by the ciliary muscles to the movement members 66, and thereafter to the optic 64. Such a force distribution system helps improve accommodation of the IOL
60.
The optics 12 and 46 may be constructed of rigid biocompatible materials such as polymethyl methacrylate (PMMA) or deformable materials such as silicone polymeric materials, acrylic polymeric materials, hydrogel polymeric materials, and the like. The deformable materials allow the IOL 10 to be rolled or folded for insertion through a small incision into the eye. Although the optic 12 as shown is a refractive lens body, the present IOLs may include a diffractive lens body, and such embodiment is included within the scope of the present invention.
The optic 12 may be either integral with or mechanically coupled to the member 16. The member 16 may be constructed of the same or different biocompatible materials as the optic 12, and is preferably made of polymeric materials such as polypropylene, silicone polymeric materials, acrylic polymeric materials, and the like. The movement assembly 14 is preferably deformable in
19 much the same manner as the optic 12 to facilitate the passage of the IOL 10 through a small incision into the eye. The material or materials of construction from which the movement assembly 14 is made are chosen to provide the assembly with the desired mechanical properties, e.g., strength and deformability, to meet the needs of the particular application involved.
The IOL 10 may be inserted into the capsular bag 28 of a mammalian eye using conventional equipment and techniques, for example, after the natural crystalline lens is removed using a phaceomulsification technique. The IOL
10 is preferably rolled or folded prior to insertion into the eye so as to fit through a small incision, for example, on the order of about 3.2 mm. After insertion, the IOL 10 may be positioned in the eye as shown in Fig. 2.
If the IOL 10 is to be implanted in an adult human eye, the optic 12 preferably has a diameter in the range of about 3.5 mm to about 7 mm and, more preferably, in the range of about 5 mm to about 6 mm. Further, the IOL 10 may have an overall diameter, with the movement assembly 14 in an unstressed condition, of about 8 mm to about 11 mm or 12 mm. Additionally, the optic 12 preferably has a far-vision correction power for infinity in an accommodated state.
The present invention provides accommodating IOLs and methods for using such IOLs. The IOLs of the invention are configured to reduce the stretching of the capsular bag, to maintain the elasticity and/or integrity of the capsular bag, to enhance the effectiveness of the eye, particularly the function of the ciliary muscle and the zonules. The present IOLs promote the secure retention within the capsular bag by providing an enlarged contact surface to which cells and fibrin may grow. In addition, the present IOLs inhibit PCO. These benefits are obtained with IOLs which are streamlined in construction and relatively easy to manufacture and insert into the eye and which effectively provide accommodation for long-term use.
While the present invention has been described with respect to various specific examples and embodiments, it is to be understood that the invention is not limited thereto 5 and that it can be variously practiced within the scope of the following claims.
The IOL 10 may be inserted into the capsular bag 28 of a mammalian eye using conventional equipment and techniques, for example, after the natural crystalline lens is removed using a phaceomulsification technique. The IOL
10 is preferably rolled or folded prior to insertion into the eye so as to fit through a small incision, for example, on the order of about 3.2 mm. After insertion, the IOL 10 may be positioned in the eye as shown in Fig. 2.
If the IOL 10 is to be implanted in an adult human eye, the optic 12 preferably has a diameter in the range of about 3.5 mm to about 7 mm and, more preferably, in the range of about 5 mm to about 6 mm. Further, the IOL 10 may have an overall diameter, with the movement assembly 14 in an unstressed condition, of about 8 mm to about 11 mm or 12 mm. Additionally, the optic 12 preferably has a far-vision correction power for infinity in an accommodated state.
The present invention provides accommodating IOLs and methods for using such IOLs. The IOLs of the invention are configured to reduce the stretching of the capsular bag, to maintain the elasticity and/or integrity of the capsular bag, to enhance the effectiveness of the eye, particularly the function of the ciliary muscle and the zonules. The present IOLs promote the secure retention within the capsular bag by providing an enlarged contact surface to which cells and fibrin may grow. In addition, the present IOLs inhibit PCO. These benefits are obtained with IOLs which are streamlined in construction and relatively easy to manufacture and insert into the eye and which effectively provide accommodation for long-term use.
While the present invention has been described with respect to various specific examples and embodiments, it is to be understood that the invention is not limited thereto 5 and that it can be variously practiced within the scope of the following claims.
Claims (18)
1. An intraocular lens comprising:
an optic adapted to focus light to a retina of an eye and having a central optical axis; and a movement assembly coupled to the optic and adapted to cooperate with the eye to effect accommodating movement of the optic;
the movement assembly including movement members, each having a proximal region coupled to the optic, extending radially outwardly from the optic, and including a distal region being entirely enlarged, and having a contact surface adapted to be in contact with a peripheral region of a capsular bag of an eye;
characterized in that the number of movement members is at least four, and the whole outer surface of each of the enlarged distal regions is parallel to the optical axis; and each of the enlarged distal regions comprises an arcuate band.
an optic adapted to focus light to a retina of an eye and having a central optical axis; and a movement assembly coupled to the optic and adapted to cooperate with the eye to effect accommodating movement of the optic;
the movement assembly including movement members, each having a proximal region coupled to the optic, extending radially outwardly from the optic, and including a distal region being entirely enlarged, and having a contact surface adapted to be in contact with a peripheral region of a capsular bag of an eye;
characterized in that the number of movement members is at least four, and the whole outer surface of each of the enlarged distal regions is parallel to the optical axis; and each of the enlarged distal regions comprises an arcuate band.
2. The intraocular lens according to claim 1, characterized in that the contact surface of the enlarged distal region has an axial length of at least about 1 mm.
3. The intraocular lens according to claim 2, characterized in that the contact surface of the enlarged distal region has an axial length of about 2 mm.
4. The intraocular lens according to any one of claims 1 to 3, characterized in that the movement assembly's four members are circumferentially spaced apart.
5. The intraocular lens of claim 4 wherein the movement assembly is positioned relative to the optic so that, with the intraocular lens at rest, the optic is anteriorly vaulted.
6. The intraocular lens of claim 4 wherein each of the enlarged distal regions is configured such that the contact surface is angled with respect to the proximal region.
7. The intraocular lens of claim 4 wherein each of the enlarged distal regions includes a plurality of through holes extending through the contact surface.
8. The intraocular lens of claim 4 which is deformable to be passed through a small incision for insertion into an eye.
9. The intraocular lens of claim 4 wherein each of the movement members includes a hinge disposed proximally of the enlarged distal region.
10. The intraocular lens of claim 4 further comprising a second optic coupled to the movement assembly.
11. The intraocular lens of claim 10 wherein said movement assembly includes a plurality of haptic members, each haptic member being coupled to the second optic and to one of the enlarged distal regions.
12. The intraocular lens of claim 11, wherein the haptic members are positioned so that, with the intraocular lens at rest, the secondary optic is posteriorly vaulted.
13. The intraocular lens of claim 4, wherein each of the proximal regions is joined to one of the distal regions so that one or more sharp edges are present therebetween.
14. The intraocular lens of claim 4, and wherein the enlarged distal region of each movement member is formed separately from and mechanically coupled to the proximal region of that movement member.
15. The intraocular lens of claim 14, wherein the optic and the proximal region of each movement member are integrally formed.
16. The intraocular lens of claim 15, wherein each distal region comprises an arcuate segment having at least one groove for receiving and mechanically coupling to a proximal region of the movement member.
17. The intraocular lens of claim 16, wherein each arcuate segment includes a pair of grooves each for receiving and mechanically coupling to a proximal region of the movement member, the intraocular lens being a two-optic lens.
18. The intraocular lens of claim 14, wherein the enlarged distal region of each movement member is mechanically coupled to the proximal region of that movement member using adhesive.
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/522,326 US6551354B1 (en) | 2000-03-09 | 2000-03-09 | Accommodating intraocular lens |
US09/522,326 | 2000-03-09 | ||
PCT/US2001/007062 WO2001066042A1 (en) | 2000-03-09 | 2001-03-06 | Accommodating intraocular lens |
Publications (2)
Publication Number | Publication Date |
---|---|
CA2401972A1 CA2401972A1 (en) | 2001-09-13 |
CA2401972C true CA2401972C (en) | 2009-01-20 |
Family
ID=24080414
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002401972A Expired - Lifetime CA2401972C (en) | 2000-03-09 | 2001-03-06 | Accommodating intraocular lens |
Country Status (9)
Country | Link |
---|---|
US (2) | US6551354B1 (en) |
EP (1) | EP1292247B1 (en) |
JP (1) | JP3958576B2 (en) |
AT (1) | ATE353198T1 (en) |
AU (1) | AU2001247288A1 (en) |
BR (1) | BR0109063A (en) |
CA (1) | CA2401972C (en) |
DE (1) | DE60126489T2 (en) |
WO (1) | WO2001066042A1 (en) |
Families Citing this family (169)
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 |
ATE272990T1 (en) * | 1995-02-15 | 2004-08-15 | Medevec Licensing Bv | ADJUSTABLE INTRAOCULAR LENS WITH T-SHAPED BRACKETS |
US20060149369A1 (en) * | 1997-05-20 | 2006-07-06 | C&C Vision International Limited | Accommodating arching lens |
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 |
US20060238702A1 (en) | 1999-04-30 | 2006-10-26 | Advanced Medical Optics, Inc. | Ophthalmic lens combinations |
US20030060881A1 (en) | 1999-04-30 | 2003-03-27 | Advanced Medical Optics, Inc. | Intraocular lens combinations |
AU2001288926A1 (en) * | 2000-09-07 | 2002-03-22 | Allergan Sales, Inc. | Intraocular lens with a posterior lens portion |
US6818158B2 (en) * | 2001-01-25 | 2004-11-16 | Visiogen, Inc. | Accommodating intraocular lens system and method of making same |
US20030078657A1 (en) * | 2001-01-25 | 2003-04-24 | Gholam-Reza Zadno-Azizi | Materials for use in accommodating intraocular lens system |
US20030078658A1 (en) * | 2001-01-25 | 2003-04-24 | Gholam-Reza Zadno-Azizi | Single-piece accomodating intraocular lens system |
US7780729B2 (en) * | 2004-04-16 | 2010-08-24 | Visiogen, Inc. | Intraocular lens |
US6884261B2 (en) * | 2001-01-25 | 2005-04-26 | Visiogen, Inc. | Method of preparing an intraocular lens for implantation |
US7198640B2 (en) * | 2001-01-25 | 2007-04-03 | Visiogen, Inc. | Accommodating intraocular lens system with separation member |
US8062361B2 (en) * | 2001-01-25 | 2011-11-22 | Visiogen, Inc. | Accommodating intraocular lens system with aberration-enhanced performance |
US6786934B2 (en) | 2001-01-25 | 2004-09-07 | Visiogen, Inc. | Biasing element for intraocular lens system |
US20120016349A1 (en) | 2001-01-29 | 2012-01-19 | Amo Development, Llc. | Hybrid ophthalmic interface apparatus and method of interfacing a surgical laser with an eye |
US6524340B2 (en) | 2001-05-23 | 2003-02-25 | Henry M. Israel | Accommodating intraocular lens assembly |
DE10139027A1 (en) * | 2001-08-15 | 2003-02-27 | Humanoptics Ag | Intraocular implant |
US6443985B1 (en) * | 2001-08-27 | 2002-09-03 | Randall Woods | Intraocular lens implant having eye accommodating capabilities |
US20030060878A1 (en) | 2001-08-31 | 2003-03-27 | Shadduck John H. | Intraocular lens system and method for power adjustment |
US7097660B2 (en) * | 2001-12-10 | 2006-08-29 | Valdemar Portney | Accommodating intraocular lens |
US7025783B2 (en) * | 2002-01-14 | 2006-04-11 | Advanced Medical Optics, Inc. | Accommodating intraocular lens with integral capsular bag ring |
US7763069B2 (en) | 2002-01-14 | 2010-07-27 | Abbott Medical Optics Inc. | Accommodating intraocular lens with outer support structure |
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 |
US20050021139A1 (en) * | 2003-02-03 | 2005-01-27 | Shadduck John H. | Ophthalmic devices, methods of use and methods of fabrication |
US6935743B2 (en) * | 2002-02-06 | 2005-08-30 | John H. Shadduck | Adaptive optic lens and method of making |
US6695881B2 (en) | 2002-04-29 | 2004-02-24 | Alcon, Inc. | Accommodative intraocular lens |
US20040034417A1 (en) * | 2002-08-16 | 2004-02-19 | Heyman Thomas M. | Intraocular lens |
US20040243232A1 (en) * | 2002-09-13 | 2004-12-02 | Eyeonics, Inc | Lens for increased depth of focus |
US20040082993A1 (en) * | 2002-10-25 | 2004-04-29 | Randall Woods | Capsular intraocular lens implant having a refractive liquid therein |
US7125422B2 (en) * | 2002-10-25 | 2006-10-24 | Quest Vision Technology, Inc. | Accommodating intraocular lens implant |
US20040082995A1 (en) * | 2002-10-25 | 2004-04-29 | Randall Woods | Telescopic intraocular lens implant for treating age-related macular degeneration |
US7662180B2 (en) | 2002-12-05 | 2010-02-16 | Abbott Medical Optics Inc. | Accommodating intraocular lens and method of manufacture thereof |
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 |
US7247168B2 (en) * | 2002-12-12 | 2007-07-24 | Powervision, Inc. | Accommodating intraocular lens system and method |
US7217288B2 (en) * | 2002-12-12 | 2007-05-15 | Powervision, Inc. | Accommodating intraocular lens having peripherally actuated deflectable surface and method |
US10835373B2 (en) | 2002-12-12 | 2020-11-17 | Alcon Inc. | Accommodating intraocular lenses and methods of use |
CA2507694C (en) * | 2002-12-12 | 2012-07-31 | Victor Esch | Accommodating intraocular lens system and method |
US8328869B2 (en) | 2002-12-12 | 2012-12-11 | Powervision, Inc. | Accommodating intraocular lenses and methods of use |
US8361145B2 (en) | 2002-12-12 | 2013-01-29 | Powervision, Inc. | Accommodating intraocular lens system having circumferential haptic support and method |
US7238201B2 (en) * | 2003-02-13 | 2007-07-03 | Visiogen, Inc. | Accommodating intraocular lens system with enhanced range of motion |
US7615056B2 (en) | 2003-02-14 | 2009-11-10 | Visiogen, Inc. | Method and device for compacting an intraocular lens |
US20040249455A1 (en) * | 2003-06-09 | 2004-12-09 | Tran Son Trung | Accommodative intraocular lens system |
US20050027354A1 (en) * | 2003-07-28 | 2005-02-03 | Advanced Medical Optics, Inc. | Primary and supplemental intraocular lens |
US20050125058A1 (en) * | 2003-12-03 | 2005-06-09 | Eyeonics, Inc. | Accommodating hybrid intraocular lens |
US7553327B2 (en) | 2003-12-04 | 2009-06-30 | The Nice Trust, A Trust Of The Isle Of Man | Accommodating 360 degree sharp edge optic plate haptic lens |
US20050131535A1 (en) * | 2003-12-15 | 2005-06-16 | Randall Woods | Intraocular lens implant having posterior bendable optic |
US7645300B2 (en) * | 2004-02-02 | 2010-01-12 | Visiogen, Inc. | Injector for intraocular lens system |
DE102004027236B4 (en) * | 2004-06-03 | 2006-04-13 | Morcher Gmbh | Capsular equatorial ring |
US7806929B2 (en) * | 2004-08-27 | 2010-10-05 | Brown David C | Intracapsular pseudophakic 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 |
US20060241752A1 (en) * | 2005-04-20 | 2006-10-26 | Israel Henry M | Accommodating multiple lens assembly |
US7771471B2 (en) | 2005-05-13 | 2010-08-10 | C & C Vision International Limited | Floating optic accommodating intraocular lens |
US7591849B2 (en) | 2005-07-01 | 2009-09-22 | Bausch & Lomb Incorpoted | Multi-component accommodative intraocular lens with compressible haptic |
US20070016293A1 (en) * | 2005-07-18 | 2007-01-18 | Alcon, Inc. | Accommodative intraocular lens system |
WO2007019389A1 (en) * | 2005-08-05 | 2007-02-15 | Visiogen, Inc. | Accommodating diffractive intraocular lens |
US20070032868A1 (en) * | 2005-08-08 | 2007-02-08 | Randall Woods | Capsular shape-restoring device |
US9636213B2 (en) * | 2005-09-30 | 2017-05-02 | Abbott Medical Optics Inc. | Deformable intraocular lenses and lens systems |
US20070088433A1 (en) * | 2005-10-17 | 2007-04-19 | Powervision | Accommodating intraocular lens system utilizing direct force transfer from zonules and method of use |
US20070129803A1 (en) * | 2005-12-06 | 2007-06-07 | C&C Vision International Limited | Accommodative Intraocular Lens |
US20080294254A1 (en) * | 2005-12-06 | 2008-11-27 | Cumming J Stuart | Intraocular lens |
US7981155B2 (en) * | 2005-12-07 | 2011-07-19 | C&C Vision International Limited | Hydrolic accommodating intraocular lens |
US7985253B2 (en) * | 2005-12-07 | 2011-07-26 | C&C Vision International Limited | Hydrolic accommodating intraocular lens |
US20070129800A1 (en) * | 2005-12-07 | 2007-06-07 | C&C Vision International Limited | Hydrolic accommodating intraocular lens |
US20070168027A1 (en) * | 2006-01-13 | 2007-07-19 | Brady Daniel G | Accommodating diffractive intraocular lens |
US7837730B2 (en) | 2006-02-21 | 2010-11-23 | C & C International Limited | Floating optic accommodating intraocular lens |
US20070244560A1 (en) * | 2006-04-12 | 2007-10-18 | Alexei Ossipov | Intraocular lens with distortion free valve |
US20070260308A1 (en) * | 2006-05-02 | 2007-11-08 | Alcon, Inc. | Accommodative intraocular lens system |
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 |
US20080021549A1 (en) * | 2006-07-21 | 2008-01-24 | Eagan Barry T | Accommodating intraocular lens having an active power source |
US8163015B2 (en) | 2006-07-25 | 2012-04-24 | C&C Vision International Limited | “W” accommodating intraocular lens |
US20080027539A1 (en) * | 2006-07-25 | 2008-01-31 | Cumming J Stuart | "W" Accommodating Intraocular Lens |
US7763070B2 (en) * | 2006-07-25 | 2010-07-27 | C&C Vision International Limited | “W” accommodating intraocular lens |
US20080027538A1 (en) * | 2006-07-27 | 2008-01-31 | Cumming J Stuart | Polyspheric Accommodating Intraocular Lens |
US20080027540A1 (en) * | 2006-07-31 | 2008-01-31 | Cumming J Stuart | Stabilized accommodating intraocular lens |
US20080046077A1 (en) * | 2006-08-15 | 2008-02-21 | C&C Vision International Limited | Multiocular Intraocular Lens Systems |
US8403984B2 (en) | 2006-11-29 | 2013-03-26 | Visiogen, Inc. | Apparatus and methods for compacting an intraocular lens |
CA2673388C (en) | 2006-12-22 | 2015-11-24 | Amo Groningen B.V. | Accommodating intraocular lens, lens system and frame therefor |
WO2008079671A1 (en) * | 2006-12-22 | 2008-07-03 | Bausch & Lomb Incorporated | Multi-element accommodative intraocular lens |
US7713299B2 (en) | 2006-12-29 | 2010-05-11 | Abbott Medical Optics Inc. | Haptic for accommodating intraocular lens |
US20080161914A1 (en) | 2006-12-29 | 2008-07-03 | Advanced Medical Optics, Inc. | Pre-stressed haptic for accommodating intraocular lens |
CA2674018C (en) | 2006-12-29 | 2015-05-26 | Advanced Medical Optics, Inc. | Multifocal accommodating intraocular lens |
US7811320B2 (en) * | 2007-01-29 | 2010-10-12 | Werblin Research & Development Corp. | Intraocular lens system |
US8066768B2 (en) * | 2007-01-29 | 2011-11-29 | Werblin Research & Development Corp. | Intraocular lens system |
US9398949B2 (en) * | 2007-01-29 | 2016-07-26 | Emmetropia, Inc. | Intraocular lens system |
US8066769B2 (en) * | 2007-01-29 | 2011-11-29 | Werblin Research & Development Corp. | Intraocular lens system |
US7857850B2 (en) * | 2007-02-02 | 2010-12-28 | Adoptics Ag | Interfacial refraction accommodating lens (IRAL) |
US8034106B2 (en) * | 2007-02-02 | 2011-10-11 | Adoptics Ag | Interfacial refraction accommodating lens (IRAL) |
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 |
US20090005866A1 (en) * | 2007-03-13 | 2009-01-01 | C&C Vision International Limited | First elastic hinge accommodating intraocular lens |
US20080281415A1 (en) * | 2007-03-13 | 2008-11-13 | C&C Vision International Limited | Second elastic hinge accommodating intraocular lens |
US20080288066A1 (en) * | 2007-05-16 | 2008-11-20 | C&C Vision International Limited | Toric sulcus lens |
ES2387702T3 (en) * | 2007-05-29 | 2012-09-28 | Steven J. Dell | Accommodative intraocular lens that has a haptic plate |
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 |
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 |
WO2009015226A2 (en) * | 2007-07-23 | 2009-01-29 | Powervision, Inc. | Accommodating intraocular lenses and methods of use |
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 |
US8425595B2 (en) | 2008-03-12 | 2013-04-23 | Visiogen, Inc. | Method for inserting an intraocular lens |
US8034108B2 (en) | 2008-03-28 | 2011-10-11 | Abbott Medical Optics Inc. | Intraocular lens having a haptic that includes a cap |
NZ592645A (en) | 2008-11-20 | 2013-01-25 | Insight Innovations Llc | Biocompatible biodegradable intraocular implant system |
US9943402B2 (en) | 2008-11-20 | 2018-04-17 | Insight Innovations, Llc | Micropatterned intraocular implant |
US20120232649A1 (en) | 2008-11-20 | 2012-09-13 | Insight Innovations, Llc | Intraocular Lens Cell Migration Inhibition System |
US10299913B2 (en) | 2009-01-09 | 2019-05-28 | Powervision, Inc. | Accommodating intraocular lenses and methods of use |
AU2010266022B2 (en) | 2009-06-26 | 2015-04-23 | Johnson & Johnson Surgical Vision, Inc. | Accommodating intraocular lenses |
WO2011017322A1 (en) | 2009-08-03 | 2011-02-10 | Abbott Medical Optics Inc. | Intraocular lens for providing accomodative vision |
US8447086B2 (en) | 2009-08-31 | 2013-05-21 | Powervision, Inc. | Lens capsule size estimation |
US20110071628A1 (en) * | 2009-09-24 | 2011-03-24 | Rainbow Medical Ltd. | Accommodative intraocular lens |
US9114005B2 (en) * | 2009-11-17 | 2015-08-25 | Akkolens International B.V. | Accommodative intraocular lens driven by ciliary mass |
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 |
US9039762B2 (en) * | 2010-03-23 | 2015-05-26 | Novartis Ag | Accommodating intraocular lens using trapezoidal phase shift |
EP2563275A4 (en) | 2010-04-27 | 2017-11-22 | Lensgen, Inc | Accommodating intraocular lens device |
US8523942B2 (en) | 2011-05-17 | 2013-09-03 | James Stuart Cumming | Variable focus intraocular lens |
US9918830B2 (en) | 2010-06-21 | 2018-03-20 | James Stuart Cumming | Foldable intraocular lens with rigid haptics |
US9351825B2 (en) | 2013-12-30 | 2016-05-31 | James Stuart Cumming | Semi-flexible posteriorly vaulted acrylic intraocular lens for the treatment of presbyopia |
US9295544B2 (en) | 2012-06-05 | 2016-03-29 | James Stuart Cumming | Intraocular lens |
US8734512B2 (en) | 2011-05-17 | 2014-05-27 | James Stuart Cumming | Biased accommodating intraocular lens |
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 |
US9295545B2 (en) | 2012-06-05 | 2016-03-29 | James Stuart Cumming | Intraocular lens |
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 |
US10080648B2 (en) | 2012-01-24 | 2018-09-25 | Clarvista Medical, Inc. | Modular intraocular lens designs, tools and methods |
US10028824B2 (en) | 2012-01-24 | 2018-07-24 | Clarvista Medical, Inc. | Modular intraocular lens designs, tools and methods |
CA3177993A1 (en) | 2012-01-24 | 2013-08-01 | The Regents Of The University Of Colorado, A Body Corporate | Modular intraocular lens designs and methods |
US9364316B1 (en) | 2012-01-24 | 2016-06-14 | Clarvista Medical, Inc. | Modular intraocular lens designs, tools and methods |
EP2838472B1 (en) * | 2012-04-20 | 2020-09-23 | Hanita Lenses R.C.A. Ltd. | Intraocular assembly |
US9084674B2 (en) | 2012-05-02 | 2015-07-21 | Abbott Medical Optics Inc. | Intraocular lens with shape changing capability to provide enhanced accomodation and visual acuity |
JP5436618B2 (en) * | 2012-06-05 | 2014-03-05 | 株式会社中京メディカル | Intraocular lens |
DE102012016893A1 (en) | 2012-08-24 | 2014-05-15 | Be Innovative Gmbh | Intraocular lens, in particular capsular bag intraocular lens |
US9925039B2 (en) | 2012-12-26 | 2018-03-27 | Rainbow Medical Ltd. | Accommodative intraocular lens |
US10258462B2 (en) | 2012-12-26 | 2019-04-16 | 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 |
WO2015066502A1 (en) | 2013-11-01 | 2015-05-07 | Thomas Silvestrini | Accomodating intraocular lens device |
EP3062742B1 (en) | 2013-11-01 | 2021-12-01 | Lensgen, Inc. | Two-part accommodating intraocular lens device |
US9615916B2 (en) | 2013-12-30 | 2017-04-11 | James Stuart Cumming | Intraocular lens |
EP3107510B1 (en) | 2014-02-18 | 2023-04-19 | Alcon Inc. | Apparatus for the removal of an intraocular lens |
WO2016038470A2 (en) | 2014-03-10 | 2016-03-17 | Amo Groningen B.V. | Dual-optic intraocular lens that improves overall vision where there is a local loss of retinal function |
WO2015177651A1 (en) | 2014-04-21 | 2015-11-26 | Amo Groningen B.V. | Ophthalmic devices, system and methods that improve peripheral vision |
US10004596B2 (en) | 2014-07-31 | 2018-06-26 | Lensgen, Inc. | Accommodating intraocular lens device |
EP3197462A4 (en) | 2014-09-23 | 2018-05-30 | Lensgen, Inc | Polymeric material for accommodating intraocular lenses |
EP3250152A1 (en) | 2015-01-30 | 2017-12-06 | Clarvista Medical, Inc. | Modular intraocular lens designs |
AU2016349363B2 (en) | 2015-11-04 | 2022-01-27 | Alcon Inc. | Modular intraocular lens designs, tools and methods |
WO2017079733A1 (en) | 2015-11-06 | 2017-05-11 | Powervision, Inc. | Accommodating intraocular lenses and methods of manufacturing |
WO2017096087A1 (en) | 2015-12-01 | 2017-06-08 | Daniel Brady | Accommodating intraocular lens device |
CA3017293A1 (en) | 2016-03-11 | 2017-09-14 | Amo Groningen B.V. | Intraocular lenses that improve peripheral vision |
AU2017252020B2 (en) | 2016-04-19 | 2021-11-11 | Amo Groningen B.V. | Ophthalmic devices, system and methods that improve peripheral vision |
US11045309B2 (en) | 2016-05-05 | 2021-06-29 | The Regents Of The University Of Colorado | Intraocular lens designs for improved stability |
JP2019519664A (en) | 2016-05-27 | 2019-07-11 | レンズジェン、インコーポレイテッド | Narrow molecular weight distribution lens oil for intraocular lens devices |
US10327886B2 (en) | 2016-06-01 | 2019-06-25 | Rainbow Medical Ltd. | Accomodative intraocular lens |
US10441411B2 (en) | 2016-12-29 | 2019-10-15 | Rainbow Medical Ltd. | Accommodative intraocular lens |
US11382736B2 (en) | 2017-06-27 | 2022-07-12 | Alcon Inc. | Injector, intraocular lens system, and related methods |
AU2018330604A1 (en) | 2017-09-11 | 2020-04-02 | Amo Groningen B.V. | Methods and apparatuses to increase intraocular lenses positional stability |
WO2019169084A1 (en) | 2018-03-01 | 2019-09-06 | Ellis Forrest J | Intraocular lens with centration lips |
WO2020226711A1 (en) | 2019-05-03 | 2020-11-12 | JelliSee Ophthalmics Inc. | Intraocular lenses with shape-changing optics |
AU2020357870A1 (en) | 2019-10-04 | 2022-04-28 | Alcon Inc. | Adjustable intraocular lenses and methods of post-operatively adjusting intraocular lenses |
US11759309B2 (en) | 2020-04-29 | 2023-09-19 | Long Bridge Medical, Inc. | Devices to support and position an intraocular lens within the eye and methods of use |
US11357620B1 (en) | 2021-09-10 | 2022-06-14 | California LASIK & Eye, Inc. | Exchangeable optics and therapeutics |
Family Cites Families (160)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
USRE25286E (en) | 1962-11-13 | Bifocal corneal contact lens | ||
US1483509A (en) | 1921-05-05 | 1924-02-12 | Franklin Optical Company | Process of making fused bifocal lenses |
US2129305A (en) | 1936-08-21 | 1938-09-06 | Feinbloom William | Contact lens |
US2274142A (en) | 1940-01-15 | 1942-02-24 | Revalens Co | Multifocal ophthalmic lens |
US2405989A (en) | 1941-08-12 | 1946-08-20 | Beach Lens Corp | Lens |
US2511517A (en) | 1947-01-31 | 1950-06-13 | Bell & Howell Co | Method of producing optical glass of varied refractive index |
US3031927A (en) | 1958-03-03 | 1962-05-01 | Plastic Contact Lens Company | Bifocal corneal contact lens |
US3034403A (en) | 1959-04-03 | 1962-05-15 | Neefe Hamilton Res Company | Contact lens of apparent variable light absorption |
US3227507A (en) | 1961-08-16 | 1966-01-04 | Feinbloom William | Corneal contact lens having inner ellipsoidal surface |
US3339997A (en) | 1962-07-30 | 1967-09-05 | Plastic Contact Lens Company | Bifocal ophthalmic lens having different color distance and near vision zones |
US3210894A (en) | 1962-08-13 | 1965-10-12 | Kollmorgen Corp | Method of producing aspheric surfaces on mirrors or lenses |
US3420006A (en) | 1964-01-27 | 1969-01-07 | Howard J Barnett | Apparatus for grinding multifocal lens |
US3431327A (en) | 1964-08-31 | 1969-03-04 | George F Tsuetaki | Method of making a bifocal contact lens with an embedded metal weight |
US3482906A (en) | 1965-10-04 | 1969-12-09 | David Volk | Aspheric corneal contact lens series |
US3542461A (en) | 1967-11-20 | 1970-11-24 | Du Pont | Contact lens having an index of refraction approximating that of human tears |
FR2097216A5 (en) | 1970-05-27 | 1972-03-03 | Anvar | |
US4055378A (en) | 1971-12-31 | 1977-10-25 | Agfa-Gevaert Aktiengesellschaft | Silicone contact lens with hydrophilic surface treatment |
CA1012392A (en) | 1973-08-16 | 1977-06-21 | American Optical Corporation | Progressive power ophthalmic lens |
US3922728A (en) | 1974-08-15 | 1975-12-02 | Krasnov Mikhail M | Artificial crystalline lens |
US3932148A (en) | 1975-01-21 | 1976-01-13 | Criterion Manufacturing Company, Inc. | Method and apparatus for making complex aspheric optical surfaces |
DE2610203B2 (en) | 1976-03-11 | 1981-01-22 | Optische Werke G. Rodenstock, 8000 Muenchen | Progressive lens |
US4210391A (en) | 1977-09-14 | 1980-07-01 | Cohen Allen L | Multifocal zone plate |
US4162122A (en) | 1977-09-14 | 1979-07-24 | Cohen Allen L | Zonal bifocal contact lens |
US4195919A (en) | 1977-10-31 | 1980-04-01 | Shelton William A | Contact lens with reduced spherical aberration for aphakic eyes |
DE2814916C3 (en) | 1978-04-06 | 1982-01-07 | Optische Werke G. Rodenstock, 8000 München | Spectacle lens with a progression area located between the far part and the near part |
US4199231A (en) | 1978-08-21 | 1980-04-22 | Evans Carl H | Hydrogel contact lens |
US4253199A (en) | 1978-09-25 | 1981-03-03 | Surgical Design Corporation | Surgical method and apparatus for implants for the eye |
US4338005A (en) | 1978-12-18 | 1982-07-06 | Cohen Allen L | Multifocal phase place |
US4340283A (en) | 1978-12-18 | 1982-07-20 | Cohen Allen L | Phase shift multifocal zone plate |
US4254509A (en) | 1979-04-09 | 1981-03-10 | Tennant Jerald L | Accommodating intraocular implant |
US4274717A (en) | 1979-05-18 | 1981-06-23 | Younger Manufacturing Company | Ophthalmic progressive power lens and method of making same |
JPS5942286B2 (en) | 1979-08-24 | 1984-10-13 | セイコーエプソン株式会社 | eyeglass lenses |
US4316293A (en) | 1979-08-27 | 1982-02-23 | Bayers Jon Herbert | Flexible intraocular lens |
US4418991A (en) | 1979-09-24 | 1983-12-06 | Breger Joseph L | Presbyopic contact lens |
US4307945A (en) | 1980-02-14 | 1981-12-29 | Itek Corporation | Progressively varying focal power opthalmic lens |
US4377329A (en) | 1980-02-26 | 1983-03-22 | Stanley Poler | Contact lens or the like |
USRE32525F1 (en) | 1980-04-01 | 1989-05-09 | Universal intraocular lens and a method of measuring an eye chamber size | |
US4370760A (en) | 1981-03-25 | 1983-02-01 | Kelman Charles D | Anterior chamber intraocular lens |
US4402579A (en) | 1981-07-29 | 1983-09-06 | Lynell Medical Technology Inc. | Contact-lens construction |
US4409691A (en) | 1981-11-02 | 1983-10-18 | Levy Chauncey F | Focussable intraocular lens |
US4702244A (en) | 1982-02-05 | 1987-10-27 | Staar Surgical Company | Surgical device for implantation of a deformable intraocular lens |
US5776191A (en) | 1982-02-05 | 1998-07-07 | Staar Surgical Company | Fixation system for intraocular lens structures |
US4404694A (en) | 1982-03-18 | 1983-09-20 | Kelman Charles D | Intraocular lens |
DE3222099C2 (en) | 1982-06-11 | 1984-06-20 | Titmus Eurocon Kontaktlinsen Gmbh & Co Kg, 8750 Aschaffenburg | Bifocal contact lens of the bivisual type |
GB2124500B (en) | 1982-07-22 | 1986-04-30 | Mazzocco Thomas R | Improved fixation system for intraocularers structures |
US4504982A (en) | 1982-08-05 | 1985-03-19 | Optical Radiation Corporation | Aspheric intraocular lens |
US4573775A (en) | 1982-08-19 | 1986-03-04 | Vistakon, Inc. | Bifocal contact lens |
US4888015A (en) | 1982-08-20 | 1989-12-19 | Domino Rudolph S | Method of replacing an eye lens |
EP0104832B1 (en) | 1982-09-29 | 1987-11-11 | Pilkington Brothers P.L.C. | Improvements in or relating to ophthalmic lenses |
US4476591A (en) | 1982-10-07 | 1984-10-16 | Arnott Eric J | Lens implants for insertion in the human eye |
DE3381691D1 (en) | 1982-10-13 | 1990-08-02 | Ng Trustees & Nominees Ltd | BIFOCAL CONTACT LENSES. |
US4890913A (en) | 1982-10-13 | 1990-01-02 | Carle John T De | Zoned multi-focal contact lens |
GB2129157B (en) | 1982-10-27 | 1986-02-05 | Pilkington Perkin Elmer Ltd | Bifocal contact lenses having defractive power |
DE3246306A1 (en) | 1982-12-14 | 1984-06-14 | Titmus Eurocon Kontaktlinsen Gmbh & Co Kg, 8750 Aschaffenburg | Bifocal lens of bivisual type |
US4580882A (en) | 1983-04-21 | 1986-04-08 | Benjamin Nuchman | Continuously variable contact lens |
US4618229A (en) | 1983-07-22 | 1986-10-21 | Bausch & Lomb Incorporated | Bifocal contact lens |
US4551864A (en) | 1983-08-18 | 1985-11-12 | Iolab Corporation | Anterior chamber lens |
DE3332313A1 (en) | 1983-09-07 | 1985-04-04 | Titmus Eurocon Kontaktlinsen GmbH, 8750 Aschaffenburg | MULTIFOCAL, ESPECIALLY BIFOCAL, INTRAOCULAR ARTIFICIAL EYE LENS |
GB2146791B (en) | 1983-09-16 | 1987-01-28 | Suwa Seikosha Kk | Progressive multifocal ophthalmic lens |
US4636049A (en) | 1983-09-20 | 1987-01-13 | University Optical Products Co. | Concentric bifocal contact lens |
US4560383A (en) | 1983-10-27 | 1985-12-24 | Leiske Larry G | Anterior chamber intraocular lens |
US4687484A (en) | 1983-12-12 | 1987-08-18 | Kaplan Linda J | Anterior chamber intraocular lens |
US4596578A (en) | 1984-01-30 | 1986-06-24 | Kelman Charles D | Intraocular lens with miniature optic |
US4636211A (en) | 1984-03-13 | 1987-01-13 | Nielsen J Mchenry | Bifocal intra-ocular lens |
US4629460A (en) * | 1984-06-25 | 1986-12-16 | Dyer Robert L | Intraocular lens |
US4720286A (en) | 1984-07-20 | 1988-01-19 | Bailey Kelvin E | Multifocus intraocular lens |
US4976732A (en) | 1984-09-12 | 1990-12-11 | International Financial Associates Holdings, Inc. | Optical lens for the human eye |
US4725278A (en) * | 1985-01-22 | 1988-02-16 | Shearing Steven P | Intraocular lens |
US4759762A (en) | 1985-03-08 | 1988-07-26 | Grendahl Dennis T | Accommodating lens |
US4693572A (en) | 1985-06-03 | 1987-09-15 | Fused Kontacts Of Chicago, Inc. | Monocentric bifocal corneal contact lens |
US4752123A (en) | 1985-11-19 | 1988-06-21 | University Optical Products Co. | Concentric bifocal contact lens with two distance power regions |
US4890912A (en) | 1986-01-24 | 1990-01-02 | Rients Visser | Trifocal eye-contact lens |
GB2192291B (en) | 1986-03-04 | 1990-08-22 | Gupta Anil K | Progressive power contact lens. |
US4725277A (en) | 1986-05-14 | 1988-02-16 | Precision-Cosmet Co., Inc. | Intraocular lens with tapered haptics |
EP0248489A3 (en) | 1986-06-02 | 1989-09-06 | Gregory N. Miller | Contact lens and method of making same |
US5192318A (en) | 1986-06-05 | 1993-03-09 | Schneider Richard T | One-piece bifocal intraocular lens construction |
US4676792A (en) | 1986-08-26 | 1987-06-30 | Donald Praeger | Method and artificial intraocular lens device for the phakic treatment of myopia |
US4842601A (en) | 1987-05-18 | 1989-06-27 | Smith S Gregory | Accommodating intraocular lens and method of implanting and using same |
US5201762A (en) | 1987-05-20 | 1993-04-13 | Hauber Frederick A | Intraocular archromatic lens |
US4790847A (en) | 1987-05-26 | 1988-12-13 | Woods Randall L | Intraocular lens implant having eye focusing capabilities |
US4898461A (en) | 1987-06-01 | 1990-02-06 | Valdemar Portney | Multifocal ophthalmic lens |
US5270744A (en) | 1987-06-01 | 1993-12-14 | Valdemar Portney | Multifocal ophthalmic lens |
US5166711A (en) | 1987-06-01 | 1992-11-24 | Valdemar Portney | Multifocal ophthalmic lens |
US5166712A (en) | 1987-06-01 | 1992-11-24 | Valdemar Portney | Multifocal ophthalmic lens |
US5225858A (en) | 1987-06-01 | 1993-07-06 | Valdemar Portney | Multifocal ophthalmic lens |
US5019099A (en) | 1987-07-02 | 1991-05-28 | Nordan Lee T | Intraocular multifocal lens method for correcting the aphakic eye |
US4769033A (en) | 1987-07-02 | 1988-09-06 | Nordan Lee T | Intraocular multifocal lens |
US4917681A (en) | 1987-08-24 | 1990-04-17 | Nordan Lee T | Intraocular multifocal lens |
US4932968A (en) | 1987-07-07 | 1990-06-12 | Caldwell Delmar R | Intraocular prostheses |
US4919663A (en) | 1987-08-24 | 1990-04-24 | Grendahl Dennis T | Laminated zone of focus artificial hydrogel lens |
US4921496A (en) | 1987-08-24 | 1990-05-01 | Grendahl Dennis T | Radially segemented zone of focus artificial hydrogel lens |
US4906246A (en) | 1987-08-24 | 1990-03-06 | Grendahl Dennis T | Cylindrically segmented zone of focus artificial hydrogel lens |
US5158572A (en) | 1987-09-10 | 1992-10-27 | Nielsen James Mchenry | Multifocal intraocular lens |
US5047052A (en) | 1987-11-06 | 1991-09-10 | Seymour Dubroff | Anterior chamber intraocular lens with four point fixation |
US4881804A (en) | 1987-11-12 | 1989-11-21 | Cohen Allen L | Multifocal phase plate with a pure refractive portion |
US4888012A (en) | 1988-01-14 | 1989-12-19 | Gerald Horn | Intraocular lens assemblies |
GB2215076A (en) | 1988-02-02 | 1989-09-13 | Dennis T Grendahl | Intraocular lens having a hard optic and a soft skirt |
IT1215851B (en) | 1988-02-11 | 1990-02-22 | Renato Liffredo | INTRAOCULAR LENS WITH CHROMATIC CORRECTION AND ABSORPTION DIAGRAM. |
US5000559A (en) | 1988-02-29 | 1991-03-19 | Nikon Corporation | Ophthalmic lenses having progressively variable refracting power |
CA1316728C (en) | 1988-04-01 | 1993-04-27 | Michael J. Simpson | Multi-focal diffractive ophthalmic lenses |
US5089024A (en) | 1988-04-19 | 1992-02-18 | Storz Instrument Company | Multi-focal intraocular lens |
FR2631228B1 (en) | 1988-05-11 | 1990-08-10 | Domilens Laboratoires | INTRA-EYE IMPLANT OF PREVIOUS CHAMBER |
US4932970A (en) | 1988-05-17 | 1990-06-12 | Allergan, Inc. | Ophthalmic lens |
US4923296A (en) | 1988-07-14 | 1990-05-08 | Erickson Paul M | Oriented simultaneous vision bifocal contact lenses or the like utilizing introaocular suppression of blur |
CN1020134C (en) | 1988-07-20 | 1993-03-17 | 艾伦·L·科恩 | Multifocal optical device |
US5192317A (en) | 1988-07-26 | 1993-03-09 | Irvin Kalb | Multi focal intra-ocular lens |
US4830481A (en) | 1988-08-12 | 1989-05-16 | Minnesota Mining And Manufacturing Company | Multifocal diffractive lens |
US4932966A (en) | 1988-08-15 | 1990-06-12 | Storz Instrument Company | Accommodating intraocular lens |
US4994082A (en) | 1988-09-09 | 1991-02-19 | Ophthalmic Ventures Limited Partnership | Accommodating intraocular lens |
US4990159A (en) | 1988-12-02 | 1991-02-05 | Kraff Manus C | Intraocular lens apparatus with haptics of varying cross-sectional areas |
US4892543A (en) | 1989-02-02 | 1990-01-09 | Turley Dana F | Intraocular lens providing accomodation |
FR2642854B1 (en) | 1989-02-03 | 1991-05-03 | Essilor Int | OPTICAL LENS WITH SIMULTANEOUS VISION FOR PRESBYTIA CORRECTION |
FR2647227B1 (en) | 1989-05-19 | 1991-08-23 | Essilor Int | OPTICAL COMPONENT, SUCH AS AN INTRAOCULAR IMPLANT OR CONTACT LENS, SUITABLE FOR CORRECTING THE VISION OF AN INDIVIDUAL |
US4955902A (en) | 1989-11-13 | 1990-09-11 | Kelman Charles D | Decentered intraocular lens |
US5002382A (en) | 1989-12-07 | 1991-03-26 | Leonard Seidner | Multifocal corneal contact lenses |
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 |
US5026396A (en) | 1990-05-07 | 1991-06-25 | Darin John J | Two-piece intraocular lens |
US5096285A (en) | 1990-05-14 | 1992-03-17 | Iolab Corporation | Multifocal multizone diffractive ophthalmic lenses |
US5147397A (en) | 1990-07-03 | 1992-09-15 | Allergan, Inc. | Intraocular lens and method for making same |
US5171266A (en) | 1990-09-04 | 1992-12-15 | Wiley Robert G | Variable power intraocular lens with astigmatism correction |
US5173723A (en) | 1990-10-02 | 1992-12-22 | Volk Donald A | Aspheric ophthalmic accommodating lens design for intraocular lens and contact lens |
US5112351A (en) | 1990-10-12 | 1992-05-12 | Ioptex Research Inc. | Multifocal intraocular lenses |
US5260727A (en) | 1990-10-22 | 1993-11-09 | Oksman Henry C | Wide depth of focus intraocular and contact lenses |
US5258025A (en) | 1990-11-21 | 1993-11-02 | Fedorov Svjatoslav N | Corrective intraocular lens |
US5766244A (en) | 1991-05-23 | 1998-06-16 | Binder; Helmut | Intraocular artificial lens and method for fabricating same |
US5326347A (en) | 1991-08-12 | 1994-07-05 | Cumming J Stuart | Intraocular implants |
EP0601055B1 (en) | 1991-08-16 | 2000-06-07 | GALIN, Miles A. | Medicament coated refractive anterior chamber ocular implant |
US5578081A (en) | 1991-11-12 | 1996-11-26 | Henry H. McDonald | Eye muscle responsive artificial lens unit |
US5275623A (en) | 1991-11-18 | 1994-01-04 | Faezeh Sarfarazi | Elliptical accommodative intraocular lens for small incision surgery |
NL9200400A (en) | 1992-03-04 | 1993-10-01 | Jose Jorge Pavlotzky Handelend | BIFOCAL CONTACT LENS, AND METHOD FOR MANUFACTURING SUCH CONTACT LENSES |
US5443506A (en) | 1992-11-18 | 1995-08-22 | Garabet; Antoine L. | Lens with variable optical properties |
US5354335A (en) | 1993-02-04 | 1994-10-11 | Isaac Lipshitz | Intraocular insert for implantation in the human eye |
US6322589B1 (en) * | 1995-10-06 | 2001-11-27 | J. Stuart Cumming | Intraocular lenses with fixated haptics |
RU2033114C1 (en) | 1993-04-22 | 1995-04-20 | Межотраслевой научно-технический комплекс "Микрохирургия глаза" | Artificial crystalline lens |
US5489302A (en) | 1994-05-24 | 1996-02-06 | Skottun; Bernt C. | Accommodating intraocular lens |
JP3745394B2 (en) | 1994-07-04 | 2006-02-15 | 武敏 鈴木 | Intraocular lens |
FR2723691B1 (en) * | 1994-08-22 | 1997-01-24 | Philippe Crozafon | INTRAOCULAR IMPLANT |
US6013101A (en) | 1994-11-21 | 2000-01-11 | Acuity (Israel) Limited | Accommodating intraocular lens implant |
US5549760A (en) | 1994-12-01 | 1996-08-27 | White Consolidated Industries, Inc. | Mounting device for dishwasher insulation |
ATE272990T1 (en) * | 1995-02-15 | 2004-08-15 | Medevec Licensing Bv | ADJUSTABLE INTRAOCULAR LENS WITH T-SHAPED BRACKETS |
US5628795A (en) | 1995-03-15 | 1997-05-13 | Langerman David W | Spare parts for use in ophthalmic surgical procedures |
US5652638A (en) | 1995-05-04 | 1997-07-29 | Johnson & Johnson Vision Products, Inc. | Concentric annular ring lens designs for astigmatism |
US5682223A (en) | 1995-05-04 | 1997-10-28 | Johnson & Johnson Vision Products, Inc. | Multifocal lens designs with intermediate optical powers |
US5684560A (en) | 1995-05-04 | 1997-11-04 | Johnson & Johnson Vision Products, Inc. | Concentric ring single vision lens designs |
US5607472A (en) | 1995-05-09 | 1997-03-04 | Emory University | Intraocular lens for restoring accommodation and allows adjustment of optical power |
EP0901354B1 (en) * | 1996-05-17 | 2004-03-17 | Helmut Payer | An ocular implant |
US5769890B1 (en) | 1997-01-16 | 2000-09-05 | Surgical Concepts Inc | Placement of second artificial lens in eye to correct for optical defects of first artificial lens in eye |
US5928283A (en) | 1997-06-26 | 1999-07-27 | Visioncare Ltd | Telescopic device for an intraocular lens |
US5843188A (en) | 1997-10-20 | 1998-12-01 | Henry H. McDonald | Accommodative lens implantation |
US5814103A (en) | 1998-01-15 | 1998-09-29 | Visioncare Ltd. | Intraocular lens and telescope with mating fasteners |
US5876442A (en) | 1998-01-15 | 1999-03-02 | Visioncare Ltd. | Intraocular lens implant with telescope support |
US6186148B1 (en) * | 1998-02-04 | 2001-02-13 | Kiyoshi Okada | Prevention of posterior capsular opacification |
US6176878B1 (en) | 1998-12-17 | 2001-01-23 | Allergan Sales, Inc. | Accommodating intraocular lens |
US6224628B1 (en) * | 1999-04-23 | 2001-05-01 | Thinoptx, Inc. | Haptics for an intraocular lens |
DE60029102T2 (en) * | 1999-04-30 | 2007-01-11 | Advanced Medical Optics, Inc., Santa Ana | MOVABLE INTRAOCULAR LENSES |
US6217612B1 (en) | 1999-09-10 | 2001-04-17 | Randall Woods | Intraocular lens implant having eye accommodating capabilities |
DE50013494D1 (en) * | 1999-12-14 | 2006-11-02 | Boehm Hans Georg | Focusable intraocular lens |
FR2804860B1 (en) * | 2000-02-16 | 2002-04-12 | Humanoptics Ag | ACCOMODATIVE CRYSTALLINE IMPLANT |
US6797004B1 (en) * | 2000-03-02 | 2004-09-28 | Advanced Medical Optics, Inc. | Holders for intraocular lenses |
-
2000
- 2000-03-09 US US09/522,326 patent/US6551354B1/en not_active Expired - Lifetime
-
2001
- 2001-03-06 CA CA002401972A patent/CA2401972C/en not_active Expired - Lifetime
- 2001-03-06 JP JP2001564696A patent/JP3958576B2/en not_active Expired - Fee Related
- 2001-03-06 DE DE60126489T patent/DE60126489T2/en not_active Expired - Lifetime
- 2001-03-06 AU AU2001247288A patent/AU2001247288A1/en not_active Abandoned
- 2001-03-06 BR BR0109063-1A patent/BR0109063A/en not_active Application Discontinuation
- 2001-03-06 AT AT01920212T patent/ATE353198T1/en not_active IP Right Cessation
- 2001-03-06 WO PCT/US2001/007062 patent/WO2001066042A1/en active IP Right Grant
- 2001-03-06 EP EP01920212A patent/EP1292247B1/en not_active Expired - Lifetime
-
2002
- 2002-12-23 US US10/329,076 patent/US20030109925A1/en not_active Abandoned
Also Published As
Publication number | Publication date |
---|---|
JP3958576B2 (en) | 2007-08-15 |
US6551354B1 (en) | 2003-04-22 |
DE60126489T2 (en) | 2007-11-15 |
BR0109063A (en) | 2002-12-10 |
DE60126489D1 (en) | 2007-03-22 |
EP1292247A1 (en) | 2003-03-19 |
ATE353198T1 (en) | 2007-02-15 |
CA2401972A1 (en) | 2001-09-13 |
AU2001247288A1 (en) | 2001-09-17 |
JP2003525694A (en) | 2003-09-02 |
US20030109925A1 (en) | 2003-06-12 |
EP1292247B1 (en) | 2007-02-07 |
WO2001066042A1 (en) | 2001-09-13 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA2401972C (en) | Accommodating intraocular lens | |
US7326246B2 (en) | Accommodating intraocular lens with elongated suspension structure | |
CA2401795C (en) | Holders for intraocular lenses | |
CA2350795C (en) | Accommodating multifocal intraocular lens | |
EP1304979B1 (en) | Accommodating intraocular lens with suspension structure | |
EP1278483B1 (en) | Accommodating, reduced add power multifocal intraocular lenses | |
EP1176930B1 (en) | Intraocular lens combinations | |
US7025783B2 (en) | Accommodating intraocular lens with integral capsular bag ring | |
EP1651145B1 (en) | Primary and supplemental intraocular lens system | |
US20020120329A1 (en) | Moveable intraocular lenses and combinations of intraocular lenses | |
AU2001259360A1 (en) | Accommodating, reduced add power multifocal intraocular lenses | |
EP1185219B1 (en) | Moveable intraocular lens |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
EEER | Examination request | ||
MKEX | Expiry |
Effective date: 20210308 |