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WO2002019949A2 - Lentille intraoculaire avec partie lentille posterieure - Google Patents

Lentille intraoculaire avec partie lentille posterieure Download PDF

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Publication number
WO2002019949A2
WO2002019949A2 PCT/US2001/028144 US0128144W WO0219949A2 WO 2002019949 A2 WO2002019949 A2 WO 2002019949A2 US 0128144 W US0128144 W US 0128144W WO 0219949 A2 WO0219949 A2 WO 0219949A2
Authority
WO
WIPO (PCT)
Prior art keywords
optic
lens
eye
intraocular lens
lens portion
Prior art date
Application number
PCT/US2001/028144
Other languages
English (en)
Other versions
WO2002019949A3 (fr
Inventor
Stephen W. Laguette
Joseph I. Weinschenk, Iii
Charles X. Liao
Massoud Ghazizadeh
Original Assignee
Allergan Sales, Inc.
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Allergan Sales, Inc. filed Critical Allergan Sales, Inc.
Priority to AU2001288926A priority Critical patent/AU2001288926A1/en
Publication of WO2002019949A2 publication Critical patent/WO2002019949A2/fr
Publication of WO2002019949A3 publication Critical patent/WO2002019949A3/fr

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 or corneal implants; 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 or corneal implants; 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 or corneal implants; 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

Definitions

  • the present invention relates to intraocular lenses (IOLs) . More particularly, the invention relates to IOLs with lens portions, for example, posterior lens portions which are adapted to provide accommodation in the eye .
  • IOLs intraocular lenses
  • the human eye includes an anterior chamber between the cornea and iris, a posterior chamber, defined by a capsular bag, containing a crystalline lens, a ciliary muscle, a vitreous chamber behind the lens containing the vitreous humor, and a retina at the rear of this chamber.
  • the human eye has a natural accommodation ability. The contraction and relaxation of the ciliary muscle provides the eye with near and distant vision, respectively. This ciliary muscle action shapes the natural crystalline lens to the appropriate optical configuration for focusing light rays entering the eye on the retina.
  • a conventional, monofocal IOL can be placed in the posterior chamber.
  • Such a conventional IOL has very limited, if any, accommodating ability.
  • the wearer of such an IOL continues to require the ability to view both near and far (distant) objects.
  • Corrective spectacles may be employed as a useful solution.
  • multifocal IOLs without accommodating movement have been used to provide near/far vision correction.
  • the present accommodating IOLs take advantage of employing an optic made including at least two portions to enhance the accommodation achievable in the eye in response to normal accommodative stimuli, for example, while preferably providing substantially normal distance vision with the IOL in a rest or unaccommodated condition.
  • the present lenses provide for controlled vision correction or focusing for both near objects and far or distant objects. Further, a greater overall range of accommodation is often achieved.
  • the present IOLs are relatively straightforward in construction and to manufacture or produce, can be implanted or inserted into the eye using systems and procedures which are well known in the art and function effectively with little or no additional treatments or medications being required.
  • intraocular lenses comprise an optic adapted to focus light toward a retina of a mammalian eye and, in cooperation with the mammalian eye, to provide accommodation.
  • the optic includes a first lens portion adapted to move in response to the action of the mammalian eye; and a second lens portion secured to the first portion of the optic and positioned generally in a posterior region of the optic and/or having a baseline diopter power for distance vision.
  • the first portion is comprised of an optically clear material that is easily reshaped and may also be axially movable, when exposed to forces exerted by the mammalian eye .
  • the first lens portion of the optic includes an anterior surface, which often coincides with the anterior face of the optic.
  • the first portion is adapted to be reshaped in response to the action of the mammalian eye.
  • Such reshaping advantageously effects a change in the curvature of the anterior surface of the first portion, or the anterior face of the optic.
  • Such change in curvature changes the optical or diopter power of the optic and, ultimately provides accommodation.
  • the first portion of the optic may additionally be adapted to move axially in the mammalian eye in response to the action of the mammalian eye. Such axial movement may provide an additional degree of accommodation.
  • the reshaping of the optic be the primary or major source of accommodating movement of the present optics.
  • the second lens portion of the optic is comprised of an optically clear material .
  • the second portion is located generally posterior of the first portion, when the IOL is placed in the eye .
  • the second portion includes a posterior surface which defines at least a portion of the posterior face of the optic.
  • the second portion can, however, be totally encased or surrounded by the first portion with the second portion being located generally posterior of the center point of the optic, for example, with the shape of at least a portion of the posterior face of the optic being substantially the shape of the posterior surface of the second portion, and this embodiment is included within the scope of the present invention.
  • the posterior bias of the second portion is advantageous in allowing the first portion, and in particular the anterior surface of the first portion, to be reshaped to an enhanced extent by the action of the mammalian eye. Such enhanced reshaping results in an enhanced amount of accommodation achieved by the present IOLs .
  • the second lens portion of the optic has a baseline diopter power for distance vision.
  • Such a baseline diopter power may be considered a zero add power in that this baseline power is such that substantially no positive diopter power beyond the distance vision correction power required by the wearer of the IOL is provided.
  • the wearer of the present IOL wishes to see a distant object, the IOL is in an unaccommodated condition and the distance baseline diopter power of the second lens portion of the optic provides the wearer with the ability to see the distant object in focus.
  • the second portion of the present optics advantageously may be monofocal, having a diopter power for distance vision.
  • the first lens portion of the optic preferably is more deformable than the second lens portion in the eye. That is, the first portion preferably is more easily reshaped or achieves a larger degree of reshaping in the eye in response to the action of the eye than does the second portion.
  • the second portion is substantially rigid, or substantially not reshapable, in response to forces exerted by the eye on the second portion in the eye .
  • the second lens portion of the present optic may have a higher, lower or the same refractive index relative to the refractive index of the first portion.
  • both first and second portions of the present optics may have refractive indexes of about 1.37 or less.
  • both the first and second portions have refractive indexes of at least about 1.40 and more preferably at least about 1.42.
  • a force transfer assembly in another very useful embodiment, has a first end coupled to the optic and a second end extending away from the optic and adapted to contact a posterior bag of the mammalian eye when the IOL is located in the mammalian eye.
  • the force transfer assembly is adapted to transfer the force exerted by the eye to the optic to facilitate the movement of the optic.
  • the force transfer assembly is adapted to transfer the force exerted by the eye to the optic to facilitate reshaping the first lens portion in response to the action of the mammalian eye, and possibly moving the first portion axially in the mammalian eye in response to the action of the mammalian eye.
  • the force transfer assembly is very effective in facilitating the accommodation obtained by the present IOLs.
  • the optic can be sized and configured to fit within the capsular bag and to contact the capsular bag, in particular the periphery of the capsular bag, so that the force exerted by the eye can be transferred directly to the optic of the present IOL.
  • IOLs in which the optics are sized and configured to contact the peripheral capsular bag are very effective in being reshaped to provide the desired accommodation.
  • substantially filling the capsular bag volume with an optic including a reshapable first lens portion and a second lens portion as in the present optics reduces the risk of decentration or tilt of the lens system in the eye, as well as reducing the risk of decentration or tilt between individual lens components, relative to lens systems in which the optic does not substantially fill the capsular bag volume.
  • Providing for a reduced risk of decentration is highly advantageous, for example, as the capsular bag compresses or contracts. Even if the contraction of the capsular bag is asymmetric, for example, because the zonules are not of uniform strength, the elastic properties of the first lens portion mitigate against this asymmetry and reduce the risk of decentration.
  • Substantially filling the capsular bag volume may reduce the risk of posterior capsular opacification (PCO) particularly if the posterior surface of the optic remains in contact with the posterior wall of the capsular bag during all states of accommodation.
  • PCO posterior capsular opacification
  • the present IOLs are deformable for insertion into the mammalian eye through a relatively small incision, for example on the order of about 3.5 mm or less.
  • both the first and second lens portions of the optic, and/or the force transfer assembly, if present are all deformable for insertion through a small incision into the eye.
  • Such IOLs regain their original undeformed condition rapidly after being inserted into the mammalian eye.
  • the present optics may be made of any suitable materials of construction.
  • the present optics may be made of one or more polymeric materials employing techniques used in manufacturing conventional polymeric material IOLs.
  • the materials from which the present optics can be made include, without limitation, acrylic polymeric materials, silicone polymeric materials, and the like and combinations thereof. Although combinations of different polymeric materials may be employed, the present optics preferably are made of different polymeric materials of the same general chemical family.
  • the first lens portion of the optic may be made of one silicone polymeric material while the second lens portion is made of a different silicone polymeric material.
  • the first lens portion of the optic can be made of one acrylic polymeric material while the second lens portion is made of a different acrylic polymeric material.
  • the first lens portion and the second lens portion of the present optics preferably are made of compatible materials of construction, that is materials which can be used to produce an effective IOL which remains as an intact structure in the eye without significant deterioration for periods of time extending for at least about 20 or about 25 years or more.
  • the first lens portion of the present optics is made of a very low modulus silicone polymeric material, while the second portion is made of a higher modulus silicone polymeric material.
  • the first lens portion of the optic can be composed of a silicone polymeric elastomer with the following material properties:
  • Refractive index of at least about 1.37 or at least about 1.40 or higher Shore A hardness of about 0; and At least about 1000% elastic elongation.
  • the second lens portion of the present optics can be made of a different silicone elastomer with the following material properties :
  • Refractive index of at least about 1.40 or at least about 1.42 or higher;
  • Shore A hardness in a range of about 0 to about 30; and An elastic elongation higher than about 150%, preferably in a range of about 150% to about 400%.
  • the second lens portion can be made of widely varying materials. Examples include, without limitation, rigid and foldable acrylic polymeric materials, rigid and foldable non-acrylic polymeric materials, deformable or foldable silicone polymeric materials and the like and combinations thereof .
  • the second lens portion can be hydrophobic or hydrophilic.
  • the second lens portion is produced in a separate mold and then inserted into a mold into which is placed the monomeric or partially polymerized monomeric mixture of the first lens portion precursors .
  • the combination is then heated to elevated temperatures, for example on the order of about 40°C to about 100°C, and/or subjected to ultraviolet radiation and the composition combination is allowed to cure, preferably for about one hour to about 24 hours.
  • the material in the mold is then post-cured, preferably at a temperature in the range of about 70°C to about 130°C, and/or by being subjected to ultraviolet radiation for a period of time, preferably for about two hours to about 30 hours.
  • the mold is disassembled and the molded lens body or optic recovered.
  • the force transfer assembly if present, can be made or provided separately and then coupled to the optic or lens body, for example, in a mold in which the optic is cured or post-cured. Alternately, the force transfer assembly can be coupled to the lens body after the lens body is formed. Conventional techniques can be employed. For example, one or more recesses can be formed in the optic and the force transfer assembly can be secured to the optic by having an end placed in the recess, for example, in much the same manner in which a haptic or fixation member is secured to the optic of a conventional IOL.
  • the force transfer assembly can have any suitable configuration provided that such assembly is effective to at least partially transfer the force of the eye to the optic of the IOL.
  • the force transfer assembly preferably is more rigid or less flexible than the first lens portion of the optic. However, the force transfer assembly preferably is sufficiently deformable to be folded or otherwise deformed to pass through a small incision for insertion into the eye.
  • the force transfer assembly can be a single member substantially surrounding the optic, or can be a plurality, for example, about 2 or about 3 to about 4 or about 6, individual elements positioned around the peripheral edge of the optic.
  • the force transfer assembly can include at least one hinge to facilitate axial movement of the optic in response to the action of the eye, preferably the force transfer assembly does not include a hinge .
  • the force transfer assembly preferably is made of a material or materials which are compatible with the eye and with the other material or materials included in the IOL. Examples of materials which can be included in the present force transfer assemblies include, but are not limited to, polypropylene, silicone polymeric materials, acrylic polymeric materials including but not limited to polymethylmethacrylate (PMMA) , polyamides and the like and combinations thereof.
  • methods for inserting an IOL in an eye comprise providing an IOL in accordance with the present invention, as described herein.
  • the IOL is placed into the eye, for example in the capsular bag of the eye, using equipment and techniques which are conventional and well known in the art.
  • the IOL is placed in the eye so that the eye effectively cooperates with the IOL to provide accommodation as desired.
  • any incision in the eye is closed.
  • the IOL provides the wearer of the IOL with substantially effective accommodation. No further treatments or medications, for example, to paralyze the ciliary muscle, to facilitate fibrosis or otherwise influence the position of the IOL in the eye, are required.
  • the optic is deformed prior to being placed into the eye.
  • the IOL in cooperation with the eye, provides the mammal or human wearing the IOL with the desired accommodation. Any and all features described herein and combinations of such features are included within the scope of the present invention provided that the features of any such combinations are not mutually inconsistent.
  • FIG. 1 is a perspective view of an IOL in accordance with the present invention with the posterior face of the optic shown facing up;
  • Fig. 2 is a fragmentary sectional view of an eye in which the IOL of Fig. 1 has been implanted, with the lens being located in a resting position with the ciliary muscle of the eye in the relaxed state;
  • Fig. 3 is a fragmentary sectional view of an eye in which the IOL of Fig. 1 has been implanted, with the ciliary muscle of the eye in the contracted state;
  • Fig. 4 is a perspective view of an additional IOL in accordance with the present invention with the posterior face of the optic shown facing up;
  • Fig. 5 is a fragmentary sectional view of an eye in which the IOL of Fig. 4 has been implanted with the lens being located in a resting position with the ciliary muscle of the eye in the relaxed state
  • Fig. 6 is a fragmentary sectional view of an eye in which the IOL of Fig. 4 has been implanted, with the ciliary muscle of the eye in the contracted state.
  • an IOL according to the present invention, shown generally at 10, includes a lens body or optic 12.
  • This optic 12 includes a posterior lens portion 14 and an anterior lens portion 16.
  • the posterior lens portion 14 is made of an optically clear material with a refractive index of at least about 1.42, for example, about 1.48.
  • the posterior lens portion 14 can be either deformable or rigid.
  • the posterior lens portion 14 is sufficiently deformable so as to be foldable or otherwise deformed for insertion into the eye through a small incision, that is an incision in the eye smaller than the maximum, undeformed diameter of the optic 12.
  • the posterior lens portion 14 preferably is more rigid than is the anterior lens portion 16.
  • the anterior lens portion 16 is comprised of an optically clear material that is easily deformable when subjected to the action of the eye.
  • the anterior lens portion 16 can have substantially the same or a different, for example, somewhat reduced, higher refractive index relative to the refractive index of the posterior lens portion 14 of optic 12.
  • the posterior lens portion 14 and the anterior lens portion 16 preferably are comprised of materials from the same basic chemical family.
  • the anterior lens portion 16 may be comprised of low or very low modulus silicone polymeric material, while the posterior lens portion 14 can be comprised of a different silicone polymeric material .
  • the modulus of the silicone polymeric material making up the anterior lens portion 16 is, for example, no greater than about 20 psi.
  • the anterior lens portion 16 can be comprised of a hydrophilic acrylic polymeric material, while the posterior lens portion 14 can be made of relatively high refractive index, rigid or deformable (for insertion) acrylic polymeric material which can be either hydrophobic or hydrophilic.
  • One example of the materials used to produce the anterior lens portion 16 and the posterior lens portion 14 are as follows :
  • the present IOL 10 can be produced using conventional polymer processing techniques.
  • the present posterior lens portion 16 can be produced separately using conventional molding, for example, injection molding, techniques.
  • This lens portions 14 can then be used to produce optic 12 using conventional molding techniques, for example, insert molding techniques, together with the material used to produce the anterior lens portion 16.
  • the optical powers of the lens portions 14 and 16 may be controlled so as to satisfactorily address the needs of the patient in whose eye IOL 10 is inserted.
  • Each of the lens portions 14 and 16 can have a suitable optical power.
  • the posterior lens portion 14 has a baseline diopter power for distance vision.
  • the posterior lens portion 14 may be substantially monofocal, having a diopter power for distance vision. Providing the posterior lens portion with a diopter power for distance vision effectively allows the wearer of IOL 10 to see distant objects in focus with the IOL located in the eye in the unaccommodated state, that is in the resting state, as generally shown in Fig. 2.
  • the IOL 10 is sized to fit within the capsular bag 50 of the eye 40 so as to be reshapable in response to the action of the eye.
  • the IOL 10 should be sized to facilitate the movement and reshaping of the optic 12 in response to the action of the eye.
  • the optic 12 is too large, . the ciliary muscle 46 will be inhibited from effectively contracting/relaxing so that the amount of accommodating movement, e.g., reshaping, will be unduly restricted.
  • the optic 12 if the IOL 10 is too small, the optic 12 will be ineffective to focus light on the retina of the eye 40, may cause glare and/or may not cooperate with the eye to effect the desired amount of accommodation.
  • the optic 12 preferably has a diameter in the range of about 8 mm to amount 12 mm.
  • the IOL 10 can be inserted into the capsular bag 50 of the eye 40 using conventional equipment and techniques, for example, after the natural crystalline lens of the eye is removed, using a phacoemulsification technique.
  • the IOL 10 in the eye 40 is located so that the posterior surface 20 of the anterior lens portion 16 and ' the posterior surface 22 of the posterior lens portion 14 are in contact with the inner posterior wall 52 of the capsular bag 50.
  • the posterior surfaces 20 and 22 together make up the posterior face 24 of optic 12 which is in contact with the inner posterior wall 52 of the capsular bag 50.
  • This contact is substantially maintained regardless of the configuration of the optic 12 in the eye 40.
  • Such contact is effective in maintaining the structural integrity of the capsular bag 50 and, in addition, effectively inhibits the growth of cells from the capsular bag onto the optic, thereby at least inhibiting or reducing the severity of posterior capsular bag opacification (PCO) .
  • PCO posterior capsular bag opacification
  • the eye 40 for example, the zonules 48 and the ciliary muscle 46 of the eye, are effective to move or compress the capsular bag 50, thereby reshaping the optic 12.
  • some axial movement of optic 12 may occur in response to the action of the eye 40.
  • the eye 40 is believed to act on optic 12 as follows. With the ciliary muscle 46 fully relaxed, the tension of the zonules 48 causes the capsular bag 50 to increase in diameter which, in turn, causes optic 12 to become relatively thin. Such configuration of optic 12 provides effective distance vision to the eye 40. This configuration is at least generally illustrated in Fig. 2. With IOL 10 in the position as shown in Fig. 2, far away or distant objects are brought into focus. If a near object is to be viewed, the ciliary muscle 46 contracts or constricts. The capsular bag 50 compresses, reshaping the optic 12 included therein, as shown in Fig. 3.
  • This reshaping of the optic 12 causes the anterior face 30 of the anterior lens portion 16 to become more curved, thereby increasing the optical power of the optic 12.
  • This reshaping of optic 12 provides near focus accommodation to allow the near object to be viewed.
  • the present IOL 10 has the ability, in cooperation with the eye, to be reshaped to provide for both distance focus and near focus .
  • IOL 10 is such that the amount of accommodation achievable preferably is in the range of about 1 to about 4 or about 5 or about 6 diopters .
  • Figs. 4, 5 and 6 illustrate an additional IOL, shown generally at 110, in accordance with the present invention.
  • IOL 110 is structured and functions similarly to IOL 10.
  • Components of IOL 110 which correspond to components of IOL 10 are indicated by the same reference numerals increased by 100.
  • force transfer assembly 70 includes four identically structured transfer members 72 which extend radially outwardly from the proximal end 74, which is attached to optic 112, to an outer or distal end 76.
  • Each of the transfer members 72 has a substantially flat configuration and is made of an acrylic polymeric material which is deformable for insertion of the IOL 110 into the eye, yet is more rigid than the anterior lens portion 116 to facilitate the transfer of force from the eye 140 to the optic 112.
  • One particularly useful acrylic polymeric material for use as a material of construction of the members 72 is a polymeric composition produced from the following mixture of monomers:
  • the IOL 110 can be produced by injection molding the posterior lens portion 114 and transfer members 72 separately and then insert molding can be employed to form the combination of the posterior lens portion, the transfer members and the anterior lens portion 116.
  • the optic 112 preferably has a diameter in the range of about 3.5 mm to about 7 mm, and the IOL 110 has an overall maximum diameter, including the force transfer assembly 70 in the rest state, that is fully extended from the optic 112, in the range of about 8 mm to about 12 mm.
  • Insertion can be accomplished using conventional techniques, for example, after the natural lens of the eye has been removed.
  • the optic 112 is reshaped in response to the action of the eye, which includes ciliary muscles 146 and zonules 148, through force transfer assembly 70.
  • the posterior surface 122 of optic 112 remains in substantial contact with the inner posterior wall 152 of the capsular bag 150. Such contact inhibits the growth of cells from the capsular bag 150 onto optic 110 and inhibits PCO.
  • IOL 110 provides focus accommodation because of the reshaping of the optic 112, in much the same way as when optic 12 is reshaped, for example, by changing the curvature of anterior face 130.
  • optic 112 provides further accommodation because of the axial movement of optic 112.
  • optic 112 may provide additional or enhanced accommodation relative to optic 12.
  • the present invention provides accommodating IOLs which cooperate with the eye to achieve advantageous amounts, preferably enhanced amounts, of accommodation. Such accommodation, as described herein, is often increased, for example relative to previous accommodating IOLs. In the resting or unaccommodated state in the eye, the present IOLs advantageously are effective to provide distance vision.

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  • Health & Medical Sciences (AREA)
  • Ophthalmology & Optometry (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Prostheses (AREA)

Abstract

L'invention concerne une lentille intraoculaire (LIO) conçue pour l'oeil humain, comportant une optique qui focalise la lumière sur la rétine et, en coopération avec l'oeil, assure l'accommodation. Cet optique comprend une première partie qui bouge en réaction à l'activité oculaire; et une seconde partie fixée à la première et placée généralement derrière l'optique.
PCT/US2001/028144 2000-09-07 2001-09-06 Lentille intraoculaire avec partie lentille posterieure WO2002019949A2 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU2001288926A AU2001288926A1 (en) 2000-09-07 2001-09-06 Intraocular lens with a posterior lens portion

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US65666100A 2000-09-07 2000-09-07
US09/656,661 2000-09-07

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Publication Number Publication Date
WO2002019949A2 true WO2002019949A2 (fr) 2002-03-14
WO2002019949A3 WO2002019949A3 (fr) 2003-01-16

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Cited By (27)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2005027796A1 (fr) * 2003-09-12 2005-03-31 Advanced Medical Optics, Inc. Implants intraoculaires renfermant plusieurs systemes mecanistes
US7025783B2 (en) 2002-01-14 2006-04-11 Advanced Medical Optics, Inc. Accommodating intraocular lens with integral capsular bag ring
US7125422B2 (en) 2002-10-25 2006-10-24 Quest Vision Technology, Inc. Accommodating intraocular lens implant
JP2010500911A (ja) * 2006-08-15 2010-01-14 シー アンド シー ビジョン インターナショナル リミテッド マルチオキュラー眼内レンズシステム
US8043372B2 (en) 2008-10-14 2011-10-25 Abbott Medical Optics Inc. Intraocular lens and capsular ring
US8052752B2 (en) 2002-10-25 2011-11-08 Abbott Medical Optics Inc. Capsular intraocular lens implant having a refractive liquid therein
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US9039760B2 (en) 2006-12-29 2015-05-26 Abbott Medical Optics Inc. Pre-stressed haptic for accommodating intraocular lens
US9072599B2 (en) 2009-08-27 2015-07-07 Abbott Medical Optics Inc. Fixation of ophthalmic implants
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US8182531B2 (en) 2006-12-22 2012-05-22 Amo Groningen B.V. Accommodating intraocular lenses and associated systems, frames, and methods
US8496701B2 (en) 2006-12-22 2013-07-30 Amo Groningen B.V. Accommodating intraocular lenses and associated systems, frames, and methods
US9039760B2 (en) 2006-12-29 2015-05-26 Abbott Medical Optics Inc. Pre-stressed haptic for accommodating intraocular lens
US8465544B2 (en) 2006-12-29 2013-06-18 Abbott Medical Optics Inc. Accommodating intraocular lens
US8814934B2 (en) 2006-12-29 2014-08-26 Abbott Medical Optics Inc. Multifocal accommodating intraocular lens
US8062362B2 (en) 2006-12-29 2011-11-22 Abbott Medical Optics Inc. Accommodating intraocular lens
US9968441B2 (en) 2008-03-28 2018-05-15 Johnson & Johnson Surgical Vision, Inc. Intraocular lens having a haptic that includes a cap
US8043372B2 (en) 2008-10-14 2011-10-25 Abbott Medical Optics Inc. Intraocular lens and capsular ring
US8585759B2 (en) 2008-10-14 2013-11-19 Abbott Medical Optics Inc. Intraocular lens and capsular ring
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US9011532B2 (en) 2009-06-26 2015-04-21 Abbott Medical Optics Inc. Accommodating intraocular lenses
US8486142B2 (en) 2009-06-26 2013-07-16 Abbott Medical Optics Inc. Accommodating intraocular lenses
US10105215B2 (en) 2009-08-03 2018-10-23 Johnson & Johnson Surgical Vision, Inc. Intraocular lens and methods for providing accommodative vision
US8343217B2 (en) 2009-08-03 2013-01-01 Abbott Medical Optics Inc. Intraocular lens and methods for providing accommodative vision
US9603703B2 (en) 2009-08-03 2017-03-28 Abbott Medical Optics Inc. Intraocular lens and methods for providing accommodative vision
US9072599B2 (en) 2009-08-27 2015-07-07 Abbott Medical Optics Inc. Fixation of ophthalmic implants
WO2012045186A1 (fr) * 2010-10-06 2012-04-12 Eduard Anton Haefliger Implant de lentille intraoculaire
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RU2551348C2 (ru) * 2010-10-06 2015-05-20 Эдуард Антон ХЕФЛИГЕР Внутриглазной имплант хрусталика
US10722400B2 (en) 2011-09-12 2020-07-28 Amo Development, Llc Hybrid ophthalmic interface apparatus and method of interfacing a surgical laser with an eye
US9987125B2 (en) 2012-05-02 2018-06-05 Johnson & Johnson Surgical Vision, Inc. Intraocular lens with shape changing capability to provide enhanced accomodation and visual acuity
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
US8945215B2 (en) 2012-05-10 2015-02-03 Abbott Medical Optics Inc. Accommodating intraocular lens with a compressible inner structure
US11497399B2 (en) 2016-05-31 2022-11-15 Qura, Inc. Implantable intraocular pressure sensors and methods of use
US11707354B2 (en) 2017-09-11 2023-07-25 Amo Groningen B.V. Methods and apparatuses to increase intraocular lenses positional stability
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US11554009B2 (en) 2019-05-17 2023-01-17 Qura, Inc. Intraocular lenses with intraocular pressure sensors and methods of manufacture

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