Prosthesis (i.e. – artificial body members) – parts thereof – or ai – Eye prosthesis – Intraocular lens
Reexamination Certificate
2000-01-18
2002-08-06
Isabella, David J. (Department: 3738)
Prosthesis (i.e., artificial body members), parts thereof, or ai
Eye prosthesis
Intraocular lens
Reexamination Certificate
active
06428574
ABSTRACT:
TECHNICAL FIELD
The present invention relates to an intraocular lens for the correction of visual disorders.
BACKGROUND OF THE INVENTION
According to “Intraocular Lenses,” authored by Dr. David J. Apple, published by Williams and Wilkins, 1989, evidence of the concept of intraocular lenses dates back at least two centuries. An 18th century oculist named Tadini proposed the idea of a lens implant and even attempted the development of one. The first recorded implant was by Casaamata around 1795, which failed due to inadequate fixation of the implant to the surface of the eye. The first successful series of implants is credited to Dr. Harold Ridley of London. Ridley observed fragments of an acrylic plastic material used in World War II fighter canopies lodged in the eyes of fighter pilots he treated. Finding no biologic reaction, he chose to use this rigid material for his first intraocular lens implants. A clinical quality version of the material, polymethylmethacrylate (PMMA), more commonly known as Plexiglass, was fabricated by Rayners of London into the first synthetic intraocular lenses (IOL).
Inflammation was commonly observed as a major complication when these early lenses were used. Ridley, however, considered moderate postoperative inflammation to be beneficial because it created adhesions to affix the lens implant. Factors which contributed to the development of postoperative inflammation included residues on or in the lenses of the sterilizing compounds, disinfectants, polishing residues on or in the lenses of the sterilizing compounds, disinfectants, polishing compounds, or additives which were added to control polymerization, as well as rough or sharp edges, holes, or ridges on the intraocular lens itself. Poor lens design suppressed the growth of IOL's until the design improved and the market grew rapidly in the 1980's.
According to “Intraocular Lens Implantation” by Dr. Emanuel S. Rosen, et al., published by The C. V. Mosby Company, 1984, intraocular lens implant procedures are used primarily for the correction of cataracts, a disease that affects the clarity of the natural lens. For the lens of the eye to remain functional it must maintain its shape and transparency. The embryonic lens is formed by layers of epithelial cells that elongate, form a crystalline structure and become optically clear. This formation process slows down but continues throughout life. The process can be upset by a number of environmental insults including old age, chemical contamination or physical injury. Any of these can trigger the formation of crystalline structures that occur within the lens itself. The newly formed crystalline structures scatter light and destroy the transparency of the lens. In cataract treatment, the IOL replaces the natural lens.
Intraocular corrective lenses for the treatment of refractive errors is a logical evolution of the cataract replacement IOL technology. Corrective lenses (eyeglasses, contact lenses) have been the mainstay for the correction of visual acuity defects. Myopia (nearsightedness), hyperopia (farsightedness), astigmatism and presbyopia (loss of near vision due to factors such as natural lens inflexibility) can all be treated with eyeglasses and contact lenses. Phakic lenses are ones which are used in combination with, rather than in place of, the natural lens in the eye. However, the use of phakic IOLs has generally been unsuccessful due to design related issues that cause insult to the natural lens resulting in such complications as cataracts or abrasion of surrounding tissue.
Refractive surgery is an alternative for treatment of certain types of visual acuity defects. Radial keratotomy (RK) and photorefractive radial keratectomy (PRK) are useful in treating mild to moderate myopia of
6
diopters or less and have shown limited success in treating astigmatism. The effectiveness of these procedures is less predictable in patients with higher degrees of myopia and cannot be used to treat hyperopia or presbyopia. Neither procedure is without significant postoperative events. The hyperopic shift and corneal instability following radial keratotomy and the high incidence of postoperative corneal haze, halos and starbursts with PRK are well documented in the literature. Additionally, both procedures produce overcorrection (hyperopia) and undercorrection (residual myopia) in a significant number of patients. Laser intrastromal in situ keratomilieusis (LASIK) is a new refractive surgery procedure that, in an experienced surgeon's hands, can treat both low and high degrees of myopia, hyperopia and astigmatism. Preliminary data indicate that LASIK produces few postoperative visual events, postoperative vision stabilizes rapidly compared to RK and PRK, and LASIK does not appear to produce any residual weakening in endothelial structure.
The phakic IOL fills the gaps in refractive surgery treatment modalities for visual acuity defects of all types, including astigmatism and, potentially, presbyopia, assuming that the shortcomings, discussed above, can be dealt with effectively. Such lenses are indicated for any level of myopia or hyperopia, including correction beyond 6 diopters.
The basic concept of phakic IOLs was disclosed in U.S. Pat. No. 4,585,456, Blackmore, issued Apr. 29, 1986. Blackmore describes a phakic lens which is placed on the surface of the natural lens and centered by being held in the ciliary sulcus. This approach failed to provide safe and effective treatment due to such complications as insult to the natural lens causing cataracts, abrasion of the pigment of the iris causing angle closure glaucoma and pupilary block glaucoma caused by blocking the flow of the eye's aqueous fluid through the pupil. Fixation of the lens using the interaction of the haptics and the ends of the ciliary sulcus requires proper measurement of the eye and selection of the proper haptic size (diagonal dimension across the lens and haptic). Improper haptic size can result in decentration of the implanted lens which leads to improper vision. See also, Mazzocco, et al., Soft Implant Lenses in Cataract Surgery, Slack, Inc., 1986, p. 93, Model E (a phakic lens fitting in the ciliary sulcus). Several other corrective lens implants having stiffened or rigid haptics, such as those described in U.S. Pat. No. 5,258,025, Fedorov, et al., issued Nov. 2, 1993, and U.S. Pat. No. 5,078,742, Dahan, issued Jan. 7, 1992, can result in similar complications. These complications are documented by Fechner, et al., in the Journal of Cataract and Refractive Surgery, March, 1996, vol. 22, pp. 178-81. Fechner also makes the observation that a cataract can form where the intraocular lens is in contact with the natural lens. Sustained contact between the implanted lens and natural lens can insult the natural lens by starving it of oxygen or nutrients provided in the aqueous fluid of the eye resulting in formation of a cataract. See also, U.S. Pat. No. 4,769,035, Kelman, issued Sep. 6, 1988, which discloses a phakic intraocular lens which sits directly on the anterior surface of the natural lens.
PCT/SU88/00180, assigned to Mikrokhirurgiya Glaza, published Apr. 21, 1993, discloses an anterior chamber lens that also has proven to result in significant complications when used. This lens has a means for iris centration that requires the lens to protrude into the anterior chamber; a spool-shaped surface on the lens restricts the movement of the iris. This concept also limits the optical diameter of the lens. The design places all or part of the lens surface in the anterior chamber of the eye and the edges of the spool scatter light creating haloes in the patients vision even during periods of bright ambient light. Also, restricting the movement of the iris results in pigment abrasions and potential trauma to the iris. The maximum diameter or diagonal dimension measured across the optic and haptics is small (less than 10.5 mm) because it is not necessary for the haptics to be centered by the ciliary sulcus or the ciliary zonules since the spool-shaped edges of the optic bod
Rozakis George W.
Valunin Igor
Chattopadhyay Urmi
Frost Brown Todd LLC
Isabella David J.
Medennium, Inc.
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