WO2012154597A1 - Cristallin artificiel torique à tolérance - Google Patents

Cristallin artificiel torique à tolérance Download PDF

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Publication number
WO2012154597A1
WO2012154597A1 PCT/US2012/036639 US2012036639W WO2012154597A1 WO 2012154597 A1 WO2012154597 A1 WO 2012154597A1 US 2012036639 W US2012036639 W US 2012036639W WO 2012154597 A1 WO2012154597 A1 WO 2012154597A1
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WO
WIPO (PCT)
Prior art keywords
power
lens
error
axis
intraocular lens
Prior art date
Application number
PCT/US2012/036639
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English (en)
Inventor
Edwin J. Sarver
Original Assignee
Croma-Pharma Gmbh
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 Croma-Pharma Gmbh filed Critical Croma-Pharma Gmbh
Publication of WO2012154597A1 publication Critical patent/WO2012154597A1/fr

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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
    • A61F2/1637—Correcting aberrations caused by inhomogeneities; correcting intrinsic aberrations, e.g. of the cornea, of the surface of the natural lens, aspheric, cylindrical, toric lenses
    • A61F2/1645—Toric 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
    • 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
    • A61F2/1637—Correcting aberrations caused by inhomogeneities; correcting intrinsic aberrations, e.g. of the cornea, of the surface of the natural lens, aspheric, cylindrical, toric lenses
    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C7/00—Optical parts
    • G02C7/02—Lenses; Lens systems ; Methods of designing lenses
    • G02C7/04—Contact lenses for the eyes
    • 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
    • A61F2240/00—Manufacturing or designing of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2240/001—Designing or manufacturing processes

Definitions

  • the present invention relates to systems and methods for human vision correction, and to methods of designing a tolerant toric intraocular lens.
  • the design of a tolerant toric lens is accomplished by modifying the power profile of the standard toric intraocular lens.
  • the eye is a complex optical system that must be well corrected to provide its owner with a high quality of life.
  • the crystalline lens can acquire a cataract requiring surgical intervention to maintain good vision. This intervention includes the removal of the crystalline lens and replacing it with an intraocular lens (IOL).
  • IOL intraocular lens
  • TIOL toric IOL
  • the cornea has significant astigmatism
  • TIOL toric IOL
  • the TIOL is properly aligned with respect to its desired meridian, the patient's vision is usually good.
  • the TIOL can be aligned at the wrong meridian either due to an error at the time of surgery or due to a postoperative rotation of the TIOL. If this axis error is large enough, some type of correction must be made to provide the patient with good vision. This intervention could be a prescription for spectacles or contact lenses, or a rotation of the TIOL to the correct axis.
  • TIOLs that attempt to correct alignment errors that are caused by surgical axis misplacement or post surgical axial rotation of the TIOL focus on the pupilar area.
  • U.S. Patent Application Publication No. 201 1 /0166652 teaches the preparation of a TIOL that has a cylinder power and a depth of focus extender.
  • U.S. Patent Application Publication No. 201 1 /0170057 a TIOL is described that spatially divides the pupil into discrete zones, with each zone having a discrete astigmatism magnitude and orientation.
  • the designs of the TIOL depend largely on the size of the pupil.
  • the present invention seeks to overcome the shortcomings of the prior art TIOL designs by providing for a tolerant TIOL (TTIOL) and methods of designing a TTIOL, by modifying the Attorney Docket No.: 77032.000004 power profi le of the standard TIOL, thereby providing tolerance to axis alignment errors along the meridians, thereby mitigating axis alignment errors.
  • TTIOL tolerant TIOL
  • the present invention provides for an improved TIOL that corrects for the misalignment of such an implant.
  • the TIOL provides for forgiveness of or tolerance to axis alignment errors along the meridians.
  • the axis alignment forgiveness mitigates negative visual aspects of an axis alignment error.
  • the a TTIOL has aspheric components to reduce the lens' spherical aberrations.
  • the design of the TTIOL is applicable to corrective corneal surgical interventions, such as PRK or LASIK.
  • the present invention also provides for methods of surgical intervention comprising the i mplantation of the TTIOL.
  • the design of the TTIOL can be applied to the manufacture of other corrective ophthalmic devices including external lens, such as but not limited to contact lenses.
  • the modified TIOL produced results in a lens leading to a higher myopic power shift than a hyperopic power shift.
  • Figure 1 Power profiles for an aligned TIOL, aligned TTIOL, and TTIOL with a 10 degree axis error.
  • Figure 3 Image simulations for 10 degree axis error TTIOL (left) and TIOL (right) at object vergence of 0, 0.25, and 0.5 D.
  • the design of a TIOL can be improved to provide more forgiveness in axis alignment errors along the meridians. This improvement enhances a patient's quality of vision in the presence of an axis alignment error and reduces the incidence of complications resulting from surgical intervention, during surgery or post surgery, that may rotate a standard TIOL.
  • the design of the improved TIOL or TTIOL is also applicable to other ocular devices and interventions that may be subject to axis alignment errors such as, but not limited to, contact lenses or to corneal surgical interventions such as PRK Attorney Docket No.: 77032.000004 or LASIK. Additionally, the TTIOL may have an aspheric components that reduces the lens' spherical aberration.
  • the present invention therefore provides for systems and methods for eliminating or mitigating the optical effects of corneal astigmatism due to axis alignment errors by providing for the implantation or application of a TIOL.
  • the present invention also helps reduce overall spherical aberrations of the eye by not introducing additional positive spherical aberrations present in spherical refractive surfaces to the positive spherical aberration present in most human corneas.
  • the embodiments are illustrated primarily in connection with intraocular lenses. It should, however, be understood that these teachings apply equally to a variety of other ophthalmic lenses, such as contact lenses.
  • a lens that mitigates axis alignment errors is designed by modifying the power profile of a standard TIOL.
  • the TIOL designed according to one aspect of the invention is accomplished by first determining the standard power profile in each meridian of a standard toric lens according to (I)
  • a toric like optical element can be optimized to yield tolerance to axis alignment errors. This allows for the adjustment of the power profile of the meridians around the TTIOL.
  • Formula (II), below, provides the combination of a standard toric power profile and a meridian dependent power adjustment term.
  • a m represents the adjustable coefficients of the polynomi l.
  • the polynomial coefficients a m need to be determined in order to provide the desired axis error tolerance.
  • the error function, as determined by formula (III) is employed, to facilitate the determination of these coefficients
  • w(n) a positive-valued myopic error weight, wherein a value of > 1 is applied if L(n-k) >
  • b is > 0. In another embodiment of the present invention b is 2.
  • the discrete probability of an axis error of integer angle k can be described by p ⁇ k).
  • the polynomial coefficients a m in formula (II) can be determined.
  • the error function in (III) is minimized, thus improving performance of the TTIOL under the assumptions of the given probability of axis error p(k).
  • the meridians are given by integer values of degrees, however, by converting the units from angles in degrees to angles in radians the numerical stability of the optimization calculations is improved.
  • the present invention employs the premise that it is better to design a lens that leads to a myopic power profile shift as opposed to a hyperopic power profile shift in the presence of an axis alignment error. Patients, especially non-accommodating, will benefit from vision that is more myopic than hyperopic. If a patient requires a TIOL correction but the lens is implanted with an axis error, half the TIOL's meridians will have a power error in the positive direction (compared to the TIOL with no axis error) and the other half will have a power error in the negative direction.
  • the patient's meridian will be hyperopic by ⁇ diopters.
  • the TIOL provides a power of P + ⁇ diopters (wherein ⁇ > 0)
  • the patient's meridian will be myopic by ⁇ diopters.
  • the TTIOL is designed using the premise that it is better to decrease hyperopic error at the expense of increased myopic error.
  • those of skill in the art may apply a TTIOL with a 1 diopter cylinder power and an axis error of 10 degrees to the Formulas of (I)-(III) recited herein.
  • the lens will have a meridional power hyperopic error limited to the range of 0 to 0.09 diopter, while the myopic error is limited to the larger range of 0 to 0.26 diopter.
  • the lens will have meridional power hyperopic and myopic errors in the range of 0 to 0. 17 diopter.
  • the TTIOL with an axis error reduces the hyperopic error (compared to a standard TIOL with the same axis error) at the expense of increasing the myopic error. This tradeoff is beneficial for the patient as it provides improved vision quality.
  • the hyperopic and myopic error ranges for the TTIOL with a 1 0 degree axis error scale with the cylinder power of the TTIOL.
  • the TTIOL with a 1 diopter cylinder power and an axis error of 10 degrees is simply an application and example of one embodiment of the present invention, and is not intended to restrict the invention to the specific numerical parameters described. Accordingly, those of skill in the art wil l appreciated that the axis errors application will vary based on the cylinder power and the assignment of an axis error. Therefore, it will be understood by those of skill in the art that if for example there is a 2 diopter cylinder power and an axis error of 10 degrees, the hyperopic error may be in the range of 0 to 0.1 8 diopter, while the myopic error may be limited to the larger range of 0 to 0.52 diopter.
  • formulas (I)— (III) described herein will provide various other ranges for both hyperopic error as well as myopic error, with the understanding that the myopic error will always be larger than the hyperopic error. It will also be understood that the application of formulas (I)- (III) to other cylinder powers and axis orientation errors will provide various other hyperopic and myopic error ranges.
  • the TTIOL hyperopic error range could be reduced while the myopic error range is increased.
  • the TTIOL range of the hyperopic error range could be increased while the myopic error range is reduced.
  • axis errors may range from about 0 to about 30 degrees, with the understanding that the TTIOLs of the present invention will have benefits to axis errors that extend well below the 30 degree range, such as but not limited to axis errors ranging from about 30 degrees to about 90 degrees.
  • the present invention seeks to correct this issue by providing for a TIOL that compensates for the compression effects associated with implantation of a TIOL. From the above, those of skill in the art will recognize that by accounting for the axis alignment errors, an improved TIOL may be manufactured and used in a subject requiring ophthalmic interventions.
  • the TTIOL of the present invention may be designed using various known methods, such as but not limited to, optical computer aided design (CAD) system. These systems will take into account the calculations for determining the axis errors defined above and may be used to design TTIOLs, contact lens, or the like.
  • CAD optical computer aided design
  • a TTIOL can be produced in a computer-controlled manufacturing system.
  • the lens design can be converted into a data file containing control signals that is interpretably by a computer-controlled manufacturing device.
  • a computer-controlled manufacturing device is a device that can be controlled by a computer system and that is capable of producing directly an ophthalmic lens or an optical tool, such as a Attorney Docket No.: 77032.000004 mold, for producing an ophthalmic lens.
  • the TTIOLs of the present invention may also be manufactured through processes such as heating, physical stacking, and/or chemical bonding.
  • the TTIOL of the present invention may be produced by any convenient means, for example, such as lathing and molding. Curing of the TTIOL material may be carried out by any convenient method. For example, the material may be deposited within a mold and cured by thermal, irradiation, chemical, electromagnetic radiation curing and the like and combinations thereof. In another embodiments, molding is carried out using ultraviolet light or using the full spectrum of visible light. More specifically, the precise conditions suitable for curing the TTIOL material wi ll depend on the material selected and the lens to be formed. Suitable processes are disclosed in U.S. Pat. No. 5,540,410 incorporated herein in its entirety by reference.
  • the manufacturing process may also be accomplished by utilizing a lathe. Suitable lathe devices will allow free-form surfaces to be cut.
  • a typical lathe lens will comprise a header, a front surface, a back surface, and an edge.
  • the Header contains comments on the lens design. This may for example include the power profile of the lens, manufacture's identity, or any other appropriate marking.
  • the front surface is non-symmetric, and thus its surface points are provided in a dense spiral scan starting at the edge of the lens.
  • a scan is accomplished by scanning in a counter-clockwise direction, starting at one of the principal meridians moving from edge of the lens to the center of the lens.
  • the scanning may also include blend zone Bezier spline samples.
  • the back surface is symmetric, we can define it with a single profile, which i ncludes a back surface blend zone Bezier spline samples. This data starts at the edge and scans toward the center point of the back surface.
  • both the front and back surfaces of the TTIOL of the present invention may be toric surfaces.
  • only the back surface of the TTIOL is a toric surface.
  • the TTIOL may also comprise a multifocal portion that is integrated into the lens.
  • the edge section is also defined with a single profile similar to the back surface.
  • Custom programs can be developed for this purpose by those Attorney Docket No.: 77032.000004 ski l led in the art.
  • Those of skill in the art will appreciate that the haptics involved in the edge of the TT10L will i nclude edge thickness, edge blend zone, and edge design.
  • Edge thickness may be determined by numerous methods known to those of skill in the art.
  • the edge thickness may be determined by formula (IV).
  • Edge thickness (ET) may be computed by taking into consideration the conic shape of each meridian on the front surface, the optical zone diameter, the center thickness, and the back surface, in one embodiment, the £T is found using the smallest E calculated from each meridian. For meridian n, formula (IV) may be used to find the ET.
  • haptic designs may be utilized in the preparation of the TTIOL of the present invention. These may include those described in U.S. Patents Nos.: 4,71 8,905, 4,834,749, 5,306,297, 6,517,577, and 6,537,3 16, all of which are incorporated by reference in their entireties.
  • the edge blend zone is required to smoothly connect each front surface meridians to the edge of the optic. It is also required so that the back surface is smoothly blended to the edge using continuous derivatives. This is illustrated in Figure 5. Zero- and first- order continuous connections between the optical portion of the meridians and the edge of the lens are made by using Bezier splines. This is implemented using custom software readily available, known, and developed by those in the art.
  • the edge of the TTIOL is not perfectly square, instead it is rounded using Bezier splines.
  • a rounded edge eliminates bright spots in the periphery of the retina from light derived from off- Attorney Docket No.: 77032.000004 axis source, such as a street lamp at night.
  • the rounded edge is illustrated in Figure 5, which depicts a blending of the optical zone to the edge of the lens via Bezier spline.
  • a barrier shelf between the haptic and optic can be employed to help inhibit the possibi lity of posterior capsular opacification (PCO). This feature is easily incorporated in the haptic designed by those of skill in the art.
  • the materials used to make the TTIOL of the present invention may be standard materials generally known to one of skill in the art. Generally speaking, the materials may be either hard and/or soft materials. In one embodiment, soft TTIOL materials are obtained in dehydrated form to provide for easier processing and cutting on a lathe. Those of skil l in the art will understand that each batch of material should be provided with information pertaining to the hydrated index of refraction, axial swell factor, and transverse swell factor. The swell factors are critical to determine the "preshrink" on the surface points in the lathe files, such that after hydration, the TTIOL produced will achieve the correct shape and dimensions. It is known by one of skilled in the art that the swell factors can be adjusted so that the hydrated surface parameters can be adjusted on the lathe.
  • the materials used to manufacture the TIOLs may be pliable materials that allow for foldable insertion into the eye through small incisions. These pliable and softer TTIOLS, allow for compression, folding, rolling or other deformations. The softer TTIOLs may be deformed prior to insertion thereof through an incision in the cornea of an eye. Following insertion of the TTIOL in an eye, the TTIOL returns to its original pre-deformed shape due to the memory characteristics of the soft material. Softer, more flexible TTIOLs as just described may be implanted into an eye through an incision that is much smaller, i.e.
  • foldable intraocular TTIOL materials can generally be silicone materials, hydrogel materials, and non- hydrogel acrylic materials. Many materials in each category are known. See, for example, Foldable Intraocular Lenses, Ed. Martin et al., Slack Incorporated, Thorofare, N.J. (1993).
  • Suitable material used in the preparation of the TTIOLs may also be chosen from conventionally available materials having adequate elasticity and/or hardness.
  • the TTIOLs may be made from any suitable lens forming materials for manufacturing ophthalmic lenses including, without limitation, spectacle, contact, and Attorney Docket No.: 77032.000004 intraocular lenses.
  • Illustrative materials for the formation of foldable or compressible TTIOLs include, without limitation silicone elastomers, silicone-containing macromers including, without limitation, those disclosed in U.S. Pat. Nos.
  • hydrogels si licone-containing hydrogels, polymethyl methacrylate (PPM), hydroxymethyl methacrylate (HEMA), 6-hydroxyhexyl methacrylate (HOHEXMA) a polymer of those materials, acrylic polymers, polyesters, , polyamides, polyurethane, hydrocarbon and fluorocarbon polymers, fluori ne-containing polysi loxane elastomers, or the like and/or any combination thereof.
  • PPM polymethyl methacrylate
  • HEMA hydroxymethyl methacrylate
  • HOHEXMA 6-hydroxyhexyl methacrylate
  • the surface is a siloxane, or contains a siloxane functionality, including, without limitation, polydimethyl siloxane macromers, methacryloxypropyl polyalkyl siloxanes, and mixtures thereof, silicone hydrogel or a hydrogel.
  • the material used to manufacture the TTIOL of the present invention may be optically coated to transmit only a portion of the optical spectrum.
  • the TTIOL may have the capability to blocking particular spectrums of UV rays.
  • the TTIOL design concept may be applied to rigid ophthalmic devices such as those which sit intraocularly or externally to the eye.
  • rigid ophthalmic devices such as those which sit intraocularly or externally to the eye.
  • a larger incision is necessary because the TTIOL must be inserted through an incision in the cornea slightly larger than that of the diameter of the inflexible TTIOL optic portion.
  • the TTIOLs of the present invention reduce the incidence of axis error alignments normally associated with larger incisions.
  • the TTIOL concept may be applied to the manufacture of a contact lens.
  • the lens may be molded, for example, in contact lens molds i ncluding molding surfaces that replicate the contact lens surfaces when a lens is cast in the molds.
  • the TTIOL of the present invention may also be a hard or soft contact lense.
  • Soft contact lenses of the invention are preferably made from a soft contact lens material, such as a silicon hydro-gel or HEMA. It will be understood that any lens described above comprising any soft contact lens material would fall within the scope of the invention such that the power profiles of the toric power profiles of the contact lens will adopt the methodology for compensating for axis alignment errors.
  • the TTIOL of the present invention may be manufactured to any appropriate size.
  • the TTIOL is of a standard diameter and thickness.
  • the optical zone of the TTIOL may range from about 4 mm to about 8 mm in diameter.
  • the optical zone diameter of the TTIOL is about 6 mm.
  • the thickness of the TTIOL at the center may range from about 0.2 mm to about 1.2 mm in thickness. In one embodiment, the thickness at the center of the TTIOL is 1 mm.
  • the TTIOL of the present invention may also be used, following removal of the crystalline lens, for the treatment of any ocular disease or condition requiring a change of focus or lens replacement.
  • the TTIOL is particularly useful for treatment of age-related macular degeneration (AMD), cataracts, astigmatism, myopia, hyperopia, presbyopia, or any other refractory error.
  • AMD age-related macular degeneration
  • cataracts cataracts, astigmatism, myopia, hyperopia, presbyopia, or any other refractory error.
  • the TTIOLs are designed to correct, amongst other diseases, preexisti ng corneal astigmatism.
  • TTIOLs are commonly implanted in the capsular bag after the cataractous lens is removed. TTIOLs must remain in a specific orientation within the eye in order to achieve the designed correction. Rotation after implantation is a significant concern with TTIOLs. See, for example, Sun et. al ., Ophthalmology, 107(9): 1776- 1782 (2000); Patel et al., Ophthalmology, 106( 1 1 ):2190-2196 ( 1999); Nguyen, et al., J. Cataract Refract.
  • the present invention seeks to correct this misalignment issue by designing a TTIOL capable of compensating for the misalignment that can occur after surgery.
  • the TTIOLs may be implanted using the convention methodologies employed by ophthalmic surgeons in the replacement of the lens during cataract surgery.
  • a small incision is made in the cornea, e.g., by utilizing a diamond blade.
  • An instrument is then inserted through the corneal incision to cut a portion of the anterior lens capsule, typically in a circular fashion, to provide access to the opacified natural lens.
  • An ultrasound or a laser probe is then employed to break up the lens, and the resulti ng lens fragments are aspirated.
  • a TTIOL can then be inserted into the capsular bag, e.g., by employing an injector. Once inside the eye, the TTIOL unfolds to replace Attorney Docket No.: 77032.000004 the natural lens.
  • the corneal incision is typically sufficiently small such that it heals without the need for sutures.
  • the i ncision caused by the surgical intervention may induce corneal aberrations including astigmatism or modify pre-existing corneal aberrations including astigmatism.
  • methods of designing a TTIOL are disclosed that allow the TTIOL to compensate for such surgically-induced corneal astigmatism.
  • FIG. 1 A normalized graph of the power profiles for meridians 1 to 180 are shown in Figure I .
  • the graph is normalized so that the y-axis has a peak of 1 (meaning full cylinder power of 3 diopters in this example).
  • Power profiles for an aligned TIOL, aligned TTIOL of the present invention, and TTIOL of the present invention with a 10 degree axis error are shown in Figure I .
  • the graph is normalized so that the y-axis has a peak of 1 (meaning full cylinder power of 3 diopters in this example).
  • Power profiles for an aligned TIOL, aligned TTIOL of the present invention, and TTIOL of the present invention with a 10 degree axis error Attorney Docket No.: 77032.000004
  • the TTIOL of the present invention profile with a 10 degree error has a small portion of the curve, (i.e., the area is on the left side of the curve) with larger power than the corresponding centered TIOL (i.e., standard TIOL).
  • This is achieved by making the TTIOL power profile a little lower and narrower than the TIOL profile.
  • a shift in a standard TIOL profile by 1 0 degrees would yield, a symmetric. In other words, half of the curve would be above the centered TIOL profile and the other half would be below, and by the same amounts.
  • the difference for the centered standard TIOL and TTIOL of the present invention are clinically the same (only about 0. 1 diopters difference).
  • the point spread functions (PSFs) for the TTIOL of the present invention with a 10 degree axis error and standard TIOL are shown in Figure 2 for object vergences of 0, 0.25, and 0.5 diopters. Over this range, the TTIOL of the present invention produced better visual performance since none of its power axes correspond to hyperopia.
  • the corresponding image simulations are given in Figure 3, where the superior performance of the TTIOL of the present invention can be seen.
  • Figure 2 depicts PSFs of 10 degree axis error TTIOL (left) and standard TIOL (right) at object vergences of 0, 0.25, and 0.5 diopters.
  • Figure 3 depicts image simulations for 10 degree axis error TTIOL of the present invention (left) and the standard TIOL (right) at object vergence of 0, 0.25, and 0.5 diopters.
  • the power of the back surface of the lens is given by one-half the mean power of the lens, according to formula (V).
  • the back surface power P2 is given in (VI).
  • s is the distance from the optical axis
  • r is the apical radius of curvature
  • K is the conic constant
  • z is the surface sag.
  • the radius of curvature r, and conic constant A ' for the back surface of the TTIOL are determined.
  • a similar operation for each meridian on the front surface of the TTIOL to find the radius and conic constant for each meridian is performed.

Abstract

La présente invention concerne un procédé de conception de cristallin artificiel torique, présentant un certain degré de tolérance à une erreur d'alignement des axes de façon à ce que les aspects négatifs d'une erreur d'alignement des axes soient atténués en créant un cristallin artificiel torique à tolérance. Les avantages de l'invention sont présentés dans la description et les figures associées, certains modes de réalisation de l'invention étant indiqués à titre d'exemple.
PCT/US2012/036639 2011-05-06 2012-05-04 Cristallin artificiel torique à tolérance WO2012154597A1 (fr)

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US9195074B2 (en) 2012-04-05 2015-11-24 Brien Holden Vision Institute Lenses, devices and methods for ocular refractive error
US9201250B2 (en) 2012-10-17 2015-12-01 Brien Holden Vision Institute Lenses, devices, methods and systems for refractive error
US9541773B2 (en) 2012-10-17 2017-01-10 Brien Holden Vision Institute Lenses, devices, methods and systems for refractive error
IT201600097763A1 (it) * 2016-09-29 2018-03-29 Sifi Medtech Srl Lente per astigmatismo
CN110123488A (zh) * 2019-05-27 2019-08-16 中国计量科学研究院 人工晶状体屈光度校验镜片及定值方法
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US10739227B2 (en) 2017-03-23 2020-08-11 Johnson & Johnson Surgical Vision, Inc. Methods and systems for measuring image quality
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US11013594B2 (en) 2016-10-25 2021-05-25 Amo Groningen B.V. Realistic eye models to design and evaluate intraocular lenses for a large field of view
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Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5570143A (en) * 1991-08-09 1996-10-29 Capricornia Contact Lens Pty. Ltd. Toric lens with axis mislocation latitude
US6533416B1 (en) * 2001-07-20 2003-03-18 Ocular Sciences, Inc. Contact or intraocular lens and method for its preparation
US20030060880A1 (en) * 1994-04-08 2003-03-27 Vladimir Feingold Toric intraocular lens
US20040237971A1 (en) * 2003-06-02 2004-12-02 Hema Radhakrishnan Methods and apparatuses for controlling optical aberrations to alter modulation transfer functions
US20090122264A1 (en) * 2007-10-26 2009-05-14 Institute For Eye Research Limited Methods and Apparatuses for Enhancing Peripheral Vision
US20090323020A1 (en) * 2008-02-21 2009-12-31 Abbott Medical Optics Inc. Toric intraocular lens with modified power characteristics

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5570143A (en) * 1991-08-09 1996-10-29 Capricornia Contact Lens Pty. Ltd. Toric lens with axis mislocation latitude
US20030060880A1 (en) * 1994-04-08 2003-03-27 Vladimir Feingold Toric intraocular lens
US6533416B1 (en) * 2001-07-20 2003-03-18 Ocular Sciences, Inc. Contact or intraocular lens and method for its preparation
US20040237971A1 (en) * 2003-06-02 2004-12-02 Hema Radhakrishnan Methods and apparatuses for controlling optical aberrations to alter modulation transfer functions
US20090122264A1 (en) * 2007-10-26 2009-05-14 Institute For Eye Research Limited Methods and Apparatuses for Enhancing Peripheral Vision
US20090323020A1 (en) * 2008-02-21 2009-12-31 Abbott Medical Optics Inc. Toric intraocular lens with modified power characteristics

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
MEISTER ET AL.: "Introduction to Ophthalmic Optics.", CARL ZEISS VISION., May 2008 (2008-05-01), pages 47 - 48, Retrieved from the Internet <URL:http://www.opticampus.com/files/introductiontoophthalmiçoptics.pdf> [retrieved on 20120731] *

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