WO2012138426A2 - Dispositif ophtalmique implantable avec une pluralité d'ouvertures statiques - Google Patents

Dispositif ophtalmique implantable avec une pluralité d'ouvertures statiques Download PDF

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Publication number
WO2012138426A2
WO2012138426A2 PCT/US2012/025922 US2012025922W WO2012138426A2 WO 2012138426 A2 WO2012138426 A2 WO 2012138426A2 US 2012025922 W US2012025922 W US 2012025922W WO 2012138426 A2 WO2012138426 A2 WO 2012138426A2
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WO
WIPO (PCT)
Prior art keywords
static
ophthalmic device
implantable ophthalmic
apertures
image
Prior art date
Application number
PCT/US2012/025922
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English (en)
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WO2012138426A3 (fr
Inventor
Rudy Mazzocchi
Amitava Gupta
Ronald Blum
Original Assignee
Elenza, Inc.
Pixeloptics, 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.)
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Publication date
Application filed by Elenza, Inc., Pixeloptics, Inc. filed Critical Elenza, Inc.
Publication of WO2012138426A2 publication Critical patent/WO2012138426A2/fr
Publication of WO2012138426A3 publication Critical patent/WO2012138426A3/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
    • A61F2/1648—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
    • A61F2/15—Implant having one or more holes, e.g. for nutrient transport, for facilitating handling
    • 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
    • A61F2002/16965—Lens includes ultraviolet absorber
    • A61F2002/1699—Additional features not otherwise provided for

Definitions

  • FIG. 1 shows a cross section of a healthy human eye 100.
  • the white portion of the eye is known as the sclera 110 and is covered with a clear membrane known as the conjunctiva 120.
  • the central, transparent portion of the eye that provides most of the eye's optical power is the cornea 130.
  • the iris 140 which is the pigmented portion of the eye and forms the pupil 150.
  • the sphincter muscles constrict the pupil 150 and the dilator muscles dilate the pupil 150.
  • the pupil 150 is the natural aperture of the eye 100.
  • the anterior chamber 160 is the fluid-filled space between the iris and the innermost surface of the cornea 130.
  • the crystalline lens 170 is held in the lens capsule 175 and provides the remainder of the eye's optical power.
  • the retina 190 which is separated from the back surface of the iris 140 by the posterior chamber 180, acts as the "image plane" of the eye 100 and is connected to the optic nerve 195, which conveys visual information to the brain.
  • a healthy eye can produce an image on the retina of an object in an object plane.
  • Objects in or near the object plane yield crisp, or focused images, whereas objects that are too far from the object plane appear blurry or out of focus.
  • the distance in front of and behind the object plane over which an object appears to be in focus on the image plane is called the "depth of field” and depends on both the eye's focal length (optical power) and aperture size.
  • a healthy eye can change its optical power (and its depth of field) to image objects at near distances (e.g., less than 1 m), intermediate distances (e.g., about 1 m to about 5 m), and far distances (e.g., more than about 5 m) to the front surface of the retina 190 in a process known as accommodation.
  • near distances e.g., less than 1 m
  • intermediate distances e.g., about 1 m to about 5 m
  • far distances e.g., more than about 5 m
  • accommodation There are two major conditions that affect an individual's ability to focus on near and intermediate distance objects: presbyopia and pseudophakia.
  • Presbyopia is the loss of accommodation of the crystalline lens of the human eye that often accompanies aging. In a presbyopic individual, this loss of accommodation first results in an inability to focus on near distance objects and later results in an inability to focus on intermediate distance objects. It is estimated that there are approximately 90 million to 100
  • the standard tools for correcting presbyopia are reading glasses, multifocal ophthalmic lenses, and contact lenses fit to provide monovision.
  • Reading glasses have a single optical power for correcting near distance focusing problems.
  • a multifocal lens is a lens that has more than one focal length (i.e., optical power) for correcting focusing problems across a range of distances.
  • Multifocal optics are used in eyeglasses, contact lenses, and intraocular lenses (IOLs).
  • Multifocal ophthalmic lenses work by means of a division of the lens's area into regions of different optical powers.
  • Multifocal lenses may be comprised of continuous surfaces that create continuous optical power as in a Progressive Addition Lens (PAL).
  • PAL Progressive Addition Lens
  • multifocal lenses may be comprised of discontinuous surfaces that create discontinuous optical power as in bifocals or trifocals.
  • Contact lenses fit to provide monovision are two contact lenses having different optical powers. One contact lens is for correcting mostly far distance focusing problems and the other contact lens is for correcting mostly near distance focusing problems.
  • Pseudophakia is the replacement of the crystalline lens of the eye with an IOL, usually following surgical removal of the crystalline lens during cataract surgery. For all practical purposes, an individual will get cataracts if he or she lives long enough.
  • Aphakia which is the absence of the crystalline lens, can be corrected using IOLs.
  • IOLs are monofocal spherical lenses that provide focused retinal images for far objects (e.g., objects over two meters away).
  • the focal length (or optical power) of a spherical IOL is chosen based on viewing a far object that subtends a small angle (e.g., about seven degrees) at the fovea.
  • Typical patients require spherical IOLs with optical powers between about +10 diopters (D) and about + 36 D. The most commonly required optical power is about +25 D or about +26 D.
  • D diopters
  • +36 D The most commonly required optical power is about +25 D or about +26 D.
  • all spherical surfaces, including spherical IOLs and the cornea suffer from spherical aberration, which limits image quality.
  • aspheric IOLs can be used to treat presbyopia and aphakia without introducing spherical aberration.
  • aspheric IOLs with constant negative spherical aberration can even be used to compensate spherical aberration introduced in the cornea.
  • these conventional aspheric IOLs provide better images for a wider range of far object scenarios than spherical IOLs, conventional aspheric IOLs do not improve image quality for near or intermediate objects. It has always been always accepted that patients with aspheric IOLs would wear glasses to see near and intermediate objects.
  • IOLs can result in one or more of: light scattering, glare, halos, ghosting, loss of contrast sensitivity, limited range of focus, and/or reduction of light hitting the retina.
  • An alternate approach to correcting presbyopia involves a implanting a corneal inlay with a small, fixed-diameter aperture in the eye.
  • limiting the diameter of the aperture of an optical system, such as the eye increases the system's depth of field.
  • the aperture increases the depth of field by blocking or attenuating at least some of the light rays that make a large angle with the lens's optical axis (i.e., the aperture blocks some of the non-paraxial light rays).
  • the aperture By blocking or attenuating some of the non- paraxial light rays, the aperture reduces the deviation of rays from the image plane, causing objects located within a fixed distance of the focal distance (i.e., within the depth of field) to appear in focus. Increasing the depth of field makes the sharpness decrease more gradually on either side of the focal plane.
  • a corneal inlay with a properly chosen aperture diameter may extend the depth of field to make near and intermediate objects appear in focus.
  • an implantable ophthalmic device (and associated methods of imaging with an implantable ophthalmic device) that includes an opaque structure and a plurality of prismatic elements.
  • the opaque structure defines a plurality of static apertures, each of which is in optical communication with a corresponding prismatic element in the plurality of prismatic elements.
  • One or more of the static apertures may be apodized, e.g., according to an apodization function that defines how the transmissivity of the static aperture varies as a function of position from the center of the static aperture.
  • the static apertures may have the same apodization function or a different apodization function.
  • the static apertures cover at least about 50% (e.g., 80% or 90%) of the implantable ophthalmic device's clear aperture, or effective size when implanted. They may be arranged in a regular array (e.g., a pattern having both short- and long-range order) or in an irregular array (e.g., a pattern that may have short-range order but not long- range order). In some cases, the irregular array may be a randomized array. [0014] One or more of the static apertures may be in the shape of a triangle, quadrilateral, hexagon, dodecagon, or circle.
  • the static apertures may all be the same shape (e.g., circles), or they may be different shapes (e.g., dodecagons and squares).
  • One or more of the static apertures may have a maximum transverse dimension (e.g., a diameter for a circle) of about 100 microns to about 2.0 millimeters.
  • the opaque structure may define the thickness of one or more static apertures to be about 10 microns to about 500 microns.
  • each prismatic element may include a surface whose gradient forms an angle with an optical axis of the implantable ophthalmic device. Each gradient may be oriented along a radius extending from the optical axis of the implantable ophthalmic device.
  • the plurality of prismatic elements may include a first prismatic element with a first prism angle and a second prismatic element with a second prism angle that is greater than the first prism angle. The second prismatic element may be located farther from the optical axis of the implantable ophthalmic device than the first element.
  • the implantable ophthalmic device may also include a lens in optical
  • the plurality of static apertures and the plurality of prismatic elements may increase the lens's optical power by about 1.0 Diopters to about 3.0 Diopters. They may also increase the lens's depth of field by about 0.5 Diopters to about 3.0 Diopters.
  • the implantable ophthalmic device may also include a plurality of microlenses, each of which is in optical communication with a corresponding static aperture in the plurality of static apertures.
  • an exemplary implantable ophthalmic device may include a plurality of optical elements, each of which is in optical communication with a corresponding static aperture in the plurality of static apertures.
  • Each optical element may be thick enough to compensate for a phase mismatch among two or beams transmitted through two or more static apertures in the plurality of static apertures.
  • the implantable ophthalmic device includes a plurality of static apertures, which, when implanted in the eye, produce a plurality of second image beams from a first image beam.
  • the implantable ophthalmic device also includes a plurality of prismatic elements, which, when implanted in the eye, refract each second image beam towards the center of the retina to form a single retinal image. In refracting each second image beam, the plurality of prismatic elements may form a third image beam that has a smaller divergence angle than the first image beam so as to increase the depth of field of the eye.
  • Each static aperture may be further configured to attenuate light according to an apodization function.
  • the device may also include at least one lens (e.g., a microlens) to focus at least one second image beam in the plurality of second image beams.
  • the device may also include an optical element that is configured to shift a phase of at least one second image beam to compensate for phase mismatch among two or more of the second image beams.
  • FIG. 1 is a cross section of a healthy human eye.
  • FIG. 2 is a perspective view of an exemplary implantable ophthalmic device.
  • FIGS. 3A-3E are plan views of implantable ophthalmic devices with different arrangements of static apertures.
  • FIG. 3F is a cross section of an implantable ophthalmic device that includes a plurality of microlenses in optical communication with the static apertures.
  • FIG. 3G is a cross section of an implantable ophthalmic device that includes a plurality of optical elements in optical communication with the static apertures.
  • FIGS. 4A ⁇ tC are plots of apodization functions for static apertures in exemplary implantable ophthalmic devices.
  • FIGS. 5 A and 5B are diagrams that illustrate intraocular imaging with a monofocal lens (FIG. 5 A) and an exemplary implantable ophthalmic device (FIG. 5B).
  • FIG. 2 is a perspective view of an exemplary implantable ophthalmic device 200 that can be used to increase the depth of field in a presbyopic patient or to replace the crystalline lens in an aphakic patient.
  • the device 200 includes an opaque structure 210 that defines two or more apertures 212 whose shape, size, and position are fixed.
  • the opaque structure 210 (and static apertures 212) can be formed in any number of suitable ways.
  • the static apertures 212 may be punched into or etched out of a sheet or film of biocompatible material, such as polyvinyldene fluoride or non-hydrogel microporous perflouroether, that blocks or severely attenuates light at visible wavelengths (i.e., from about 450 nm to about 700 nm).
  • biocompatible material such as polyvinyldene fluoride or non-hydrogel microporous perflouroether
  • the film or sheet may be of uniform thickness (e.g., of about 10 microns to about 500 microns), or it may be of varying thickness (e.g., thicker in the center and thinner on the edges). The thickness may be chosen to increase or reduce vignetting by one or more of the apertures 212.
  • the resulting opaque structure 210 scan be embedded in plastic (e.g., acrylic, polyimide, PMMA, PVDF, or any other suitable polymer or fluorocarbon) or glass (e.g., BK7), sandwiched between transparent substrates, or adhered to a transparent substrate to form part of the device 200.
  • the device 200 can also be coated (e.g., with SiO x ) to prevent material from escaping into the eye.
  • the opaque structure 210 can also be etched or burned into or onto a transparent substrate.
  • the opaque structure 210 may be burned into a piece of glass or plastic with femtosecond laser pulses focused to the piece's surface or its interior or etched into the piece's surface using a suitable lithographic or etching technique. Etching or burning could be used to create apertures 212 at different depths within a substrate or to create apertures 212 of different thicknesses (e.g., from about 10 microns thick to about 500 microns thick).
  • the static apertures 212 may cover 50%, 80%, 90%, or more of the implantable ophthalmic device's clear aperture, which is the area through which light can pass when the device 200 is implanted in an eye.
  • Each static aperture 212 may be in the shape of a triangle (e.g., like apertures 212"' in FIG. 3D), quadrilateral (e.g., a parallelogram, rectangle, or square), hexagon, dodecagon, circle, or any other suitable shape, including both regular and irregular shapes. They can also be in the shape of concentric rings (i.e., annularly shaped), e.g., as in the device 200' with apertures 212' shown in FIG. 3A.
  • Each aperture 212 may have a maximum transverse dimension (diameter) of about 100 microns to about 2.0 millimeters.
  • a single device 200 may include apertures 212 of only single shape or of a variety of shapes; likewise, a single device 100 may include apertures 212 of only single size (transverse dimension) or of a variety of sizes (e.g., like apertures 212" in FIG. 3C).
  • the static apertures 212 can be arranged in a regular array as in the devices 200", 200"', and 200"" of FIGS. 3B, 3C, and 3D, respectively. For instance, they may be tiled in tessellated pattern.
  • the static apertures 212 can be arranged in an irregular array, such as a sparse array or an array in which the apertures are arranged in a random or semi-random manner, as shown in FIG. 3E.
  • the implantable ophthalmic device 100 also includes one or more prismatic elements 220a-220n (collectively, prismatic elements 220), each of which is in optical communication with a corresponding static aperture 212. That is, there is at least one ray path that intersects the principal planes of a given static aperture 212 and the corresponding prismatic element 220.
  • FIG. 2 shows a one-to-one correspondence between static apertures 210 and prismatic elements 220, other devices may include more static apertures 210 than prismatic elements 220 or vice versa.
  • a single aperture 212 may be in optical communication with more than one prismatic element 220, and a prismatic element 220 may be in optical communication with more than one single aperture 212.
  • the prismatic elements 220 may be selected and arranged to correct for any lateral shift in the image location induced by the corresponding static aperture 212.
  • FIG. 2 shows that each prismatic element 220 has a corresponding surface 222 in the principal ray's path.
  • FIG. 2 shows planar surfaces 222
  • other implantable ophthalmic devices may include one or more prismatic elements with warped or stepped surfaces.
  • Each surface 222 can be characterized by a gradient 224, or line of steepest descent, whose slope depends on the prism angle of the prismatic element 220.
  • each prismatic element 220 is oriented such that, when the device 200 is viewed along its optical axis, its gradient 224 appears to radiate from the optical axis.
  • each gradient 224 is co-planar with a radius that extends perpendicularly from the optical axis.
  • the prismatic elements 220 may have gradients 224 of the same slope (prism angle) or of different slopes (prism angles) when viewed along a cross section of the device 200 (e.g., as shown in FIG. 5B). Each prismatic element 220 may have a prism angle of about 1 degree to about 75 degrees (e.g., 15 degrees, 30 degrees, 45 degrees, 60 degrees, or any other value between 1 and 75 degrees). If the gradients 224 are of different slopes, the prismatic elements 220 may be arranged according to increasing slope (prism angle) and distance from the device's optical axis.
  • prismatic elements 220 with smaller prism angles may be disposed closer to the optical axis, and prismatic elements 220 with larger prism angles (slopes) may be disposed farther from the optical axis.
  • the prismatic elements 220 may appear to form a Fresnel phase plate.
  • the prismatic elements 220 may be formed from glass (e.g., BK7), plastic (e.g., acrylic, polyimide, PMMA, PVDF, or any other suitable polymer or fluorocarbon), or any other suitable biocompatible material that is substantially transparent and has suitable dispersion characteristics at visible wavelengths.
  • Each element 220 may be about 100 microns to about 2.0 millimeters wide (e.g., about 1.0 millimeters).
  • the prismatic elements 220 may have the same or different refractive indices, which may be about 1.45 to about 1.80 (e.g., about 1.51 to about 1.67), or dispersion characteristics characterized by Abbe number of 25 and above (e.g., 30, 40, 50, 60, 100).
  • the prismatic elements 220 may be formed as individual pieces, groups of pieces, or as a single piece by injection molding, grinding, polishing, or any other suitable method. They can also be formed by selectively melting or nonlinearly altering regions within a transparent substrate, e.g., with focused or shaped pulses of light from a pulsed laser. For a device 200 where the prismatic elements 220 and the opaque structure 210 are separate pieces, the prismatic elements 220 may be bonded to the opaque structure 210 using a suitable adhesive (e.g., a UV-curable adhesive) or any other suitable bonding method.
  • a suitable adhesive e.g., a UV-curable adhesive
  • the implantable ophthalmic device 200 may also include a transparent element 230 that encapsulates the opaque structure 210 and the prismatic elements 220.
  • the transparent element 230 may be formed of two or more individual pieces that are bonded or sealed together around the opaque structure 210, the prismatic elements 220, or both.
  • the transparent element 230 is a single piece that bonds to or mates with the opaque structure 210, the prismatic elements 220, or both.
  • the opaque structure 210, the prismatic elements 220, or both are etched, burned, or melted into or onto the transparent element 230.
  • a suitable transparent element 230 may be made of glass, plastic, or any other suitable biocompatible material, such as a hydrophobic acrylic elastomer of glass with a transition temperature in the range of about 0° C to about 20° C (e.g., about 5° C to 10° C), that is substantially transparent at visible wavelengths.
  • the transparent element's refractive index is lower than that of the prismatic elements 220.
  • the transparent element 230 may have no optical power of its own, or it may have static optical power thanks to one or more curved surfaces or a graded index (GRIN) profile.
  • the transparent element 230 may be a planoconvex or biconvex lens with an optical power of between about 1.0 Diopters and about 36.0 Diopters (e.g., 20 Diopters, 25 Diopters, 30 Diopters, 35 Diopters, or any other value between 1.0 Diopters and 36.0 Diopters.
  • the static apertures 210 and the prismatic elements 220 may be configured to increase the lens's optical power by about 1.0 Diopters to about 3.0 Diopters (e.g., 1.5 Diopters, 2.0 Diopters, 2.5 Diopters, or any other value between 0.5 Diopters to about 3.0 Diopters) and its depth of field by about 0.5 Diopters to about 3.0 Diopters (e.g., 1.0
  • FIG. 3F shows an implantable ophthalmic device 202 that includes one or more microlenses 240, each of which is in optical communication with a corresponding static aperture 220.
  • Each microlens 240 may be an individual piece disposed within a
  • the microlenses 240 may also be formed as an array that is mated or bonded to the opaque structure 210 such that each microlens 240 aligns with a corresponding static aperture 220.
  • the size (diameter) of each microlens 240 may about 50 microns to about 2.0 millimeters (e.g., about 100 microns to about 1.5 millimeters).
  • the opaque structure 210 may be deposited or disposed between
  • microlenses 240 in a microlens array may all have the same focal length, or they may have different focal lengths.
  • the microlens focal length may depend on each microlens's position with respect to the device's optical axis.
  • FIG. 3G shows an implantable ophthalmic device 204 that includes one or more optical elements 250.
  • the optical elements 250 can be formed, mated, and aligned in the same fashions as the microlenses described above.
  • Each optical element 250 is in optical communication with a corresponding static aperture and is made of a transparent material, such as glass or plastic, whose refractive index is different that the refractive index of the surrounding material (e.g., air, vacuum, microlens material, or substrate material).
  • the refractive index and thickness of each optical element 250 may be chosen to compensate for a phase mismatch among two or beams transmitted through two or more of the static apertures 212 in the device. For a static aperture 212 that is filled with air or vacuum, phase mismatch can be compensated by selecting the thickness of the static aperture 212 to achieve the desired the optical path length.
  • Each static aperture may be apodized according to a particular apodization function whose amplitude varies smoothly from the static aperture's center to its edge.
  • Each static aperture may be perfectly transmissive (or nearly perfectly transmissive) over a central region and perfectly opaque (or nearly perfectly opaque) at its edge.
  • the opaque structure may include or define a boundary region that extends from the static aperture's central region to its edge.
  • the boundary region may have a transmissivity that varies smoothly from about 100% at the central region to about 0% at the edge.
  • FIGS. 4A-4C illustrate transmission profiles along the cross-sections of different implantable ophthalmic devices. Each profile has multiple transmission windows, each of which corresponds to a different static aperture in the device.
  • Each static aperture is apodized according to a corresponding apodization function, such as a power law function (e.g., with a coefficient of about 1.6), a Gaussian or super-Gaussian function, a Harming window, or any other suitable apodization function.
  • the static apertures may have identical, identically spaced apodization functions as shown in FIG. 4A. They may also have identical apodization functions spaced at unequal intervals, as shown in FIG. 4B; different apodization functions spaced at equal intervals, as shown in FIG. 4C; or different apodization functions spaced at unequal intervals.
  • FIGS. 5 A and 5B illustrate intraocular imaging with a monofocal intraocular lens (IOL) 30 (FIG. 5 A) and intraocular imaging with an implantable ophthalmic device 200 that includes multiple static apertures 212 and prismatic elements 220 (FIG. 5B).
  • IOL intraocular lens
  • FIGS. 5 A and 5B illustrate intraocular imaging with a monofocal intraocular lens (IOL) 30 (FIG. 5 A) and intraocular imaging with an implantable ophthalmic device 200 that includes multiple static apertures 212 and prismatic elements 220 (FIG. 5B).
  • a first beam 3 of light from an object 1 impinges on the monofocal lens 30, which produces a second beam 5 that illuminates a retinal plane 9 of a presbyopic or psueodophakic eye.
  • the object 1 is at far distances (e.g., distances greater than 5 m)
  • the second beam 5 comes into focus at the retinal plane 9
  • the image 7 may appear blurry when the object 1 is at near distances (e.g., distances closer than 1 m) or intermediate distances (e.g., distances of about 1 m to about 5 m) due to the IOL's limited depth of field and its inability to accommodate for changes in object position.
  • near distances e.g., distances closer than 1 m
  • intermediate distances e.g., distances of about 1 m to about 5 m
  • the implantable ophthalmic device 200 produces a relatively sharp single image 7 over a depth of field that may extend over near and intermediate object distances.
  • light propagating from the object 1 forms an incident beam, or first beam 3, that illuminates each of the static apertures 212.
  • Each static aperture 212 projects a second, shifted image beam 5' towards the retinal plane 9. Because each static aperture 212 is at a different position from the optical axis, each shifted image beam 5' forms an image on the retina 9 that is shifted with respect to the other beams 5' from the other static apertures 212. Unless these shifts are corrected or compensated, these shifted images may be blurred beyond recognition.
  • the prismatic elements 220 correct for the shifts in the image beams 5 ' by referacting the image beams 5' slightly.
  • the prismatic elements 220 do not necessarilty produce constructively interfering beams; rather, they shift the shifted image beams 5' such that beams' modulation transfer functions (MTFs) add together.
  • the prismatic elements 220 align the shifted image beams 5' such that the beams' intensities add at the retinal plane 9 to form a single image 7.
  • the prismatic elements 220 convert the shifted beams 5' into a third beam 11 whose divergence angle is smaller than that of the image beam 5 produced by the monofocal IOL 30.
  • the third beam 11 has a wider waist and is more nearly collimated than the image beam 5 produced by the monofocal IOL 30.
  • the static apertures 212 and prismatic elements 220 spread the single focal point of the lens 230 over about three Diopters in image space. This increases the depth of field, but it may also reduce the spatial resolution and contrast sensitivity of the lens. Even though the opaque structure 210 blocks some of the incident light, it does not block nearly as much light an opaque structure used to define a single aperture. As a result, an implantable ophthalmic device 200 with multiple static apertures 212 and prismatic elements 220 offers the depth-of-field increase associated with a single aperture without the dramatic decrease in light throughput associated with a single aperture.
  • two or more of the refracted beams from the prismatic elements 220 may interfere to create an aberrated image in the retinal plane 5. These aberrations can be reduced or eliminated by adjusting the optical path length associated with one or more of the static apertures, e.g., by adding one or more optical elements as in FIG. 3G to compensate for phase mismatch. In other words, the prismatic elements 220 and optical elements 250 manage only the complex part of wavefront.
  • Inventive implantable ophthalmic devices may take the form of IOLs, intraocular optics (IOOs), corneal inlays, and corneal onlays.
  • the IOL may have optical power provided by a transparent or translucent element with one or more curved surfaces or one or more graded refractive index profiles as described above.
  • the implantable ophthalmic device may be an IOO, which has little to no optical power except when actuated as described herein.
  • An inventive implantable ophthalmic device may be inserted or implanted in the anterior chamber or posterior chamber of the eye, into the capsular sac, or the stroma of the cornea (similar to a corneal inlay), or into the epithelial layer of the cornea (similar to a corneal onlay), or within any anatomical structure of the eye.
  • An inventive implantable ophthalmic device may have one or more thin, hinge-like sections that allow the implantable ophthalmic device to be folded before implantation and unfolded once positioned properly in a patient's eye. When implanted, any partially transparent or opaque elements (other than the opaque element 210 that defines the static apertures 212) may be disposed out of the patient's line of sight.
  • any two components so associated can also be viewed as being “operably connected,” or “operably coupled,” to each other to achieve the desired functionality, and any two components capable of being so associated can also be viewed as being “operably couplable,” to each other to achieve the desired functionality.
  • operably couplable include but are not limited to physically mateable components and physically interacting components.

Abstract

La présente invention concerne un dispositif ophtalmique, telle qu'une lentille intraoculaire, comportant au moins deux ouvertures dont les dimensions, formes, et positions sont fixes par rapport au dispositif lui-même. Chacune de ces ouvertures statiques reproduit un faisceau d'image incident sous la forme d'un faisceau d'image décalé, où la direction et l'amplitude du décalage dépendent de la position de l'ouverture statique par rapport à l'axe optique du dispositif. Le dispositif comporte également un élément prismatique couplé optiquement à chaque ouverture statique. Chaque élément prismatique reçoit le faisceau d'image décalé depuis son ouverture statique correspondante et réalise une réfraction du faisceau d'image décalé de sorte que les faisceaux réfractés forment une seule image au niveau du plan image (la rétine). Conjointement les ouvertures statiques et les éléments prismatiques accroissent la profondeur effective de champ du dispositif (par exemple, jusqu'à trois dioptres).
PCT/US2012/025922 2011-04-04 2012-02-21 Dispositif ophtalmique implantable avec une pluralité d'ouvertures statiques WO2012138426A2 (fr)

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US9201250B2 (en) 2012-10-17 2015-12-01 Brien Holden Vision Institute Lenses, devices, methods and systems for refractive error
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US11298222B2 (en) 2017-06-01 2022-04-12 Carl Zeiss Meditec Ag Artificial eye lens with diffractive grating structure and method for producing an artificial eye lens
US11344405B2 (en) 2017-06-01 2022-05-31 Carl Zeiss Meditec Ag Artificial eye lens having medicine repository formed therein, and method for producing an artificial eye lens
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