WO2010104654A1 - Interfacial refraction accommodating lens (iral) - Google Patents
Interfacial refraction accommodating lens (iral) Download PDFInfo
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- WO2010104654A1 WO2010104654A1 PCT/US2010/024518 US2010024518W WO2010104654A1 WO 2010104654 A1 WO2010104654 A1 WO 2010104654A1 US 2010024518 W US2010024518 W US 2010024518W WO 2010104654 A1 WO2010104654 A1 WO 2010104654A1
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- Prior art keywords
- lens
- haptics
- chamber
- liquids
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Classifications
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- 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
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- 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
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- 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
- A61F2/1627—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 index of refraction, e.g. by external means or by tilting
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- 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
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- 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
- A61F2/1635—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 shape
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- A61F9/00—Methods or devices for treatment of the eyes; Devices for putting-in contact lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
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- 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
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- A61F2/16—Intraocular lenses
- A61F2002/1681—Intraocular lenses having supporting structure for lens, e.g. haptics
- A61F2002/1682—Intraocular lenses having supporting structure for lens, e.g. haptics having mechanical force transfer mechanism to the lens, e.g. for accommodating lenses
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- A—HUMAN NECESSITIES
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- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
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Definitions
- the natural lens of a human eye is a transparent crystalline body, which is contained within a capsular bag located behind the iris and in front of the vitreous cavity in a region known as the posterior chamber.
- the capsular bag is attached on all sides by fibers, called zonules, to a muscular ciliary body.
- the vitreous cavity which is filled with a gel further includes the retina, on which light rays passing through the lens are focused. Contraction and relaxation of the ciliary body changes the shape of the bag and of the natural lens therein, thereby enabling the eye to focus light rays originating from objects at various distances on the retina.
- Cataracts occur when the natural lens of the eye or of its surrounding transparent membrane becomes clouded and obstructs the passage of light resulting in varying degrees of vision impairment.
- a surgical procedure is performed in which the clouded natural lens, or cataract, is extracted and i replaced by an artificial intraocular lens.
- cataract surgery the anterior portion of the capsular bag is removed along with the cataract, and the posterior portion of the capsular bag, called the posterior capsule, is sometimes left intact to serve as a support site for implanting the intraocular lens (IOL).
- IOL intraocular lens
- Such conventional IOLs have the drawback that they have a fixed refractive power and are therefore unable to change their focus in response to changing focal distance needs of the patient, such as reading, or working on a computer.
- U.S. Pat. No. 5,443,506 to Garabet discloses a variable focus intraocular lens which alters the medium between the two surfaces of the lens to alter its accommodation.
- the lens of the '506 patent has continuous flow loops which couple a channel in first portion of the intraocular lens.
- the continuous flow loops in addition to providing a channel, provide the means by which the intraocular lens is positioned and held in the eye.
- the continuous flow loop(s) comprise the lens haptics i.e., the lens body supporting structures, which, in turn move a charged solution into an optical zone between solid lens surfaces to change the lens focus.
- 5,489,302 discloses an accommodating intraocular lens for implantation in the posterior chamber of the eye.
- This lens comprises a short tubular rigid frame and transparent and resilient membrane attached thereto at its bases.
- the frame and the membranes confine a sealed space filled with a gas.
- the frame includes flexible regions attached via haptics to the posterior capsule. Upon stretching of the capsule by the eye's ciliary muscles, the flexible regions are pulled apart, thereby increasing the volume and decreasing the pressure within the sealed space. This changes the curvature of the membranes and accordingly, the refractive power of the lens.
- U.S. Pat. No. 6,117,171 discloses an accommodating intraocular lens which is contained inside an encapsulating rigid shell so as to make it substantially insensitive to changes in the intraocular environment.
- the lens is adapted to be implanted within the posterior capsule and comprises a flexible transparent membrane, which divides the interior of the intraocular lens into separate front and rear spaces, each filled with a fluid having a different refractive index.
- the periphery of the rear space is attached to haptics, which are in turn attached to the posterior capsule.
- the haptics Upon stretching of the capsule by the eye's ciliary muscles, the haptics and hence this periphery is twisted apart to increase the volume of rear space and changes the pressure difference between the spaces.
- the curvature of the membrane and accordingly, the refractive power of the lens changes.
- Another approach to varying the focus of an IOL is to form a conventional hard intraocular lens with a flexible outer surface made from a material such as silicone. Water is then injected in between the conventional hard portion of the lens and the flexible outer surface of the lens. The water will stretch the outer flexible layer to change the radius of curvature of the intraocular lens and thereby change the accommodation of the lens.
- a fluid source, a fluid pump and a flow control valve all must be provided within close proximity to the lens. As the area around the crystalline lens of the eye is quite confined, most of the fluid injection components have to be provided on the lens itself. Further, an energy source must be provided to pump the fluid. As there is no mechanical force generated in the eye that is strong enough to pump the fluid, an external power supply is required to run the pump. Such an external power supply is usually implemented using a battery which has a limited life cycle.
- IOL is the coating of a conventional IOL with a liquid crystal material.
- a voltage source is applied to the crystal material to polarize the crystals. Once the crystals are polarized the refractive index of the crystalline material changes thereby changing the accommodation of the IOL.
- One principal disadvantage of this type of system is the relatively large amount of energy that is required to polarize the liquid crystal material, on the order of 25 volts. As there is no known manner of generating that level of voltage within the body, an external power source, such as a battery, is therefore necessary. [0011]
- Some conventional accommodating IOLs rely on a solid curved surface to provide refraction.
- the present invention addresses the shortcomings of prior art lenses and lens assemblies through the use of a novel refraction system based on the interface naturally created between first and second immiscible fluids or liquids (sometimes designated "I” and "IT").
- first and second immiscible fluids or liquids sometimes designated "I” and "IT”
- I and I immiscible fluids or liquids
- An accommodating IOL of the present invention generally comprises a lenticular chamber where two immiscible liquids are in contact with each other forming a meniscus.
- the interface between the two liquids provides the refractive surface that bends light into a focal point on the retina.
- the meniscus curvature and thus the focus of the lens is changed by applying pressure on the periphery of the lens generally by means of the lens haptics.
- a very small force e.g., by ciliary muscle contraction applied to the haptics, is required to cause a significant change in meniscus curvature, which in turn changes the diopter of the lens to provide focus on objects at various distances.
- the force is transmitted from the ciliary muscles to the meniscus through the haptics.
- the haptics may be formed into several configuration including C-loop, modified C-loop, square, disk-like, plate, etc.
- the haptics themselves are at least partially hollow having fluid-containing haptic internal chambers, the haptic chambers being in fluidic communication with the lenticular chamber or lens body such that displacement of the haptic, e.g., posteriorly, causes some of fluid I or II to flow into the lens body and enhance, increase or amplify the accommodation obtained.
- the visually transparent posterior and anterior walls which define the lenticular chamber are flexible or stretchable such that they can be displaced by one or the other of the fluids.
- the posterior lenticular chamber wall is flexible or stretchable permitting it to be posteriorly displaced when fluid from the haptic chamber flows into the haptic chamber
- the hollow lens haptics are preferably rectangular in configuration preferably are two in number, and are disposed on opposite sides of the optic body.
- a variety of liquids may be used for this invention. The most important parameters are clarity, surface energy, density, viscosity and refractive index. Virtually any liquid combination may be used. The accommodating power for a variety of liquid combinations was calculated based on the change in meniscus curvature. The following Table 1 summarizes some of those results. In a preferred practice of this invention, the densities of the respective liquids are substantially the same.
- substantially the same densities herein it is meant densities of such similarity such that the fluids or liquids can be contained within an elongate, vertically-disposed, optical chamber and, being immiscible as described herein, the fluid(s) or liquid(s) have little or no tendency to "settle out” at the bottom of the chamber (or collect at the bottom of the chamber) due to gravitational forces and thereby maintain a separated, vertically-disposed relationship with respect to each other when the wearer is looking horizontally or at a distance.
- the interface can be moved with minute forces. This allows a change of curvature with minimal forces from ciliary muscles and hence significantly larger diopter changes.
- the haptics element of the assembly according to the present invention may adopt any of a variety of designs known in the art, e.g. it may be curved or it may be in the form of a plate. In addition, the haptics element may be completely transparent or opaque.
- the haptics element of the lens assembly in accordance with the present invention may be made of a variety of possible rigid materials suitable for invasive medical use and known in the art to be used in the formation of haptics.
- the haptics are at least partially hollow, containing one of the fluids, and being fluidically coupled via a channel to the lenticular chamber or lens body.
- the lens of this invention is foldable.
- the lens comprises optically-acceptable, foldable materials.
- the lens assembly of the present invention offers advantages such as a simple and inexpensive construction.
- the lens assembly of the present invention also provides the ability to accommodate within a vast range of refractive power, including the full range provided by the natural eye and much more if needed in case of other eye diseases such as age-related macular degeneration (AMD).
- AMD age-related macular degeneration
- the lens assembly provides means for varying its sensitivity in response to the force applied by the capsular unit.
- the lens assembly is similar in design to conventional monofocal IOLs and can be implanted using existing surgical instruments and techniques. No special surgical skills or training is required.
- FIG. 1 is a flow chart showing the interaction between an accommodation
- FIG. 2 is a front view of an Interfacial Refraction Accommodating Lens or
- FIG. 4 is a perspective view of a second embodiment of the present invention in which the direction of the application of force to the haptics by the ciliary muscle is illustrated by arrows (11).
- the accommodating lens of FIG. 4 also has a different haptic configuration from the lens of FIGS. 1 and 2.
- FIG. 5 is a perspective view of a piezoelectric or electrical accommodating lens embodiment of the present invention.
- FIG. 6 shows a further embodiment of the present invention in which 6A shows an IOL of this invention in the accommodated state and 6B shows the same IOL as is shown in FIG. 6A in an unaccommodated state.
- FIG. 8 shows yet a third accommodating IOL of this invention in cross section.
- FIG. 10 shows the lens of FIG. 9 in section taken along line 10A- 1OA of
- FIGS. 11-13 illustrate in side view, a top view, and in section along line
- FIG. 14 shows the IOL of FIG. 13 in an accommodating state, the haptics being slightly bent, depressed or moved in the direction of the arrows toward the bottom of the figure.
- FIG. 15 shows an implantation site of an IOL of the present invention
- IOL being in an accommodated state.
- FIG. 16 shows the IOL of FIG. 15, as implanted, in an unaccommodated state.
- FIGS. 17, 18 and 19 show in side-view, in top view, and in section, respectively, the further embodiment of an IOL of this invention.
- FIGS. 20 and 21 show an implantation site of the IOL of FIGS. 17-19 in an accommodated, and unaccommodated state, respectively.
- FIGS. 22, 23 and 24 show a further embodiment of the present invention in side view, top view and section taken along line 24-24 of FIG. 23.
- FIGS. 25-26 and 27 A-D show a further embodiment of the present invention in which lens haptic fluid chambers are coupled to the lens body and which by moving posteriorly (or anteriorly) change the lens focus.
- this invention is an implantable interfacial refraction ophthalmic lens (IRAL) assembly or apparatus which adjusts its focal distance in response to changing physiologic needs of the user of said lens (e.g., a patent in which the lens has been implanted.).
- the lens comprises a flexible optic chamber, lens body, or optic and cooperating haptics.
- the optic chamber is defined by opposed, substantially parallel, visually transparent, generally circular, elastic or stretchable discs or walls, which are flexibly coupled at their edges and spaced apart to define a closed fluidic chamber.
- the fluidic chamber includes first and second liquids, the liquids having different refractive indices (the difference being ⁇ RI) and, in one embodiment, being immiscible and preferably of substantially the same densities so as to define a changeable or changing spherical or lenticular interface therebetween.
- the haptics are coupled to the edge of the optic chamber and to the fluidic chamber so that application of force to the haptics deforms the fluidic chamber, displaces fluid into the optic chamber and thereby changes the sphericity of the liquid interface.
- the focal length of the lens assembly changes in response to application of force to the haptics to change the visual focus of the user.
- the haptics Upon relaxation of the ciliary muscle force applied to the haptics, the haptics, having a natural bias to resist the applied force, return to their pre-application of force configuration or arrangement, the lens diopter thereby declining by, change in the shape of the I, II, fluid interface.
- the fluids are optionally immiscible and are separated by a visually transparent, flexible membrane which is sealed to the edge of the disc(s) to define flexible fluidic chamber and which prevents the fluids from mixing.
- This invention also includes a method of correcting visual activity by the use of an accommodating IRAL, the method comprising the steps of: replacing a defective natural lens of an eye of a patient in need of such replacement with an accommodating IRAL; permitting the IRAL to accommodate the patient's need to change the focal point of the eye e.g., the retinal focus, by changing the diopter strength and thus the focal point of the IRAL wherein the diopter strength change of the IRAL is at least 2 diopters; and wherein the IRAL employs liquids having different refractive indices to define to change diopter strength and thus the interface.
- the haptics center the IOL in the focal zone or focal axis of the eye and receive and transmit ciliary muscle force to the optic chamber or lens body (described in greater detail below).
- the haptics can be in direct contact with eye muscle if the accommodation IOL is implanted into the sulcus.
- the optomechanics of an accommodating IOL of the invention then converts the ciliary muscle force into diopter changes of the lens.
- FIG. 2 is a front view of an interfacial refraction accommodating lens
- FIG. 2 there is shown a lens assembly 10 comprising an optic chamber or lens body 12 and haptics 14. It will be understood that haptics 14 shown in FIG. 2 are only one possible haptic configuration, there being many others which will readily occur to one skilled in this art in view of this disclosure. Also shown within optic chamber 12 by a dotted circle 16, 16' is the position of the refractive surface (i.e. the interface between the two fluids) upon responding to the force exerted by the ciliary muscles.
- the refractive surface i.e. the interface between the two fluids
- FIG. 3 is a cross-sectional view of the IRAL shown in Fig. 2 showing the relationship between hap tic deformation or displacement angle 15, 15' and the change in interfacial radius of curvature 16, 16' achieved by very small haptic deformation angle changes.
- the change in the shape of the interface 16 shown in Fig. 2 illustrates the increase in radius of curvature of the refractive surface upon changes in haptic pressure. Changes in haptic pressure are obtained by changes in the deformation of the haptics which, in turn, result from increased pressure of the ciliary muscle or capsular bag.
- the radius of curvature of the interior envelope 16, 16' changes in response to haptic deformation angle changes.
- That change in radius of curvature in conjunction with the Liquids I and II create substantial dioptric changes for very small ciliary muscle movement(s). Changes in diopter per degree change in deformation angle for various Liquids I and II are shown in Table 1 above.
- the invention provides diopter changes which are substantially in excess of anything disclosed in the prior art. Thus, for example, diopter changes (and accommodation as discussed above) in the range of four diopters, preferably six diopters, and most preferably about 7.5 diopters or more are obtained in once practice of this invention.
- FIG. 5 illustrates an electrical or piezoelectric design or approach to the present invention.
- a transducer element or circular haptic 40 is coupled or connected via the connecting or coupling element 42 to fluid chamber 44.
- movement of the transducer element-haptic 40 by the user's ciliary muscle causes an electrical signal to be transmitted, via conducting element 42 to fluid chamber 44.
- Accommodation in the eye is induced by the contraction of ciliary muscles (not shown) and capsular bag (not shown).
- a method of this invention involves a transducing element 40 sensing the ciliary muscle force and generating an electrical current or voltage through lens chamber 44.
- a transducer capable of converting the ciliary muscle or capsular bag movement into an electrical signal is used to effectively change the shape of the meniscus and allow accommodation.
- the transducer can be a piezoelectric device, a force sensor, an actuator or any other element capable of converting a force into an electrical signal.
- the haptics may be made from a force sensing element.
- the haptics may be formed into several configuration including C-loop, modified C-loop, square, disk-like, plate, etc.
- haptic materials may include PMMA, PVDF, PP, or other polymers.
- Optic chamber 12 materials can include hydrophobic acrylic polymers or copolymers (HAC), hydrophilic acrylic polymers or copolymers, silicone polymers or copolymers (PDMS) or other polymers.
- Preferred polymers include PDMS or HAC. (12 and 16 are made from the same material). As is noted the relationship between refractive indices of Liquids I and II are required in order to obtain the advantages of the present invention.
- FIG. 6-14 the anterior side of the implant, lens body or lens assembly 20 is generally to the left; posterior 22 generally to the right.
- the lens body or optic chamber generally comprises discs 24, 26 which are flexibly coupled at their edges 28.
- flexible coupler or sidewall 28 is compressible and provides an annular connection between discs 24, 26, coupler 28.
- Chamber 30 contains immiscible liquids 32, 34 having differing refractive indexes according to this inventor. Generally, the higher refractive index liquid will be posteriorly disposed in lens body 34, with the lower refractive index liquid 32 being anterior, although the opposite arrangement may be used in some embodiments.
- a spherical curved interface 36 is formed. At its perimeter the interface has a fixed contact angle 4OA at the interface to the implant sidewall 28.
- the curvature of this liquid interface depends on the properties (surface tensions) of the liquids and the implant material. It corresponds to an energy minimum. Force from the eye muscle is transmitted to the implant by haptics schematically shown by arrows 42, the bolder arrow indicating greater force. This applied force deforms a sidewall 28. Because of the fixed contact angle 40 a change in sidewall inclination will change the radius of the liquid interface 36 (an energy minimum is attained). A change in radius will lead to a change in optical power i.e., diopter rating of the device 10. In this manner the focal length of the IOL will change to provide a better focus of impinging light on the retina (not shown).
- FIG. 7 a variation is shown in which the force from the eye muscle is transmitted to the implant by haptics to a displaceable annular sidewall 50.
- the applied force shown by arrows 52 pushes the liquid interface along the variable curved sidewall 50. This is done by deforming hinge-like structure 56, which is integrated into the implant.
- hinge-like structure 56 which is integrated into the implant.
- the liquid interface will adapt its curvature to achieve the fix contact angle. This corresponds to an energy minimum. A change in radius will lead to a change in optical power of the device.
- FIGS. 8, 9, and 10 illustrate a further embodiment of the invention.
- Haptics 80 in this embodiment are interiorly coupled to a moveable interior ring 81. Force applied at arrows 82 moves the ring structure 81 within the implant.
- the movable ring structure could be made out of a different materials (e.g., having a high stiffness) than the implant. As the ring structure is swept across the liquid interface a certain radius of the liquid interface will be formed that corresponds to an energy minimum. The change in radius thus will lead to a change in optical power of the implant.
- Arrows 98 generally show the direction of shift in haptic 90 deformation to achieve the accommodated or accommodation state.
- the curvature of the liquid interface is increased compared to the unaccommodated state 96 (FIGS. 11, 12, and 13) and the optical power of the implant increases.
- Deformation Angle arcus sin( — ⁇ -) - arcus sin( — ⁇ -)
- FIGS. 15 and 16 show generally the implant site in the eye where a lens of this invention would be located. Anterior is to the left while posterior is to the right. Impinging light enters from the left and is to be focused upon the retina (not shown).
- FIG. 15 shows, e.g., a lens of FIGS. 9-14 with the contracted ciliary muscle 110 applying force to hap tics 90 - so as to deform the surfaces of the immiscible liquids in lens body 10 to change of optical characteristics of the lens, i.e., to accommodate the optical need of the implant patient.
- the sulcus 112, vitreous 114 cornea 116, iris 118, collapsed lens bag 120, and zonules 122 eye structures are shown.
- FIGS. 17-19 show a variation in which an anterior uniconvex lens 140 is used. All other structural elements are the same.
- FIGS . 20-21 shows the lens of FIGS . 17- 19 as implanted.
- FIGS. 22-24 shows an equiconvex or biconvex IOL 160 design of this invention. An implantation view would be similar to that as shown in FIGS. 15 and 16.
- FIGS. 25-26, and 27 A-D show a preferred embodiment of this invention in which one or the other of fluids I, II are contained within hollow lens haptics and is displaced into the optic body by e.g., ciliary muscle contraction. The lenses shown are generally viewing toward the bottom of the page.
- FIG. 25 shows in section an unaccommodated lens 200 comprising an optic chamber or lens body 202 defined by transparent anterior 204 and posterior 206 lens walls.
- FIG. 26 shows the lens 200 of FIG. 25 in an accommodated state where posterior displacement of haptics 214 obtains the accommodation.
- posterior lens wall 206 is flexible allowing it to bulge posteriorly permitting increased accommodation by increased change in the curvature defined by interface 212.
- Arrows 218 show the direction of haptic displacement while arrows 220 show the direction of fluid flow in response to haptic displacement.
- the reverse direction fluid flow occurs (i.e., into the haptic chamber 216) when the haptics in FIG. 26 are permitted to return to the configuration shown in FIG. 25.
- accommodation and relaxation of the accommodation are obtained.
- FIGS. 27 A-D illustrate in partial plan and partial section further embodiments of the lens shown in FIGS. 25 and 26. As is shown, rectangular, oppositely disposed hollow optics are used. Other lens body/haptic configuration will occur to one skilled in this art.
- fluids having differing refractive indices are used but which are miscible.
- the two liquids are separated by an optically-acceptable, flexible, or elastic membrane, film, or divider.
- the membrane would then define the interface or meniscus between the fluids (e.g., at 16, 16' in FIG. 3, 96 in FIG. 13, 36' 36 in FIGS. 6-9,) and thus the radius of curvature which determines the degree of accommodation.
- the membrane which separates fluids I and II would not be permeable by either fluid, would not be chemically affected by either fluid, and would be internally bonded to the edge of the optical chamber or lens body so as to prevent the liquids from mixing.
- an IRAL of the present invention is a completely hermetically sealed structure.
- the present IRAL are robust, intended for long term implantation, providing many years of near-natural lens accommodation for the patient.
- IRALs of this invention are, in a preferred embodiment, foldable.
- the lens obtains small incision implantation and other medical advantages which foldable IOLs provide.
- materials chosen for the various lens structures must have relative flexibility or rigidity so as to perform the their optical intended function(s) and to provide structural integrity while also permitting the entire structure to be sufficiently soft or flexible to be stored in a folded state and to unfold when inserted in folded or rolled fashion through a small incision during the implantation procedure.
Abstract
Description
Claims
Priority Applications (8)
Application Number | Priority Date | Filing Date | Title |
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CN2010800082162A CN102316825A (en) | 2009-02-18 | 2010-02-18 | Interfacial refraction accommodating lens (IRAL) |
CA2752743A CA2752743A1 (en) | 2009-02-18 | 2010-02-18 | Interfacial refraction accommodating lens (iral) |
MX2011008699A MX2011008699A (en) | 2009-02-18 | 2010-02-18 | Interfacial refraction accommodating lens (iral). |
AU2010223018A AU2010223018A1 (en) | 2009-02-18 | 2010-02-18 | Interfacial refraction accommodating lens (IRAL) |
JP2011551202A JP2012517889A (en) | 2009-02-18 | 2010-02-18 | Interfacial refraction adjustment lens (IRAL) |
EP10751162A EP2323590A1 (en) | 2009-02-18 | 2010-02-18 | Interfacial refraction accommodating lens (iral) |
BRPI1008687A BRPI1008687A2 (en) | 2009-02-18 | 2010-02-18 | interfacial (iral) refractive accommodation lens. |
US13/265,085 US8657878B2 (en) | 2009-02-18 | 2010-02-18 | Interfacial refraction accommodating lens (IRAL) |
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US12/388,254 | 2009-02-18 | ||
US12/388,254 US8034106B2 (en) | 2007-02-02 | 2009-02-18 | Interfacial refraction accommodating lens (IRAL) |
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WO2010104654A1 true WO2010104654A1 (en) | 2010-09-16 |
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PCT/US2010/024518 WO2010104654A1 (en) | 2009-02-18 | 2010-02-18 | Interfacial refraction accommodating lens (iral) |
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US (1) | US8034106B2 (en) |
EP (1) | EP2323590A1 (en) |
JP (1) | JP2012517889A (en) |
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CN (1) | CN102316825A (en) |
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- 2010-02-18 EP EP10751162A patent/EP2323590A1/en not_active Withdrawn
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EP3081192A4 (en) * | 2013-12-13 | 2017-08-09 | Xlens Technologies Inc. | Adjustable intraocular lens |
WO2018064061A1 (en) * | 2016-09-27 | 2018-04-05 | Verily Life Sciences Llc | Intraocular active accommodation system |
US11273029B2 (en) | 2016-09-27 | 2022-03-15 | Verily Life Sciences Llc | Intraocular active accommodation system |
Also Published As
Publication number | Publication date |
---|---|
KR20110127706A (en) | 2011-11-25 |
AU2010223018A1 (en) | 2011-09-01 |
BRPI1008687A2 (en) | 2016-03-08 |
JP2012517889A (en) | 2012-08-09 |
MX2011008699A (en) | 2011-11-29 |
EP2323590A1 (en) | 2011-05-25 |
CN102316825A (en) | 2012-01-11 |
US8034106B2 (en) | 2011-10-11 |
US20090264998A1 (en) | 2009-10-22 |
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