WO2008108524A1 - Intraocular lens - Google Patents
Intraocular lens Download PDFInfo
- Publication number
- WO2008108524A1 WO2008108524A1 PCT/KR2007/004632 KR2007004632W WO2008108524A1 WO 2008108524 A1 WO2008108524 A1 WO 2008108524A1 KR 2007004632 W KR2007004632 W KR 2007004632W WO 2008108524 A1 WO2008108524 A1 WO 2008108524A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- intraocular lens
- lens according
- optic
- face
- support bar
- Prior art date
Links
- ATJFFYVFTNAWJD-UHFFFAOYSA-N Tin Chemical compound [Sn] ATJFFYVFTNAWJD-UHFFFAOYSA-N 0.000 claims description 45
- 229910052718 tin Inorganic materials 0.000 claims description 45
- WOBHKFSMXKNTIM-UHFFFAOYSA-N Hydroxyethyl methacrylate Chemical compound CC(=C)C(=O)OCCO WOBHKFSMXKNTIM-UHFFFAOYSA-N 0.000 claims description 42
- 239000000463 material Substances 0.000 claims description 40
- 230000000007 visual effect Effects 0.000 claims description 23
- 229920001296 polysiloxane Polymers 0.000 claims description 16
- CERQOIWHTDAKMF-UHFFFAOYSA-N Methacrylic acid Chemical compound CC(=C)C(O)=O CERQOIWHTDAKMF-UHFFFAOYSA-N 0.000 claims description 15
- WHNWPMSKXPGLAX-UHFFFAOYSA-N N-Vinyl-2-pyrrolidone Chemical compound C=CN1CCCC1=O WHNWPMSKXPGLAX-UHFFFAOYSA-N 0.000 claims description 15
- -1 polypropylene Polymers 0.000 claims description 15
- 239000002775 capsule Substances 0.000 claims description 14
- VVQNEPGJFQJSBK-UHFFFAOYSA-N Methyl methacrylate Chemical compound COC(=O)C(C)=C VVQNEPGJFQJSBK-UHFFFAOYSA-N 0.000 claims description 12
- NIXOWILDQLNWCW-UHFFFAOYSA-N acrylic acid group Chemical group C(C=C)(=O)O NIXOWILDQLNWCW-UHFFFAOYSA-N 0.000 claims description 12
- 238000013459 approach Methods 0.000 claims description 12
- 239000000017 hydrogel Substances 0.000 claims description 12
- 229920003229 poly(methyl methacrylate) Polymers 0.000 claims description 12
- 239000004926 polymethyl methacrylate Substances 0.000 claims description 12
- 230000001965 increasing effect Effects 0.000 claims description 11
- 229920000036 polyvinylpyrrolidone Polymers 0.000 claims description 9
- 239000001267 polyvinylpyrrolidone Substances 0.000 claims description 9
- 235000013855 polyvinylpyrrolidone Nutrition 0.000 claims description 9
- 239000000853 adhesive Substances 0.000 claims description 8
- 230000001070 adhesive effect Effects 0.000 claims description 8
- XKRFYHLGVUSROY-UHFFFAOYSA-N Argon Chemical compound [Ar] XKRFYHLGVUSROY-UHFFFAOYSA-N 0.000 claims description 6
- IJGRMHOSHXDMSA-UHFFFAOYSA-N Atomic nitrogen Chemical compound N#N IJGRMHOSHXDMSA-UHFFFAOYSA-N 0.000 claims description 6
- 230000008878 coupling Effects 0.000 claims description 6
- 238000010168 coupling process Methods 0.000 claims description 6
- 238000005859 coupling reaction Methods 0.000 claims description 6
- 229920002338 polyhydroxyethylmethacrylate Polymers 0.000 claims description 6
- 239000007789 gas Substances 0.000 claims description 5
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 5
- SQDAZGGFXASXDW-UHFFFAOYSA-N 5-bromo-2-(trifluoromethoxy)pyridine Chemical compound FC(F)(F)OC1=CC=C(Br)C=N1 SQDAZGGFXASXDW-UHFFFAOYSA-N 0.000 claims description 4
- 229920001287 Chondroitin sulfate Polymers 0.000 claims description 4
- 229920002385 Sodium hyaluronate Polymers 0.000 claims description 4
- 229940059329 chondroitin sulfate Drugs 0.000 claims description 4
- 239000001866 hydroxypropyl methyl cellulose Substances 0.000 claims description 4
- 229920003088 hydroxypropyl methyl cellulose Polymers 0.000 claims description 4
- UFVKGYZPFZQRLF-UHFFFAOYSA-N hydroxypropyl methyl cellulose Chemical compound OC1C(O)C(OC)OC(CO)C1OC1C(O)C(O)C(OC2C(C(O)C(OC3C(C(O)C(O)C(CO)O3)O)C(CO)O2)O)C(CO)O1 UFVKGYZPFZQRLF-UHFFFAOYSA-N 0.000 claims description 4
- 235000010979 hydroxypropyl methyl cellulose Nutrition 0.000 claims description 4
- 239000007788 liquid Substances 0.000 claims description 4
- 229940010747 sodium hyaluronate Drugs 0.000 claims description 4
- YWIVKILSMZOHHF-QJZPQSOGSA-N sodium;(2s,3s,4s,5r,6r)-6-[(2s,3r,4r,5s,6r)-3-acetamido-2-[(2s,3s,4r,5r,6r)-6-[(2r,3r,4r,5s,6r)-3-acetamido-2,5-dihydroxy-6-(hydroxymethyl)oxan-4-yl]oxy-2-carboxy-4,5-dihydroxyoxan-3-yl]oxy-5-hydroxy-6-(hydroxymethyl)oxan-4-yl]oxy-3,4,5-trihydroxyoxane-2- Chemical compound [Na+].CC(=O)N[C@H]1[C@H](O)O[C@H](CO)[C@@H](O)[C@@H]1O[C@H]1[C@H](O)[C@@H](O)[C@H](O[C@H]2[C@@H]([C@@H](O[C@H]3[C@@H]([C@@H](O)[C@H](O)[C@H](O3)C(O)=O)O)[C@H](O)[C@@H](CO)O2)NC(C)=O)[C@@H](C(O)=O)O1 YWIVKILSMZOHHF-QJZPQSOGSA-N 0.000 claims description 4
- QRIMLDXJAPZHJE-UHFFFAOYSA-N 2,3-dihydroxypropyl 2-methylprop-2-enoate Chemical compound CC(=C)C(=O)OCC(O)CO QRIMLDXJAPZHJE-UHFFFAOYSA-N 0.000 claims description 3
- NIXOWILDQLNWCW-UHFFFAOYSA-M Acrylate Chemical compound [O-]C(=O)C=C NIXOWILDQLNWCW-UHFFFAOYSA-M 0.000 claims description 3
- 229920002972 Acrylic fiber Polymers 0.000 claims description 3
- 239000004925 Acrylic resin Substances 0.000 claims description 3
- 229920000178 Acrylic resin Polymers 0.000 claims description 3
- BMTAFVWTTFSTOG-UHFFFAOYSA-N Butylate Chemical compound CCSC(=O)N(CC(C)C)CC(C)C BMTAFVWTTFSTOG-UHFFFAOYSA-N 0.000 claims description 3
- 102000008186 Collagen Human genes 0.000 claims description 3
- 108010035532 Collagen Proteins 0.000 claims description 3
- CERQOIWHTDAKMF-UHFFFAOYSA-M Methacrylate Chemical compound CC(=C)C([O-])=O CERQOIWHTDAKMF-UHFFFAOYSA-M 0.000 claims description 3
- 239000004642 Polyimide Substances 0.000 claims description 3
- 239000004743 Polypropylene Substances 0.000 claims description 3
- 238000010521 absorption reaction Methods 0.000 claims description 3
- 239000003570 air Substances 0.000 claims description 3
- 229910052786 argon Inorganic materials 0.000 claims description 3
- CQEYYJKEWSMYFG-UHFFFAOYSA-N butyl acrylate Chemical compound CCCCOC(=O)C=C CQEYYJKEWSMYFG-UHFFFAOYSA-N 0.000 claims description 3
- 229920002301 cellulose acetate Polymers 0.000 claims description 3
- 229920001436 collagen Polymers 0.000 claims description 3
- 229920001577 copolymer Polymers 0.000 claims description 3
- 239000004205 dimethyl polysiloxane Substances 0.000 claims description 3
- 235000013870 dimethyl polysiloxane Nutrition 0.000 claims description 3
- 229920001971 elastomer Polymers 0.000 claims description 3
- 239000000806 elastomer Substances 0.000 claims description 3
- 239000003292 glue Substances 0.000 claims description 3
- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 claims description 3
- 239000010931 gold Substances 0.000 claims description 3
- 229910052737 gold Inorganic materials 0.000 claims description 3
- 239000001307 helium Substances 0.000 claims description 3
- 229910052734 helium Inorganic materials 0.000 claims description 3
- SWQJXJOGLNCZEY-UHFFFAOYSA-N helium atom Chemical compound [He] SWQJXJOGLNCZEY-UHFFFAOYSA-N 0.000 claims description 3
- 230000002209 hydrophobic effect Effects 0.000 claims description 3
- 229910052754 neon Inorganic materials 0.000 claims description 3
- GKAOGPIIYCISHV-UHFFFAOYSA-N neon atom Chemical compound [Ne] GKAOGPIIYCISHV-UHFFFAOYSA-N 0.000 claims description 3
- 229910052757 nitrogen Inorganic materials 0.000 claims description 3
- 125000000914 phenoxymethylpenicillanyl group Chemical group CC1(S[C@H]2N([C@H]1C(=O)*)C([C@H]2NC(COC2=CC=CC=C2)=O)=O)C 0.000 claims description 3
- 229920000435 poly(dimethylsiloxane) Polymers 0.000 claims description 3
- 229920000058 polyacrylate Polymers 0.000 claims description 3
- 229920001721 polyimide Polymers 0.000 claims description 3
- 229920001155 polypropylene Polymers 0.000 claims description 3
- VXLYKKNIXGIKAE-UHFFFAOYSA-N prop-2-enoyl 2-methylprop-2-enoate Chemical group CC(=C)C(=O)OC(=O)C=C VXLYKKNIXGIKAE-UHFFFAOYSA-N 0.000 claims description 3
- 229920005573 silicon-containing polymer Polymers 0.000 claims description 3
- 229920002379 silicone rubber Polymers 0.000 claims description 3
- 239000003106 tissue adhesive Substances 0.000 claims description 3
- 229920002401 polyacrylamide Polymers 0.000 claims description 2
- 239000007787 solid Substances 0.000 claims description 2
- 210000001508 eye Anatomy 0.000 description 77
- 239000012530 fluid Substances 0.000 description 18
- 230000003993 interaction Effects 0.000 description 15
- 210000003205 muscle Anatomy 0.000 description 14
- 238000012546 transfer Methods 0.000 description 7
- 238000003780 insertion Methods 0.000 description 5
- 230000037431 insertion Effects 0.000 description 5
- 210000001747 pupil Anatomy 0.000 description 5
- 210000005252 bulbus oculi Anatomy 0.000 description 4
- 238000000034 method Methods 0.000 description 4
- 239000003190 viscoelastic substance Substances 0.000 description 4
- 208000002177 Cataract Diseases 0.000 description 3
- 230000008859 change Effects 0.000 description 3
- 210000004087 cornea Anatomy 0.000 description 3
- 238000004519 manufacturing process Methods 0.000 description 3
- HRPVXLWXLXDGHG-UHFFFAOYSA-N Acrylamide Chemical compound NC(=O)C=C HRPVXLWXLXDGHG-UHFFFAOYSA-N 0.000 description 2
- 230000008602 contraction Effects 0.000 description 2
- 201000010099 disease Diseases 0.000 description 2
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 239000011261 inert gas Substances 0.000 description 2
- 201000010041 presbyopia Diseases 0.000 description 2
- 210000001519 tissue Anatomy 0.000 description 2
- 206010027646 Miosis Diseases 0.000 description 1
- 208000006550 Mydriasis Diseases 0.000 description 1
- 230000002159 abnormal effect Effects 0.000 description 1
- 230000009471 action Effects 0.000 description 1
- 238000007796 conventional method Methods 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 230000002708 enhancing effect Effects 0.000 description 1
- 239000011521 glass Substances 0.000 description 1
- 230000004402 high myopia Effects 0.000 description 1
- 238000003384 imaging method Methods 0.000 description 1
- 230000003547 miosis Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 210000000056 organ Anatomy 0.000 description 1
- 229920003023 plastic Polymers 0.000 description 1
- 239000004033 plastic Substances 0.000 description 1
- 230000002040 relaxant effect Effects 0.000 description 1
- 210000001525 retina Anatomy 0.000 description 1
- 238000007363 ring formation reaction Methods 0.000 description 1
- 230000009278 visceral effect Effects 0.000 description 1
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
- A61F2/1624—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
-
- 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
- A61F2/16—Intraocular lenses
- A61F2/1694—Capsular bag spreaders therefor
-
- 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
- A61F2002/1681—Intraocular lenses having supporting structure for lens, e.g. haptics
- A61F2002/169—Surrounding optic
-
- 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
- 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
- A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
- A61F2250/0036—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in thickness
Definitions
- the present invention relates to an intraocular lens, and more particularly to an intraocular lens provided inside a capsular sac.
- the intraocular lens may give an opaque sight to patients instead of their own natural eye lens.
- the intraocular lens has problems that a capsular sac into which the intraocular lens is inserted is contracted after the insertion of the intraocular lens.
- a new method comprising steps of inserting a capsular tension ring into an equatorial region of a capsular sac prior to the insertion of the intraocular lens and fixing the intraocular lens in the capsular tension ring.
- a capsular tension ring which is referred to as open or closed ring formations, is effective in partially relieving contraction of a capsular sac, partially maintaining a shape of the capsular sac from which an eye lens is removed, and easily supporting the inserted intraocular lens.
- the problems is that a patient does not ensure a sight through active three-dimensional movements of an intraocular lens along objects to be seen, but ensures a passive sight according to the predetermined power of an intraocular lens.
- FIG. 1 is a cross-sectional view showing a human eyeball
- FIG. 2 is a cross- sectional view showing a structure of a natural eye lens.
- a cornea 10 is a transparent avascular tissue disposed in the outermost region of the eye and protects an eyeball. Also, the cornea serves to reflect the light together with the eye lens.
- An iris 20 functions as the iris of a camera by adjusting the intensity of the light entering the eye.
- a pupil 30 is a hole in the center of the iris 20, and adjusts the intensity of the light entering the retina 40 by contracting the hole under the bright light and expanding the hole under the dark light.
- An eye lens 50 is a colorless and transparent avascular structure having a convex lens shape in both sides, and arranged in the back of the iris 20.
- the eye lens 50 is an organ that takes part in reflecting the light entering the eye together with the cornea 10, and its shape is changed according to the contraction and relaxation of a ciliaris muscle 60 and a zonule of Zinn 70 coupled to the ciliaris muscle 60.
- Presbyopia is a state that the hardness of the eye lens 50 increases with the age, and therefore the shape of the eye lens 50 is not changed even if the ciliaris muscle 60 contracts, and the cataract is a disease that the eye lens 50 becomes opaque with the age.
- the eye lens 50 is filled inside a capsular sac 80, and the capsular sac 80 is composed of an anterior capsule 80a and a posterior capsule 80b, each of which is in contact with an anterior surface 51 and a posterior surface 55 of the eye lens 50.
- the anterior surface 51 and the posterior surface 55 of the eye lens 50 are coupled to each other in an equator (E).
- Each of the anterior surface 51 and the posterior surface 55 is divided into a central region (a) and an equatorial region (b) according to the distance from the equator (E).
- the central region (a) of the anterior surface 51 has a smaller curvature than the central region (a) of the posterior surface 55, and the equatorial region (b) of the anterior surface 51 has a larger curvature than the equatorial region (b) of the posterior surface 55.
- the zonule of Zinn 70 is coupled along an edge of the capsular sac 80.
- the zonule of Zinn 70 is coupled along an edge of the capsular sac 80.
- Zinn 70 is a kind of a fibrous tissue that couples the capsular sac 80 to the ciliaris muscle 60, and composed of a first zonule portion coupled to the center of the equatorial region in which the anterior capsule 80a and the posterior capsule 80b of the capsular sac 80 meets; and a second zonule portion coupled to a circumference of the equatorial region.
- FIG. 3 and FIG. 4 are illustrative views showing an interaction of a zonule of Zinn, an eye lens and a capsular sac when focused on a long distance and a short distance object, respectively.
- a Y direction represents a visual axis direction of an eye lens
- an X direction represents an equatorial direction of an eye lens.
- the visual axis direction of the eye lens means a direction that the light enters an eye lens 50 through a pupil
- the equatorial direction means a direction that, as a vertical direction of the visual axis direction, connects a point that an anterior capsule and a posterior capsule of an eye lens meets.
- a first zonule portion 73 coupled to the center of the equatorial region of the capsular sac 80 is pulled taut and a second zonule portion 71 coupled to the circumference of the equatorial region of the capsular sac 80 is relaxed when focused on a long distance object.
- the capsular sac 80 is extended in an X direction of the eye lens 50, and therefore the eye lens 50 arranged inside the capsular sac 80 is extended in the same direction (X).
- the first zonule portion 73 coupled to the center of the equatorial region of the capsular sac 80 is relaxed and the second zonule portion 71 coupled to the circumference of the equatorial region of the capsular sac 80 is pulled taut when focused on a short distance object.
- the capsular sac 80 is projected in a Y direction of the eye lens 50, and therefore the eye lens 50 arranged inside the capsular sac 80 is extended in the same direction.
- the capsular sac 80 having a natural eye lens disposed therein is coupled to the zonule of Zinn 70, and therefore takes part in actively deforming shapes of the natural eye lens, but the use of the conventoinal intraocular lens and capsular tension ring forces the capsular sac to contract, which leads to the substantial loss of its functions.
- a ciliaris muscle which is coupled to a zonule of Zinn to take part in the shape deformation of an eye lens, is a visceral muscle that maintains the endless function to the death. Therefore, the conventional method of artificially removing an ability of healthy ciliaris muscle must be improved in that an ability of ciliaris muscle is not damaged although the eye lens is damaged.
- the present invention is designed to solve such drawbacks of the prior art, and therefore an object of the present invention is to provide an intraocular lens that is configured so that an intraocular lens moves similarly to a natural eye lens.
- One embodiment of the present invention is achieved by providing an intraocular lens inserted inwardly into a capsular sac including an optic portion including a first optic body whose central region has a smaller thickness than a circumference of the central region and a second optic body coupled to the first optic body and whose central region has the same or higher thickness as/than the first optic body; and a haptic portion including a connection bar coupled to the optic portion and first support bar coupled to a circumference of the connection bar to be in contact with an inner surface of the capsular sac.
- the first optic body may be made of materials that are more flexible than the second optic body.
- the first optic body may include an inner surface and an outer surface and the inner surface and the outer surface may be a spherical surface or an aspheric surface, and the inner surface is preferably a spherical surface having a higher curvature than the outer surface, or a more aspheric surface than the outer surface.
- the first support bar preferably has a surface that is in contact with an inner surface of the capsular sac and has a round shape.
- the connection bar is preferably a shaft bar-shaped structural body coupled to at least two sections in a circumference of the optic portion.
- the first support bar is preferably a structural body for coupling at least two ends of the shaft bars arranged opposite to the optic portion of the connection bar.
- the first support bar is preferably a ring-shaped structural body for coupling all ends of the shaft bars arranged opposite to the optic portion of the connection bar.
- ends of the optic portion of the shaft bar preferably include a second support bar for coupling ends of the optic portion.
- both ends of the shaft bar preferably have a larger cross-sectional area than a central region of the shaft bar.
- an inner surface of the second support bar preferably has a concave shape toward the central region of the optic portion.
- the second support bar may be coupled to a circumference of the optic portion.
- the second support bar is preferably inserted inwardly into the optic portion.
- connection bar is preferably a disk-shaped structural body coupled to the entire section of the circumference of the optic portion.
- connection bar is preferably a disk-shaped structural body coupled to at least two sections of the circumference of the optic portion and divided into at least two sections.
- first support bar may be formed around an end of the disk-shaped connection bar.
- the optic portion and the first support bar may be made of flexible materials that is more flexible than a material of the connection bar.
- the optic portion and the first support bar may be made of the same flexible materials as the connection bar, and formed in a thinner thickness than the connection bar.
- the first support bar may be a structural body that is extended along an end of the connection bar, and may include a first face coming in contact with the inner surface of the capsular sac in at least one point; and a second face arranged opposite to the first face, and the first face may be provided at a length as much as 3/4 to 3 times of a length (d5, d 10) of a region where a zonule of Zinn is coupled to an outer surface of the capsular sac in a section where the first support bar is cut along a virtual plane in a visual axis direction (Y direction) of an eye lens.
- the first face may be made of flexible materials that more flexible than the second face.
- the first face may be made of the same flexible materials as the second face, and formed in a thinner thickness than the second face.
- the first face may be made of the same flexible materials as the second face, and formed in the same thickness as the second face.
- a surface of the first face may be rougher than the other surface.
- the surface of the first face may further include an adhesive for facilitating mounting of the capsular sac.
- the adhesive is preferably a tissue glue or a glue.
- a flowing space is preferably provided inside the intraocular lens.
- the flowing space is preferably provided at least between the first optic body and the second optic body.
- the flowing space preferably includes a first space portion provided between the first optic body and the second optic body; a second space portion provided inside the connection bar; and a third space portion provided inside the first support bar.
- the first space portion, the second space portion and the third space portion may be coupled to each other.
- the flowing space is preferably filled with one selected from the group consisting of liquid, gas, and fluent solid.
- the liquid is preferably one selected from the group consisting of water, silicone, sodium hyaluronate, chondroitin sulfate, hydroxypropyl methylcellulose and polyacrylamide.
- the gas is preferably one selected from the group consisting of air, nitrogen, helium, neon and argon.
- at least one face out of the first face and the second face is preferably protruded in a direction from the second face toward the first face.
- the first face preferably has an anterior portion and a posterior portion divided by an equator, which correspond respectively to an anterior capsule and a posterior capsule of the capsular sac, and the anterior portion preferably has a larger curvature than the posterior portion.
- the first face of the first support bar preferably has an extended length (dl) from the equator to an end point of the anterior portion and an extended length (d2) from the equator to an end point of the posterior portion, and the extended lengths (dl, d2) preferably range from 1 to 4.2 mm in the section where the intraocular lens is cut along a virtual plane in a visual axis direction (Y direction) of the eye lens.
- the extended length (dl) from the equator to the end point of the anterior portion is preferably smaller than the extended length (d2) from the equator to the end point of the posterior portion.
- a sectional shape of the first face of the first support bar preferably accords with an inner surface of the capsular sac when the sectional shape of the first face is in contact with the inner surface of the capsular sac in the section where the intraocular lens is cut along a virtual plane in a visual axis direction (Y direction) of the eye lens.
- the first space portion preferably has at least one convex surface.
- the first space portion preferably has at least one aspheric surface.
- the second optic body preferably has a thinner thickness in its central region than its circumference.
- the second optic body preferably includes an inner surface and an outer surface, and the inner surface and the outer surface may be spherical surface or an aspheric surface, and the inner surface is preferably a spherical surface or an aspheric surface that has a larger curvature than the outer surface.
- first optic body and the second optic body preferably have the same thickness, and preferably include sections that have an increasing thickness as their central regions approach their circumference, respectively.
- a material of the intraocular lens is preferably composed of one selected from the group consisting of silicone, silicone elastomer, silicone polymer, polydimethyl siloxane, polypropylene, polyimide, polybutester, polymethyl methacrylate (PMMA), Microplex PMMA, CQ-UV PMMA, acrylic resin, rigid acrylic, flexible acrylic, acrylic plastic, hydrophobic acrylic, hydrophilic acrylic, hydrophilic acrylic polymer, UV absorbing acrylate, methacrylate copolymer, butyl acrylate, polysiloxane elastomer, UV absorbing polysiloxane, collagen copolymer, gold, hydrogel, 2-hydroxyethyl methacrylate (HEMA), methyl methacrylate (MMA), cellulose acetate butylate (CAB), 2-hydroxy ethyl methacrylate (2-HAMA), n- vinyl pyrrolidone (NVP), polyvinyl pyrrolidone (PVP), methacrylic acid (
- the first optic body preferably includes a section that grows thicker as its equatorial region approaches its circumference.
- the intraocular lens according to the present invention has an effect to transfer a force to the intraocular lens, which is inserted inwardly into the ciliaris muscle, to allow the intraocular lens to operate like the natural eye lens, the force being generated from the ciliaris muscle and transferred through the zonule of Zinn and the capsular sac.
- the intraocular lens according to the present invention may be used for the intraocular lens operation used to treat cataract, presbyopia, high myopia, etc.
- FIG. 1 is a cross-sectional view showing a human eyeball.
- FIG. 2 is a cross-sectional view showing a structure of a natural eye lens.
- FIG. 3 and FIG. 4 are illustrative views showing interactions a zonule of Zinn and an eye lens when focused on a long distance and a short distance object, respectively.
- FIG. 5 is a perspective view showing an intraocular lens supporter according to the first embodiment of the present invention.
- FIG. 6 is a cross-sectional view taken from a line I-I' as shown in FIG. 5.
- FIG. 7 and FIG. 8 are illustrative views showing interactions of a zonule of Zinn, an intraocular lens and a capsular sac when focused respectively on a long distance and a short distance object according to the first embodiment of the present invention.
- FIG. 9 is a perspective view showing an intraocular lens according to the second embodiment of the present invention.
- FIG. 10 is a cross-sectional view taken from a line I-I' as shown in FIG. 9.
- FIG. 11 is perspective view showing an intraocular lens as a modified example of the intraocular lens according to the second embodiment of the present invention.
- FIG. 12 is a perspective view showing an intraocular lens according to the third embodiment of the present invention.
- FIG. 13 and FIG. 14 are illustrative views showing interactions of a zonule of Zinn, an intraocular lens and a capsular sac when focused on a respectively long distance and a short distance object according to the third embodiment of the present invention.
- FIG. 15 is a perspective view showing an intraocular lens according to the fourth embodiment of the present invention.
- FIG. 16 is a perspective view showing an intraocular lens according to the fifth embodiment of the present invention. [80] FIG. 17, FIG.
- FIG. 18 and FIG. 19 are is a perspective view showing an intraocular lens according to the sixth embodiment of the present invention, and cross-sectional views showing virtual planes in a visual axis direction of the eye lens.
- FIG. 20 is a cross-sectional view showing virtual planes in an equatorial direction of the eye lens of the intraocular lens according to the embodiment as shown in FIG. 17.
- FIG. 5 is a perspective view showing one embodiment intraocular lens (IOL) according to one embodiment of the present invention
- FIG. 6 is a cross-sectional view taken from a line I-I' as shown in FIG. 5.
- the intraocular lens 110 is an artificial eye lens that is inserted inwardly into a capsular sac, and the intraocular lens 110 according to this embodiment is divided into an optic portion 121 and a hap tic portion 123.
- the optic portion 121 is a portion that is arranged in the rear of a pupil in the eye and functions as a lens of a natural eye lens in a hard lens, and it has a convex lens shape
- the optic portion 121 includes a first optic body 121a that has an increasing thickness as its central region approaches its circumferential region, and a second optic body 121b coupled to the first optic body 121a, wherein a thickness of a central region of the second optic body 121b is identical to or thicker than the first optic body 121a.
- an inner surface of the first optic body 121a is a spherical surface having a larger curvature than an outer surface, or a more aspheric surface.
- the first optic body 121a and the second optic body 121b may have different convexity.
- the first optic body 121a and the second optic body 121b may be different from each other like an anterior surface and a posterior surface of a human eye lens, but a curvature of the anterior surface is preferably smaller than the posterior surface.
- shapes of the optic portion 121 are not limited thereto, but the optic portion 121 is preferably provided in a conventional convex lens shape. In this case, a diameter of the optic portion 121 may be provided in a diameter as much as 0.2 to 0.8 times of the total diameter of the intraocular lens 110.
- To constitute an optic portion 121 composed of two pieces of a first optic body 121a and a second optic body 121b is for the purpose of facilitating a shape deformation of the optic portion 121.
- a thickness (Ll) of the first optic body 121a is smaller than a thickness (L2) of the second optic body 121b in the section cut along a virtual plane in a visual axis direction (Y direction) of the eye lens. This is for the purpose that the shape deformation of the first optic body 121a is more induced than the second optic body 121b as if the shape deformation of the anterior surface is actually higher in the eye lens if a mechanical or fluent force is transferred to the optic portion 121, as described later.
- the thickness (L2) is preferably increased as the central region approaches the circumferential region if the front and rear surfaces of the central region ensure a flowing space with an aspheric surface while enhancing its functions using as an oil pressure manner as described later.
- the optic portion has a structure of a natural eye lens, and the central region of the optic portion makes it easier to make shape deformation than the circumferential region, thereby to function more similarly to the natural eye lens.
- the haptic portion 123 is coupled to the optic portion 121 from an edge region of the optic portion 121, and the haptic portion 123 has a plurality of shaft bars 122.
- the shaft bars 122 of the haptic portion 123 are provided in at least two numbers to transfer a force to the intraocular lens 110 in balance.
- an end 122b arranged opposite to the optic portion of the shaft bar 122 further includes a support bar 125 that is in contact with an inner surface of a capsular sac (not shown) (or, if an intraocular lens supporter is provided, an inner surface of the intraocular lens supporter (hereinafter, referred to as an inner surface of a capsular sac) means including an inner surface of the intraocular lens supporter).
- the support bar includes a first face 111 and a second face 113, each of which is extended from the end 122b of the shaft bar 122.
- the first face 111 is in contact with an equatorial region of the capsular sac in at least one point, and the second face 113 is formed to face the first face 111 and coupled to the end 122b arranged opposite to the optic portion of the shaft bar 122. At this time, at least the first face 111 is protruded in a direction from the second face 113 toward the first face 111, namely a direction from the inside toward the outside of the capsular sac.
- the first face 111 has an anterior portion I l ia and a posterior portion 11 Ib that are divided by the equator (E) to correspond respectively to the anterior capsule and the posterior capsule of the capsular sac.
- the anterior portion 11 Ia of the first face 111 has a larger curvature than the posterior portion 11 Ib.
- the section where the first face 111 is cut along a virtual plane in a visual axis direction (Y direction) of the eye lens is formed in the same shape as a sectional shape of an equatorial region of a natural eye lens.
- the anterior surface in the central region of the eye lens has a smaller curvature than the posterior surface, but has a reverse shape as it approaches an equatorial region.
- the first face 111 is formed in the same sectional shape as the inherent eye lens of a patient that undergoes a surgical operation.
- a photograph of a sectional shape of the patient eye lens before the surgical operation may be taken using ultrasonic imaging, CT, and MRI.
- the first face 111 has a sectional shape between mydriasis and miosis, but may have a shape that accord with the sectional shape of the eye lens having a pupil size of 3 to 4 mm.
- the first face 111 accords with a shape of the inner surface in the equatorial region of the capsular sac.
- the first face 111 is preferably provided in a length as much as 3/4 to 3 times of a length (d5, see FIG. 7) of a region where a zonule of Zinn is coupled to an outer surface of the capsular sac.
- a force transferred to the intraocular lens with the movement of the zonule of Zinn is not effectively transferred if the first face 111 is formed in a smaller length range than 3/4 times, and an optic portion of the intraocular lens may be covered if the first face 111 is formed in a smaller length range than 3 times.
- an extended length (dl) from the equator (E) to an end point of the anterior portion I l ia, and an extended length (d2) from the equator (E) to an end point of the posterior portion 11 Ib may generally range from 1 to 4.2 mm in the section where the eye lens of the intraocular lens 110 is cut along a virtual plane in a visual axis direction (Y direction) of the eye lens.
- the support bar 125 is provided in an inner position than a point where the second zonule portion 171 of the zonule of Zinn is coupled to the capsular sac if the extended length is less than 1 mm, and therefore a force is not suitably transferred to the intraocular lens 110 according to the movement of the zonule of Zinn induced in the ciliaris muscle, which leads to insufficient volume change in the intraocular lens 110.
- the total length of the section where the first face is cut along a virtual plane in a visual axis direction (Y direction) of the eye lens will range from 2 to 8.4mm.
- a roughness of the first face 111 may be improved or a separate adhesive may be used to facilitate mounting of the intraocular lens supporter 110 in the capsular sac. Therefore, the intraocular lens supporter 110 may be fixed in a stable position.
- a tissue glue or glue may be, for example, used as the adhesive.
- the second face 113 is a surface to which the shaft bar 122 of the intraocular lens
- F2 is a constant determined by a length ratio of d3 and d4.
- the length ratio of d3 and d4 may be varied according to the ability of the zonule of Zinn in patients, and a length of d4 is preferably longer as much as 0.4 to 1 times than a length of d3.
- the optic portion 121 in the intraocular lens 110 is preferably made of flexible materials that are more flexible than the materials constituting the shaft bar 122 of the hap tic portion 123, or in a thinner thickness. This is for the purpose of deforming a shape of the optic portion 121 effectively by a force transferred by the movement of the zonule of Zinn that is induced in the ciliaris muscle.
- f lexible means that a material is so soft to deform easily.
- the shaft bar 122 of the haptic portion 123 is made of a relatively more rigid material than the optic portion 121, or has suitable elasticity and restoring force for the mechanical deformation. In this case, it is possible to operate on an eye by cutting a relatively smaller eyeball.
- the optic portion 121 and the haptic portion 123 are made of different materials as described above, and therefore the intraocular lens 110 may be composed of a plurality of pieces. Also, the optic portion 121 and the haptic portion 123 may be composed of the same materials, but they may have different flexibility.
- the flexibility of the shaft bar 122 of the haptic portion 123 may be identical to, or different from the flexibility of the support bar 125 of the haptic portion 123, and the shaft bar 122 and the support bar 125 may be composed of at least two pieces, or composed of one piece.
- the support bar 125 is a region that directly reflects a volume change in the intraocular lens supporter as described later according to the shape deformation of the zonule of Zinn, and therefore the shape deformation of the support bar 125 is made more effectively if the flexible materials that are more flexible than the shaft bar 122 are used.
- the intraocular lens is composed of pieces, the pieces may be attached to each other using an adhesive, a laser and a heat.
- a material of the intraocular lens supporter 110 may include silicone, silicone elastomer, silicone polymer, polydimethyl siloxane, polypropylene, polyimide, polybutester, Polymethyl methacrylate (PMMA), Microplex PMMA, CQ-UV PMMA, acrylic resin, rigid acrylic, flexible acrylic, acrylic plastic, hydrophobic acrylic, hy- drophilic acrylic, hydrophilic acrylic polymer, UV absorbing acrylate, methacrylate copolymer, butyl acrylate, polysiloxane elastomer, UV absorbing polysiloxane, collagen copolymer, gold, hydrogel, 2-hydroxy ethyl methacrylate (HEMA), methyl methacrylate (MMA), cellulose acetate butylate (CAB), 2-hydroxy ethyl methacrylate (2-HAMA), n-vinyl pyrrolidone (NVP), polyvinyl pyrrolidone (PVP), methacryl
- FIG. 7 and FIG. 8 are illustrative views showing interactions of a zonule of Zinn, an intraocular lens and a capsular sac when focused on a long distance and a short distance object according to the first embodiment of the present invention.
- the zonule of Zinn 170 is coupled to the outer surface of the capsular sac 180, and the zonule of Zinn 170 is coupled to a region around the equator of the capsular sacl80, and therefore a region to which the zonule of Zinn 170 is coupled is referred to as a connection region for zonule of Zinn (Z) in this application.
- a first zonule portion 173 coupled to the center of the connection region for zonule of Zinn (Z) in the capsular sac 180 is pulled taut, and a second zonule portion 171 coupled to a circumference of the equatorial region of the connection region for zonule of Zinn (Z) in the capsular sac 180 is relaxed.
- the equatorial region of the capsular sac 180 is subject to a force generated when extended in an X direction, and the intraocular lens 120 with elasticity arranged inside the capsular sac 180 is also extended in the same direction, which leads to the convex intraocular lens 120.
- the use of the intraocular lens supporter 110 according to this embodiment makes it the intraocular lens 110 possible to control its thickness like the natural eye lens. That is to say, as a thickness of the natural eye lens is controlled by the action of the capsular sac 180 coupled to the zonule of Zinn, a thickness of the intraocular lens 110 according to this embodiment may also be controlled.
- the intraocular lens according to this embodiment has a lower transfer ability in the movement of the zonule of Zinn, thanthe second embodiment, since the intraocular lens according to this embodiment is deformed machanically only, and therefore the intraocular lens according to this embodiment will be suited for patients whose zonule of Zinn move more smoothly.
- FIG. 9 is a perspective view showing one embodiment of an intraocular lens (IOL) according to one aspect of the present invention
- FIG. 10 is a cross-sectional view taken from a line I-I' as shown in FIG. 9.
- IOL intraocular lens
- the optic portion 221 includes a first optic body 221a having an increasing thickness as its central region approaches its equatorial region, and a second optic body 221b coupled to the first optic body 221a and having at least a thicker thickness in the central region than the first optic body 221a.
- the first optic body 221a includes an inner surface 22 lab and an outer surface 221aa, wherein at least the inner surface 22 lab preferably is a spherical surface having a larger curvature than the outer surface 221aa, or a more aspheric surface.
- an optic portion 121 composed of two pieces of a first optic body 121a and a second optic body 121b is for the purpose of facilitating a shape deformation of the optic portion 121.
- a thickness (Ll) of the first optic body 221a is smaller than a thickness (L2) of the second optic body 221b in the section cut along a virtual plane in a visual axis direction (Y direction) of the eye lens. This is for the purpose that the shape deformation of the first optic body 121a is more induced than the second optic body 121b as if the shape deformation of the anterior surface is actually higher in the eye lens if a mechanical or fluent force is transferred to the optic portion 221.
- An empty flowing space 231 is provided between the first optic body 221a and the second optic body 221b.
- the size and shape of the flowing space 231 is associated with the shape of the inner surface of the first optic body 221a and the second optic body 221b.
- the flowing space 231 is small, at least an anterior surface and a posterior surface of the flowing space 231 is protruded toward the first optic body 221a, and therefore the flowing space 231 starts to be formed into a convex lens shape with an increasing curvature of the anterior surface, and the first face is formed a convex lens shape that is protruded toward the first optic body 221a and the second face is formed a convex lens shape that is protruded toward the second optic body 221b as the flowing space 250 increases in volume.
- the anterior surface and the posterior surface are generally protruded toward a pupil, but the anterior surface is a spherical surface having a larger curvature, or a more aspheric surface, which leads to a convex lens shape as a whole.
- the thickness (L2) of the second optic body 221b is desirable to have a larger thickness in its central region if the second optic body 221b is mechanically deformed without any of the flowing space as in the above-mentioned embodiment.
- the second optic body 221b has a flowing space, namely if the anterior/posterior surfaces has a flowing space ensured in a large scale and formed inside the optic body with an aspheric surface, the second optic body 221b preferably has an increasing thickness as its central region approaches its equatorial region. This is also for the purpose that the optic portion has a structure of a natural eye lens, and the central region of the optic portion makes it easier to shape deformation than the circumferential region, thereby to function more similarly as the natural eye lens.
- the hap tic portion 223 is coupled to the optic portion 221 from an edge of the optic portion 221, and the hap tic portion 223 is composed of a plurality of shaft bars 222 and a support bar 225.
- the shaft bars 222 of the hap tic portion 223 may be provided in at least two numbers to transfer a force to the intraocular lens in balance.
- both ends 222a, 222b of the shaft bar 222 preferably has a larger cross-sectional area than the central region. As a result, both ends 222a, 222b of the shaft bar 222 are stably coupled respectively to the optic portion 221 and the support bar 225.
- the support bar 225 is a ring-shaped body to which the end 222b arranged opposite to the optic portion 221 of the shaft bar 222 and transferring a force transferred from the capsular sac in more balance, and includes a first face 211 and a second face 213.
- the shape of the support bar 225 may be widely varied, and shapes are not limited if the shapes couples at least two ends 222b of the shaft bar 222. That is to say, it is possible to be formed as shown in FIG. 11.
- a force transferred from the zonule of Zinn is mechanically transferred to the intraocular lens 210 to control a thickness of the optic portion 221 of the intraocular lens 210.
- the materials of the intraocular lens may be identical to those of the first embodiment, and their interactions may be easily conducted from the disclosure of the first embodiment by those in the art, and their descriptions are omitted for clarity.
- FIG. 12 is a cross-sectional view showing a virtual plane in a visual axis direction of an eye lens of the intraocular lens according to the third embodiment of the present invention.
- the intraocular lens 310 according to the third embodiment has a similar structure to the intraocular lens according to the first embodiment or the second embodiment, but the intraocular lens 310 according to the third embodiment is different from the intraocular lens according to the first embodiment or the second embodiment in that a flowing space 350 filled with a fluid is provided inside the intraocular lens 310, and the flowing space 350 may be filled with the fluid.
- the size and shapes of the flowing space 350 may be widely varied.
- the size and shapes of the flowing space 231 are related to the shape of the inner surfaces of the first optic body 221a and the second optic body 221b. Both of the anterior surface and the posterior surface of the flowing space 231 start to be formed in a convex lens shape that is protruded toward the first optic body 221a as the flowing space 231 gets small, whereas the anterior surface is formed in a convex lens shape that is protruded toward the first optic body 221a and the posterior surface is formed in a convex lens shape that is protruded toward the second optic body 221b as the flowing space increases in volume.
- both of the anterior surface and the posterior surface are preferably formed in a convex lens shape with an aspheric surface.
- the fluid filled in the flowing space 350 includes water, air, silicone, viscoelastic materials.
- examples of the viscoelastic materials, as used herein, may include sodium hyaluronate, chondroitin sulfate, hydroxypropyl methylcellulose, poly- acrylamide, etc.
- the flowing space 330 may be composed of a first space portion 331 formed inside the optic portion 321; second space portion 333 formed inside the connection bar 322; and a third space portion 335 formed inside the support bar 325.
- the first space portion 331, the second space portion 333 and the third space portion 335 may be coupled, or not coupled to each other, but it is easy to deform the in- traocular lens 310 using a fluent force if the first space portion 331, the second space portion 333 and the third space portion 335 are coupled to each other.
- the first space portion 331, the second space portion 333 and the third space portion 335 are coupled to each other. Therefore, the fluid filled in the flowing space 330 allows the first space portion 331, the second space portion 333 and the third space portion 335 of the flowing space 330 to move by external forces.
- the fluid filled in the flowing space 350 includes water, air, inert gas, silicone, viscoelastic materials.
- inert gas examples include nitrogen, helium, neon, argon, etc.
- viscoelastic materials examples include sodium hyaluronate, chondroitin sulfate, hydroxypropyl methylcellulose, poly- acrylamide, etc.
- the optic portion 321 may function as a lens with a low power of glasses due to the low refractive index when the first space portion 331 is filled with gas or water, and therefore it is possible to manufacture a negative lens used for the extremely myopic operations.
- the second space portion 333 is a space formed in the shaft bar 322.
- the shaft bar 322 functions as a kind of a connection tube to allow a fluid to flow between the first space portion 331 and the third space portion 335.
- the third space portion 335 is a space formed in the support bar 325 as described above, and the third space portion 335 is a region that directly reflects a volume change in the capsular sac. That is to say, the intraocular lens 310 allows a fluid to flow in the flowing space according to the force transferred from the zonule of Zinn since it has the flowing space 330. For example, when focused on a short distance object, the fluid is collected inside the optic portion 321 of the intraocular lens 310, and therefore the optic portion 321 may be deformed more effectively.
- FIG. 13 and FIG. 14 are illustrative views showing interactions of a zonule of Zinn, an intraocular lens and a capsular sac when focused onrespectively a long distance and a short distance object according to the third embodiment of the present invention.
- the equatorial region of the capsular sac 380 is extended in an equatorial direction (X direction) of the eye lens, and a shape of the first face 311 of the support bar in the intraocular lens 310 that is in contact with the capsular sac is also extended in the same direction, which leads to the less convex optic portion 321.
- the fluid filled in the flowing space 330 of the intraocular lens 310 is also subject to external forces, and the intraocular lens 310 is more extended in an equatorial direction of the eye lens when focused on a a long distance object, and therefore the fluid in the flowing space 330 is distributed at a higher amount in the third space portion 335 than the first space portion 331 and the second space portion 333. Therefore, the shapes of the optic portions 321;321a, 321b of the intraocular lens 310 are deformed more effectively to make the optic portion 321 less convex.
- the equatorial region of the capsular sac 380 is protruded in a visual axis direction (Y direction) of the eye lens, and therefore the intraocular lens 310 with elasticity arranged inside the capsular sac 380 is also extended in the same direction (Y direction) to be deformed into a suitable shape to see at a short distance.
- the fluid filled in the flowing space of the intraocular lens 310 is also subject to the external forces.
- the fluid in the third space portion 335 is gathered in the first space portion 331 through the second space portion 333 since the external forces are applied to a flexible region of the support bar of the intraocular lens 310 when focused on a short distance, and therefore the shape of the optic portion 321 of the intraocular lens 310 is deformed more effectively to make the optic portion more convex.
- the first optic body 321a is formed in a smaller thickness than the second optic body 321b, and therefore the optic portion 321 is made more convex toward the first optic body 321a than the second optic body 321b.
- the intraocular lens may be deformed similarly to an actual eye structure.
- the intraocular lens according to this embodiment may effectively control a shape of the intraocular lens if an ability of the ciliaris muscle is lowered since a force transferred from the zonule of Zinn is mechanically transferred to the intraocular lens 310 and also transferred to the intraocular lens 310 by means of the oil pressure to effectively control a thickness of the optic portion 321 of the intraocular lens 310.
- an interaction force by a mechanical force complementarily acts together with an interaction force by an oil pressure in this embodiment.
- the use of more flexible materials, thinner materials or fluids as more flexible media makes the deformation of the optic portion 321 by the oil pressure more increased, and the use of less flexible materials, thicker materials or fluids as more compact media makes the deformation of the optic portion 321 by the mechanical force more increased.
- the deformation of the optic portion 321 by the mechanical force is varied with different interaction forces according to the shapes and positions of the above- mentioned materials inserted into the optic portion 321 by the end 322a in the optic portion of the shaft bar 322.
- the shape deformation of the optic portion 321 is made in a large scale but its stability is low if the interaction force is high, whereas the shape deformation of the optic portion 321 is made in a small scale but its stability is high if the interaction force is low.
- the suitable materials and fluids may be selected to adjust a control ability of the intraocular lens since the deformation of the optic portion 321 is made in a higher level by the oil pressured other than the mechanical force.
- the intraocular lens with very high control ability has a disadvantage that it has a short lift span due to the repeated excessive deformation and the thin materials of the optic portion, but it is suitable for old patients who has a poor control ability of the eye. Accordingly, the intraocular lens according to this embodiment may control a thickness of the optic portion 321 of the intraocular lens since a force transferred from the zonule of Zinn is transferred to the intraocular lens mechanically or fluently.
- materials of the intraocular lens may be applied in the same manner as described above.
- FIG. 15 is a perspective view showing an intraocular lens according to the fourth embodiment of the present invention.
- the connection bar 422 is configured with a disk-shaped structural body in the fourth embodiment.
- the support bar 425 formed in an end of the connection bar 422 may be a ring-shaped structural body formed in the entire circumference of the disk-shaped structural body, or formed in some section of the circumference.
- FIG. 16 is a perspective view showing an intraocular lens according to the fifth embodiment of the present invention.
- the connection bar 522 is composed of divided disk-shaped structural bodies that are coupled to one section of the optic portion 521 in the fifth embodiment.
- the support bar 525 formed in an end of the connection bar 522 may be a ring- shaped structural body formed in the entire circumference of the disk-shaped structural body, or formed in some section of the circumference.
- FIG. 17 is a perspective view showing an intraocular lens according to the sixth embodiment of the present invention
- FIGs. 18 and 19 are cross-sectional views taken from lines I-I' and II- II' as shown in FIG. 17, respectively.
- FIG. 20 is a cross-sectional view where the intraocular lens as show in FIG. 17 is cut along a virtual plane in an equatorial direction of the eye lens. Referring to FIG. 17 and 20, this embodiment is different from the above-mentioned embodiments in that the intraocular lens according to this embodiment has a second support bar 627.
- the optic portion 621 includes a first optic body 621a and a second optic body 621b, and the hap tic portion 623 is then confugred to include a first support bar 625, a second support bar 627 and a shaft bar 622.
- the optic portion 621 includes a first optic body 621a and a second optic body 621b, which have an increasing thickness as its central region approaches its equatorial region.
- the posterior surface of the first optic body 621a and the anterior surface of the second optic body 621b are preferably aspheric surfaces.
- first optic body 621a and the second optic body 621b may have different convexity. That is to say, the first optic body 621a and the second optic body 621b may be different from each other like an anterior surface and a posterior surface of a human eye lens, but a curvature of the anterior surface is preferably smaller than the posterior surface.
- shapes of the optic portion 621 are not limited thereto, but the optic portion 621 is preferably provided in a conventional convex lens shape.
- a diameter of the optic portion 621 may be provided in a diameter as much as 0.2 to 0.8 times of the total diameter of the intraocular lens 610.
- an optic portion 621 composed of two pieces of a first optic body 621a and a second optic body 621b is for the purpose of facilitating a shape deformation of the optic portion 621.
- a first space portion 631 through which a fluid may flow is included between the first optic body 621a and the second optic body 621b of the optic portion 621.
- the hap tic portion 623 is coupled to the optic portion 621 so that some portion of the optic portion 621 is included inside the hap tic portion 623, and the hap tic portion 623 i s composed of a plurality of shaft bars 622, a first support bar 625 and a second support bar 627.
- the shaft bars 622 of the hap tic portion 623 is provided in at least two numbers to transfer a force to the intraocular lens in balance, and includes a second space portion 633 as a flowing space formed inside of it.
- the first support bar 625 is provided to transfer a force transferred from the capsular sac in more balance, as described above in the above embodiments.
- the first support bar 625 has a first face 641 coming in contact with the inner surface of the capsular sac in at least one point; and a second face 643 arranged opposite to the first face 641, and, as the ring-shaped structure to which an end 622b arranged opposite to the optic portion of the shaft bar 622, its outer surface is preferably in a circular shape, and its inside may include a third space portion 635.
- the first support bar 625 is preferably provided at a length as much as at least 3/4 to 3 times of a length of a section in a region where a zonule of Zinn is coupled to an outer surface of the capsular sac.
- the second support bar 627 couples ends 622a in the optic portion of the shaft bar 622 to the hap tic portion of the intraocular lens 610 to give stability to the shaft bar 622, thereby to transfer a force, transferred through the shaft bar 622, to the optic portion 621 in more balance.
- the second support bar 627 may be a structural body that couples the ends 622a in the optic portion of the shaft bar 622, or couples shaft bars 622 around the ends to each other.
- a surface where the second support bar 627 is in contact with the optic portion preferably has a shape corresponding to an equatorial surface of the optic portion, namely a shape that is concave toward the center of the optic portion.
- the end 622a in the optic portion of the shaft bar 622 maximizes its mechanical control ability, and some of the end 622a may be included inside the optic portion 621 for the purpose of the stability of the optic portion 621 in manufacturing the shaft bar 622.
- the first optic body 621a and the second optic body 621b are met and pressured to form an optic junction 621c in a circumferential region regardless of the flowing space.
- the optic junction 621c functions to reduce a mechanical or oil pressure deformation in the optic portion 621, but to cause a mechanical or oil pressure deformation more effectively and intensively in the central region where the first optic body 621a and the second optic body 621b are attached to each other.
- shapes coupled to the optic portion of the shaft bar 622 may be widely varied, and the control ability by the mechanical force may be different according to the shapes.
- the deformation of the optic portion 621 by the mechanical force is varied with different interaction forces according to the shapes and positions of the above-mentioned materials surrounding the circumference of the optic portion 621 by means of the end 622a in the optic portion of the shaft bar 622.
- the shape deformation of the optic portion 621 is made in a large scale but its stability is high if the interaction force is high, whereas the shape deformation of the optic portion 621 is made in a small scale but its stability is very high if the interaction force is low.
- the end 622a in the optic portion of the shaft bar 622 may be in various shapes such as a convex cone, a convex sphere, circular cylinder, a concave sphere and a concave cone, and the above-mentioned control ability by the mechanical force is varied according to the shapes.
- the end 622a in the optic portion has a conical shape toward the optic portion 621, as shown in FIG. 18, and has a cylindrical shape in an exploded diagram of FIG. 20.
- the shaft bar 622 of the haptic portion 623 is made of relatively more rigid materials than the optic portion 621, or the first support bar 625 and the second support bar 627, or has suitable elasticity and restoring force for the mechanical deformation.
- materials con- stituting the first face 641 of the first support bar 625 and the optic portion 621 are preferably more flexible than materials constituting the second face 643 of the first support bar 625 and the second support bar 627.
- the term flexible means that a material is so soft to deform easily.
- the second face 643 is provided in a larger thickness than the first face 641. This is for the purpose of functioning as a wheel capable of making the second face 643 less flexible and strongly fixing the shaft bar 622 in the first support bar 625 at the same time.
- the movement of the zonule of Zinn may be reflected more sensitively since a flowing space is provided inside the optic portion 621 and the hap tic portion 623, as described above.
- the intraocular lenses according to the above-mentioned embodiments of the present invention may be formed into one piece as described above, or formed with several pieces.
- the intraocular lens may be manufactured using various plastic forming methods, and if the intraocular lens is formed with several pieces, it may also be easily manufactured through the attachment of the pieces using an adhesive, a heat, a laser, etc.
Abstract
Description
Claims
Priority Applications (9)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US12/530,242 US8603165B2 (en) | 2007-03-08 | 2007-09-21 | Intraocular lens |
EA200901214A EA016269B1 (en) | 2007-03-08 | 2007-09-21 | Intraocular lens |
CN2007800519882A CN101641060B (en) | 2007-03-08 | 2007-09-21 | Intraocular lens |
BRPI0721395-6A2A BRPI0721395A2 (en) | 2007-03-08 | 2007-09-21 | Intraocular Lens |
CA2678777A CA2678777C (en) | 2007-03-08 | 2007-09-21 | Intraocular lens |
JP2009552574A JP5266262B2 (en) | 2007-03-08 | 2007-09-21 | Intraocular lens |
EP07808410.0A EP2131786B1 (en) | 2007-03-08 | 2007-09-21 | Intraocular lens |
MX2009009588A MX2009009588A (en) | 2007-03-08 | 2007-09-21 | Intraocular lens. |
IL200590A IL200590A (en) | 2007-03-08 | 2009-08-26 | Intraocular lens |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
KR10-2007-0022871 | 2007-03-08 | ||
KR1020070022871A KR100807940B1 (en) | 2007-03-08 | 2007-03-08 | Intraocular lens |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2008108524A1 true WO2008108524A1 (en) | 2008-09-12 |
Family
ID=39383512
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/KR2007/004632 WO2008108524A1 (en) | 2007-03-08 | 2007-09-21 | Intraocular lens |
Country Status (11)
Country | Link |
---|---|
US (1) | US8603165B2 (en) |
EP (1) | EP2131786B1 (en) |
JP (1) | JP5266262B2 (en) |
KR (1) | KR100807940B1 (en) |
CN (1) | CN101641060B (en) |
BR (1) | BRPI0721395A2 (en) |
CA (1) | CA2678777C (en) |
EA (1) | EA016269B1 (en) |
IL (1) | IL200590A (en) |
MX (1) | MX2009009588A (en) |
WO (1) | WO2008108524A1 (en) |
Cited By (27)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20100179653A1 (en) * | 2009-01-09 | 2010-07-15 | Claudio Argento | Intraocular Lenses and Methods of Accounting for Capsule Size Variability and Post-Implant Changes in the Eye |
US20110029074A1 (en) * | 2009-08-03 | 2011-02-03 | Abbott Medical Optics Inc. | Fixation of ophthalmic implants |
US20110054600A1 (en) * | 2009-06-26 | 2011-03-03 | Abbott Medical Optics Inc. | Accommodating intraocular lenses |
WO2011031557A1 (en) * | 2009-08-27 | 2011-03-17 | Abbott Medical Optics Inc. | Fixation of opthalmic implants |
JP2012509751A (en) * | 2008-11-26 | 2012-04-26 | アニユー・オプテイクス・インコーポレイテツド | Haptic device for intraocular lens |
US8216310B2 (en) | 2007-09-28 | 2012-07-10 | Abbott Medical Optics Inc. | Polymer compositions suitable for intraocular lenses and related methods |
US8232363B2 (en) | 2007-12-21 | 2012-07-31 | Abbott Medical Optics Inc. | Silicone containing polymeric materials |
WO2011085349A3 (en) * | 2010-01-11 | 2012-09-13 | Abbott Medical Optics Inc. | Fixation of opthalmic implants |
US20130131794A1 (en) * | 2009-01-09 | 2013-05-23 | Terah Whiting Smiley | Accommodating Intraocular Lenses and Methods of Use |
WO2013170125A1 (en) * | 2012-05-10 | 2013-11-14 | Abbott Medical Optics Inc. | Accommodating intraocular lens with a compressible inner structure |
GB2518378A (en) * | 2013-09-18 | 2015-03-25 | Timothy Paine | Intraocular Lenses |
US9039760B2 (en) | 2006-12-29 | 2015-05-26 | Abbott Medical Optics Inc. | Pre-stressed haptic for accommodating intraocular lens |
US9156949B2 (en) | 2007-12-21 | 2015-10-13 | Abbott Medical Optics Inc. | Silicone containing polymeric materials |
US9271830B2 (en) | 2002-12-05 | 2016-03-01 | Abbott Medical Optics Inc. | Accommodating intraocular lens and method of manufacture thereof |
US9603703B2 (en) | 2009-08-03 | 2017-03-28 | Abbott Medical Optics Inc. | Intraocular lens and methods for providing accommodative vision |
WO2017060537A3 (en) * | 2015-10-08 | 2017-06-22 | Optotune Ag | Lens comprising an adjustable focus length |
US9814570B2 (en) | 1999-04-30 | 2017-11-14 | Abbott Medical Optics Inc. | Ophthalmic lens combinations |
US9968441B2 (en) | 2008-03-28 | 2018-05-15 | Johnson & Johnson Surgical Vision, Inc. | Intraocular lens having a haptic that includes a cap |
US10010405B2 (en) | 2008-11-26 | 2018-07-03 | Anew Aol Technologies, Inc. | Haptic devices for intraocular lens |
US10485657B2 (en) | 2012-06-04 | 2019-11-26 | Alcon Pharmaceuticals, Ltd. | Intraocular lens inserter |
US10835373B2 (en) | 2002-12-12 | 2020-11-17 | Alcon Inc. | Accommodating intraocular lenses and methods of use |
US11382736B2 (en) | 2017-06-27 | 2022-07-12 | Alcon Inc. | Injector, intraocular lens system, and related methods |
US11406490B2 (en) | 2012-01-24 | 2022-08-09 | Alcon Inc. | Modular intraocular lens designs and methods |
US11406491B2 (en) | 2015-01-30 | 2022-08-09 | Alcon Inc | Modular intraocular lens designs, tools and methods |
US11446138B2 (en) | 2014-02-18 | 2022-09-20 | Alcon Inc. | Modular intraocular lens designs, tools and methods |
US11484402B2 (en) | 2011-11-08 | 2022-11-01 | Alcon Inc. | Accommodating intraocular lenses |
US11707354B2 (en) | 2017-09-11 | 2023-07-25 | Amo Groningen B.V. | Methods and apparatuses to increase intraocular lenses positional stability |
Families Citing this family (40)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8328869B2 (en) | 2002-12-12 | 2012-12-11 | Powervision, Inc. | Accommodating intraocular lenses and methods of use |
US9872763B2 (en) | 2004-10-22 | 2018-01-23 | Powervision, Inc. | Accommodating intraocular lenses |
WO2008103798A2 (en) * | 2007-02-21 | 2008-08-28 | Powervision, Inc. | Polymeric materials suitable for ophthalmic devices and methods of manufacture |
US20080306587A1 (en) * | 2007-02-21 | 2008-12-11 | Jingjong Your | Lens Material and Methods of Curing with UV Light |
US8314927B2 (en) * | 2007-07-23 | 2012-11-20 | Powervision, Inc. | Systems and methods for testing intraocular lenses |
US8668734B2 (en) | 2010-07-09 | 2014-03-11 | Powervision, Inc. | Intraocular lens delivery devices and methods of use |
US8968396B2 (en) | 2007-07-23 | 2015-03-03 | Powervision, Inc. | Intraocular lens delivery systems and methods of use |
EP2178462B1 (en) * | 2007-07-23 | 2014-04-02 | PowerVision, Inc. | Post-implant lens power modification |
WO2009015226A2 (en) | 2007-07-23 | 2009-01-29 | Powervision, Inc. | Accommodating intraocular lenses and methods of use |
EP2647353B1 (en) | 2007-07-23 | 2014-12-31 | PowerVision, Inc. | Lens delivery system |
US8043372B2 (en) * | 2008-10-14 | 2011-10-25 | Abbott Medical Optics Inc. | Intraocular lens and capsular ring |
US8447086B2 (en) | 2009-08-31 | 2013-05-21 | Powervision, Inc. | Lens capsule size estimation |
JP2013520291A (en) | 2010-02-23 | 2013-06-06 | パワーヴィジョン・インコーポレーテッド | Liquid for accommodation type intraocular lens |
WO2012129407A2 (en) | 2011-03-24 | 2012-09-27 | Powervision, Inc. | Intraocular lens loading systems and methods of use |
EP4052681A3 (en) * | 2011-11-08 | 2023-01-04 | Alcon Inc. | Accommodating intraocular lenses and methods of use |
DE102012016892A1 (en) * | 2012-08-24 | 2014-02-27 | Be Innovative Gmbh | Intraocular lens, in particular ciliary intraocular lens |
US9195890B2 (en) * | 2012-12-10 | 2015-11-24 | Sri International | Iris biometric matching system |
US10441676B2 (en) | 2013-01-15 | 2019-10-15 | Medicem Institute s.r.o. | Light-adjustable hydrogel and bioanalogic intraocular lens |
PL2945569T3 (en) | 2013-01-15 | 2019-04-30 | Medicem Inst S R O | Bioanalogic intraocular lens |
EP3785668A1 (en) | 2013-03-15 | 2021-03-03 | Alcon Inc. | Intraocular lens storage and loading devices and methods of use |
EP2976042B1 (en) * | 2013-03-21 | 2023-09-13 | Shifamed Holdings, LLC | Accommodating intraocular lens |
CN103340703A (en) * | 2013-06-17 | 2013-10-09 | 无锡蕾明视康科技有限公司 | Implantable myopia lens and preparation method thereof |
MX2016001300A (en) * | 2013-07-29 | 2016-08-18 | Oculentis Holding Bv | Intraocular lens structure. |
CN110279494B (en) * | 2014-08-26 | 2023-02-17 | 施菲姆德控股有限责任公司 | Accommodating intraocular lens |
EP3198913A4 (en) | 2014-09-24 | 2018-05-23 | Princeton Identity, Inc. | Control of wireless communication device capability in a mobile device with a biometric key |
SG11201704097XA (en) | 2014-12-03 | 2017-06-29 | Princeton Identity Inc | System and method for mobile device biometric add-on |
US11129709B2 (en) * | 2019-01-28 | 2021-09-28 | Jitander Dudee | Accommodating intraocular lens assembly |
ES2686472T3 (en) | 2015-03-10 | 2018-10-18 | Consejo Superior De Investigaciones Científicas | Photochemically induced coupling of intraocular implants |
KR101718075B1 (en) * | 2015-05-29 | 2017-04-04 | 주식회사 로섹 | Lens assembly |
US10172706B2 (en) * | 2015-10-31 | 2019-01-08 | Novartis Ag | Intraocular lens inserter |
WO2017079733A1 (en) | 2015-11-06 | 2017-05-11 | Powervision, Inc. | Accommodating intraocular lenses and methods of manufacturing |
WO2017090615A1 (en) * | 2015-11-25 | 2017-06-01 | 株式会社Xlems Technologies | Adjustable intraocular lens |
EP3403217A4 (en) | 2016-01-12 | 2019-08-21 | Princeton Identity, Inc. | Systems and methods of biometric analysis |
US10373008B2 (en) | 2016-03-31 | 2019-08-06 | Princeton Identity, Inc. | Systems and methods of biometric analysis with adaptive trigger |
US10366296B2 (en) | 2016-03-31 | 2019-07-30 | Princeton Identity, Inc. | Biometric enrollment systems and methods |
WO2018187337A1 (en) | 2017-04-04 | 2018-10-11 | Princeton Identity, Inc. | Z-dimension user feedback biometric system |
EP3634309B1 (en) | 2017-06-07 | 2023-05-24 | Shifamed Holdings, LLC | Adjustable optical power intraocular lenses |
US10716661B2 (en) | 2017-07-17 | 2020-07-21 | Verily Life Sciences Llc | Accommodating intraocular lens with meniscus |
JP2020529073A (en) | 2017-07-26 | 2020-10-01 | プリンストン・アイデンティティー・インコーポレーテッド | Biosecurity systems and methods |
JP7440417B2 (en) | 2017-11-01 | 2024-02-28 | アルコン インコーポレイティド | Intraocular lens and peripheral stabilization method |
Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4451938A (en) * | 1982-09-24 | 1984-06-05 | Kelman Charles D | Intraocular lens and method of positioning the same in an eye |
US5152789A (en) * | 1991-05-14 | 1992-10-06 | Allergan, Inc. | Fixation member for an intraocular lens |
US6051024A (en) * | 1995-10-06 | 2000-04-18 | Cumming; J. Stuart | Intraocular lenses with fixated haptics |
US20030135272A1 (en) * | 2002-01-14 | 2003-07-17 | Advanced Medical Optics, Inc. | Accommodating intraocular lens with integral capsular bag ring |
US7048760B2 (en) * | 1995-02-15 | 2006-05-23 | Medevec Licensing B.V. | Accommodating intraocular lens having T-shaped haptics |
US7097660B2 (en) * | 2001-12-10 | 2006-08-29 | Valdemar Portney | Accommodating intraocular lens |
Family Cites Families (19)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4666446A (en) * | 1986-05-06 | 1987-05-19 | Koziol Jeffrey E | Intraocular lens with converging and diverging optical portions |
US4932966A (en) * | 1988-08-15 | 1990-06-12 | Storz Instrument Company | Accommodating intraocular lens |
DE4403326C1 (en) * | 1994-02-03 | 1995-06-22 | Hans Reinhard Prof Dr Koch | Intraocular lens arrangement for astigmatism correction |
EP0901354B1 (en) | 1996-05-17 | 2004-03-17 | Helmut Payer | An ocular implant |
FR2784575B1 (en) * | 1998-10-15 | 2000-12-22 | Megaoptic Gmbh | ACCOMMODATIVE INTRAOCULAR IMPLANT |
US6599317B1 (en) * | 1999-09-17 | 2003-07-29 | Advanced Medical Optics, Inc. | Intraocular lens with a translational zone |
FR2804860B1 (en) * | 2000-02-16 | 2002-04-12 | Humanoptics Ag | ACCOMODATIVE CRYSTALLINE IMPLANT |
US6884263B2 (en) * | 2001-07-17 | 2005-04-26 | Medennium, Inc. | Accommodative intraocular lens |
US7090888B2 (en) * | 2002-01-18 | 2006-08-15 | Snyder Michael E | Sustained release ophthalmological device and method of making and using the same |
US7261737B2 (en) * | 2002-12-12 | 2007-08-28 | Powervision, Inc. | Accommodating intraocular lens system and method |
US6695881B2 (en) * | 2002-04-29 | 2004-02-24 | Alcon, Inc. | Accommodative intraocular lens |
US20040082995A1 (en) * | 2002-10-25 | 2004-04-29 | Randall Woods | Telescopic intraocular lens implant for treating age-related macular degeneration |
US7125422B2 (en) | 2002-10-25 | 2006-10-24 | Quest Vision Technology, Inc. | Accommodating intraocular lens implant |
CA2507694C (en) * | 2002-12-12 | 2012-07-31 | Victor Esch | Accommodating intraocular lens system and method |
US7217288B2 (en) * | 2002-12-12 | 2007-05-15 | Powervision, Inc. | Accommodating intraocular lens having peripherally actuated deflectable surface and method |
US6972032B2 (en) * | 2003-01-14 | 2005-12-06 | Visioncare Ophthalmic Technologies Inc. | Intraocular lens implant |
US20060001186A1 (en) * | 2004-06-30 | 2006-01-05 | Richardson Gary A | IOL and method of manufacturing an IOL |
US20060155373A1 (en) * | 2005-01-13 | 2006-07-13 | Israel Henry M | Introacular lens assembly with distinguishing structure |
JP4564061B2 (en) * | 2005-04-05 | 2010-10-20 | アルコン,インコーポレイティド | Intraocular lens |
-
2007
- 2007-03-08 KR KR1020070022871A patent/KR100807940B1/en not_active IP Right Cessation
- 2007-09-21 MX MX2009009588A patent/MX2009009588A/en active IP Right Grant
- 2007-09-21 EP EP07808410.0A patent/EP2131786B1/en active Active
- 2007-09-21 CA CA2678777A patent/CA2678777C/en not_active Expired - Fee Related
- 2007-09-21 JP JP2009552574A patent/JP5266262B2/en not_active Expired - Fee Related
- 2007-09-21 WO PCT/KR2007/004632 patent/WO2008108524A1/en active Application Filing
- 2007-09-21 CN CN2007800519882A patent/CN101641060B/en not_active Expired - Fee Related
- 2007-09-21 US US12/530,242 patent/US8603165B2/en not_active Expired - Fee Related
- 2007-09-21 BR BRPI0721395-6A2A patent/BRPI0721395A2/en not_active IP Right Cessation
- 2007-09-21 EA EA200901214A patent/EA016269B1/en not_active IP Right Cessation
-
2009
- 2009-08-26 IL IL200590A patent/IL200590A/en not_active IP Right Cessation
Patent Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4451938A (en) * | 1982-09-24 | 1984-06-05 | Kelman Charles D | Intraocular lens and method of positioning the same in an eye |
US5152789A (en) * | 1991-05-14 | 1992-10-06 | Allergan, Inc. | Fixation member for an intraocular lens |
US7048760B2 (en) * | 1995-02-15 | 2006-05-23 | Medevec Licensing B.V. | Accommodating intraocular lens having T-shaped haptics |
US6051024A (en) * | 1995-10-06 | 2000-04-18 | Cumming; J. Stuart | Intraocular lenses with fixated haptics |
US7097660B2 (en) * | 2001-12-10 | 2006-08-29 | Valdemar Portney | Accommodating intraocular lens |
US20030135272A1 (en) * | 2002-01-14 | 2003-07-17 | Advanced Medical Optics, Inc. | Accommodating intraocular lens with integral capsular bag ring |
Non-Patent Citations (1)
Title |
---|
See also references of EP2131786A4 * |
Cited By (46)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9814570B2 (en) | 1999-04-30 | 2017-11-14 | Abbott Medical Optics Inc. | Ophthalmic lens combinations |
US10206773B2 (en) | 2002-12-05 | 2019-02-19 | Johnson & Johnson Surgical Vision, Inc. | Accommodating intraocular lens and method of manufacture thereof |
US9271830B2 (en) | 2002-12-05 | 2016-03-01 | Abbott Medical Optics Inc. | Accommodating intraocular lens and method of manufacture thereof |
US11751991B2 (en) | 2002-12-12 | 2023-09-12 | Alcon Inc. | Accommodating intraocular lenses and methods of use |
US10835373B2 (en) | 2002-12-12 | 2020-11-17 | Alcon Inc. | Accommodating intraocular lenses and methods of use |
US9039760B2 (en) | 2006-12-29 | 2015-05-26 | Abbott Medical Optics Inc. | Pre-stressed haptic for accommodating intraocular lens |
US9339373B2 (en) | 2007-09-28 | 2016-05-17 | Abbott Medical Optics Inc. | Polymer compositions suitable for intraocular lenses and related methods |
US8216310B2 (en) | 2007-09-28 | 2012-07-10 | Abbott Medical Optics Inc. | Polymer compositions suitable for intraocular lenses and related methods |
EP2200536B1 (en) * | 2007-09-28 | 2016-01-27 | Abbott Medical Optics Inc. | Polymer compositions suitable for intraocular lenses and related methods |
US8232363B2 (en) | 2007-12-21 | 2012-07-31 | Abbott Medical Optics Inc. | Silicone containing polymeric materials |
US8481667B2 (en) | 2007-12-21 | 2013-07-09 | Abbott Medical Optics Inc. | Silicone containing polymeric materials |
US9534088B2 (en) | 2007-12-21 | 2017-01-03 | Abbott Medical Optics Inc. | Silicone containing polymeric materials |
US9156949B2 (en) | 2007-12-21 | 2015-10-13 | Abbott Medical Optics Inc. | Silicone containing polymeric materials |
US9968441B2 (en) | 2008-03-28 | 2018-05-15 | Johnson & Johnson Surgical Vision, Inc. | Intraocular lens having a haptic that includes a cap |
JP2012509751A (en) * | 2008-11-26 | 2012-04-26 | アニユー・オプテイクス・インコーポレイテツド | Haptic device for intraocular lens |
US9439755B2 (en) | 2008-11-26 | 2016-09-13 | Anew Iol Technologies, Inc. | Haptic devices for intraocular lens |
US10010405B2 (en) | 2008-11-26 | 2018-07-03 | Anew Aol Technologies, Inc. | Haptic devices for intraocular lens |
CN104146797A (en) * | 2009-01-09 | 2014-11-19 | 力景公司 | Intraocular lenses and methods of accounting for capsule size variability and post-implant changes in the eye |
US20130131794A1 (en) * | 2009-01-09 | 2013-05-23 | Terah Whiting Smiley | Accommodating Intraocular Lenses and Methods of Use |
EP2384167A4 (en) * | 2009-01-09 | 2016-02-17 | Powervision Inc | Intraocular lenses and methods of accounting for capsule size variability and post-implant changes in the eye |
AU2020202819B2 (en) * | 2009-01-09 | 2022-03-10 | Alcon Inc. | Intraocular lenses and methods of accounting for capsule size variability and post-implant changes in the eye |
US11166808B2 (en) | 2009-01-09 | 2021-11-09 | Alcon Inc. | Accommodating intraocular lenses and methods of use |
US20100179653A1 (en) * | 2009-01-09 | 2010-07-15 | Claudio Argento | Intraocular Lenses and Methods of Accounting for Capsule Size Variability and Post-Implant Changes in the Eye |
US10299913B2 (en) * | 2009-01-09 | 2019-05-28 | Powervision, Inc. | Accommodating intraocular lenses and methods of use |
US9011532B2 (en) | 2009-06-26 | 2015-04-21 | Abbott Medical Optics Inc. | Accommodating intraocular lenses |
US20110054600A1 (en) * | 2009-06-26 | 2011-03-03 | Abbott Medical Optics Inc. | Accommodating intraocular lenses |
US10052194B2 (en) * | 2009-06-26 | 2018-08-21 | Johnson & Johnson Surgical Vision, Inc. | Accommodating intraocular lenses |
US20110029074A1 (en) * | 2009-08-03 | 2011-02-03 | Abbott Medical Optics Inc. | Fixation of ophthalmic implants |
US9603703B2 (en) | 2009-08-03 | 2017-03-28 | Abbott Medical Optics Inc. | Intraocular lens and methods for providing accommodative vision |
WO2011031557A1 (en) * | 2009-08-27 | 2011-03-17 | Abbott Medical Optics Inc. | Fixation of opthalmic implants |
AU2010292490B2 (en) * | 2009-08-27 | 2016-01-14 | Johnson & Johnson Surgical Vision, Inc. | Fixation of opthalmic implants |
US9072599B2 (en) | 2009-08-27 | 2015-07-07 | Abbott Medical Optics Inc. | Fixation of ophthalmic implants |
WO2011085349A3 (en) * | 2010-01-11 | 2012-09-13 | Abbott Medical Optics Inc. | Fixation of opthalmic implants |
US11484402B2 (en) | 2011-11-08 | 2022-11-01 | Alcon Inc. | Accommodating intraocular lenses |
US11406490B2 (en) | 2012-01-24 | 2022-08-09 | Alcon Inc. | Modular intraocular lens designs and methods |
WO2013170125A1 (en) * | 2012-05-10 | 2013-11-14 | Abbott Medical Optics Inc. | Accommodating intraocular lens with a compressible inner structure |
AU2013259357B2 (en) * | 2012-05-10 | 2017-06-08 | Johnson & Johnson Surgical Vision, Inc. | Accommodating intraocular lens with a compressible inner structure |
US8945215B2 (en) | 2012-05-10 | 2015-02-03 | Abbott Medical Optics Inc. | Accommodating intraocular lens with a compressible inner structure |
US10485657B2 (en) | 2012-06-04 | 2019-11-26 | Alcon Pharmaceuticals, Ltd. | Intraocular lens inserter |
GB2518378A (en) * | 2013-09-18 | 2015-03-25 | Timothy Paine | Intraocular Lenses |
US11446138B2 (en) | 2014-02-18 | 2022-09-20 | Alcon Inc. | Modular intraocular lens designs, tools and methods |
US11406491B2 (en) | 2015-01-30 | 2022-08-09 | Alcon Inc | Modular intraocular lens designs, tools and methods |
US10802297B2 (en) | 2015-10-08 | 2020-10-13 | Optotune Ag | Lens comprising an adjustable focus length |
WO2017060537A3 (en) * | 2015-10-08 | 2017-06-22 | Optotune Ag | Lens comprising an adjustable focus length |
US11382736B2 (en) | 2017-06-27 | 2022-07-12 | Alcon Inc. | Injector, intraocular lens system, and related methods |
US11707354B2 (en) | 2017-09-11 | 2023-07-25 | Amo Groningen B.V. | Methods and apparatuses to increase intraocular lenses positional stability |
Also Published As
Publication number | Publication date |
---|---|
US20100063588A1 (en) | 2010-03-11 |
CA2678777C (en) | 2012-08-14 |
JP2010520010A (en) | 2010-06-10 |
KR100807940B1 (en) | 2008-02-28 |
EP2131786B1 (en) | 2017-07-12 |
IL200590A (en) | 2014-07-31 |
JP5266262B2 (en) | 2013-08-21 |
US8603165B2 (en) | 2013-12-10 |
IL200590A0 (en) | 2010-05-17 |
EA016269B1 (en) | 2012-03-30 |
CN101641060B (en) | 2012-11-28 |
CN101641060A (en) | 2010-02-03 |
BRPI0721395A2 (en) | 2014-03-04 |
CA2678777A1 (en) | 2008-09-12 |
MX2009009588A (en) | 2009-11-26 |
EP2131786A1 (en) | 2009-12-16 |
EP2131786A4 (en) | 2011-10-26 |
EA200901214A1 (en) | 2010-04-30 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA2678777C (en) | Intraocular lens | |
US8603166B2 (en) | Intraocular lens assembly | |
CA2646831C (en) | Intraocular lens supporter | |
AU776819B2 (en) | Intraocular lenses | |
JP4982495B2 (en) | Deformable intraocular lens and lens system | |
US20070129798A1 (en) | Intraocular device | |
TW201632151A (en) | Dual optic, curvature changing accommodative IOL | |
US10758339B2 (en) | Intraocular lens assembly | |
RU2795243C1 (en) | Intraocular lens |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
WWE | Wipo information: entry into national phase |
Ref document number: 200780051988.2 Country of ref document: CN |
|
121 | Ep: the epo has been informed by wipo that ep was designated in this application |
Ref document number: 07808410 Country of ref document: EP Kind code of ref document: A1 |
|
WWE | Wipo information: entry into national phase |
Ref document number: 2678777 Country of ref document: CA |
|
WWE | Wipo information: entry into national phase |
Ref document number: 5437/DELNP/2009 Country of ref document: IN |
|
WWE | Wipo information: entry into national phase |
Ref document number: 200590 Country of ref document: IL |
|
WWE | Wipo information: entry into national phase |
Ref document number: MX/A/2009/009588 Country of ref document: MX |
|
WWE | Wipo information: entry into national phase |
Ref document number: 12530242 Country of ref document: US Ref document number: 2009552574 Country of ref document: JP |
|
NENP | Non-entry into the national phase |
Ref country code: DE |
|
REEP | Request for entry into the european phase |
Ref document number: 2007808410 Country of ref document: EP |
|
WWE | Wipo information: entry into national phase |
Ref document number: 2007808410 Country of ref document: EP |
|
WWE | Wipo information: entry into national phase |
Ref document number: 200901214 Country of ref document: EA |
|
ENP | Entry into the national phase |
Ref document number: PI0721395 Country of ref document: BR Kind code of ref document: A2 Effective date: 20090908 |