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WO1985000965A1 - Implants de lentilles intraoculaires - Google Patents

Implants de lentilles intraoculaires Download PDF

Info

Publication number
WO1985000965A1
WO1985000965A1 PCT/AU1984/000196 AU8400196W WO8500965A1 WO 1985000965 A1 WO1985000965 A1 WO 1985000965A1 AU 8400196 W AU8400196 W AU 8400196W WO 8500965 A1 WO8500965 A1 WO 8500965A1
Authority
WO
WIPO (PCT)
Prior art keywords
intraocular lens
lens implant
implant according
optical portion
lens
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/AU1984/000196
Other languages
English (en)
Inventor
Graham David Barrett
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Ezekiel Nominees Pty Ltd
Original Assignee
Ezekiel Nominees Pty Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Ezekiel Nominees Pty Ltd filed Critical Ezekiel Nominees Pty Ltd
Priority to KR1019850700024A priority Critical patent/KR890000205B1/ko
Priority to BR8407042A priority patent/BR8407042A/pt
Publication of WO1985000965A1 publication Critical patent/WO1985000965A1/fr
Priority to DK198501911A priority patent/DK172520B1/da
Priority to NO851735A priority patent/NO164879C/no
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

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 or corneal implants; Artificial eyes
    • A61F2/16—Intraocular 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 or corneal implants; 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
    • A61F2/1616—Pseudo-accommodative, e.g. multifocal or enabling monovision
    • 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 or corneal implants; Artificial eyes
    • A61F2/16—Intraocular lenses
    • A61F2/1691—Packages or dispensers for intraocular lenses
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
    • A61L24/04—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials
    • A61L24/043—Mixtures of macromolecular materials

Definitions

  • the present invention relates to intraocular lens.
  • PMMA polymethyl ethacrylate
  • an intraocular lens implant formed of a hydrogeL
  • a hydrogel is an organic polymeric or copolymeric material comprising hydrophilic monomers.
  • the hydrogel material swells upon being hydrated and becomes soft and flexible.
  • One particularly useful hydrogel is hydroxyethyl methacrylate (HEMA) and it has been found that this material causes little endothelial damage on contact. Also, since hydrogels are hydrophilic in nature endothelial damage is generally less than with PMMA.
  • hydrogel intraocular lens of the present invention could be useful in the anterior chamber of the eye or the posterior chamber, but. it is particularly envisaged for use in the posterior chamber. It has been found in particular that a HEMA hydrogel lens manufactured from HEMA having the capability of absorbing about 38% of its weight of water, makes a particularly useful posterior chamber intraocular lens.
  • the intraocular lens implant is of integral construction and comprises a relatively thick optical portion having relatively thin resilient flange means
  • flange means being arranged to retain the implant in place in the eye.
  • Figure 1 is a plan view of an intraocular lens implant in accordance with one embodiment of the present invention.
  • Figure 2 is a side elevation of the intraocular lens implant of Figure 1;
  • Figure 3 is a plan view of an intraocular lens implant in accordance with another embodiment of the present invention.
  • Figure 4a is a cross-sectional view of an eye with an implant according to Figures 1 and 2 in place with a ciliary sulcus placement
  • Figure 4b is a cross-sectional view of an eye with an implant according to Figures 1 and 2 in place with a capsule bag placement
  • Figures 5 to 8, 10 and 11 are views similar to that of Figure 4a showing alternative intraocular lens config ⁇ urations in accordance with the present invention
  • . - Figures 9 and 12 are plan views of the lens shown in Figures 8 and 11 respectively;
  • FIG 13 is a side elevation of a package containing an intraocular lens implant in accordance with the present invention.
  • an intraocular lens implant 10 comprising a central optical portion 12 which is in the form of a lens.
  • the central optical portion 12 is flanked by laterally extending flanges 14.
  • the implant has a posterior face 16 and an anterior face 18.
  • the lens implant of Figures 1 and 2 is arranged to be inserted in the posterior chamber of an eye.
  • the optical portion 12 is of asymmetrical biconvex construction which gives good optical resolution.
  • the posterior face 16 is at a standard curvature such as a curve having a radius of about 17mm.
  • the posterior face 16 is, in this case, a non-variable optical surface whilst the anterior face 18 is an optical surface of varying power.
  • the anterior face 18 may be a non- variable optical surface whilst the posterior face 16 may be an optical surface of varying power.
  • the optical properties of the optical portion 12 can be varied by varying the curvature of the anterior face of the optical portion 12.
  • the ratio of"curvature is preferably approximately 3:1 which computer analysis shows to provide optimum ocular resolution for an intraocular lens.
  • the power of each eye is different and therefore the thickness of the optical portion 12 and the curvature of the anterior face 18 thereof will vary from case to case.
  • the technique for forming the correct shape of the anterior face and thickness of the optical portion 12 are known.
  • the lens implant shown in Figure 3 is similar to that shown in Figures 1 and 2, except that the flanges 14 have been replaced by a single circular flange 15 which completely surrounds the optical portion 12.
  • the flanges 14 have been replaced by a single circular flange 15 which completely surrounds the optical portion 12.
  • the curvature of the posterior face 16 is preferably such that the resultant lens will be of asymmetrical biconvex construction with the posterior face having the larger curvature as shown in Figure 2.
  • optical portion 12 and flanges 14 are formed in an entegral unit, that is the entire implant 10 is formed in one piece.
  • the flanges 14 may be of a wide variety of thickness but are preferably between 0.02 and
  • the flanges 14 are between 0.10 and
  • the optical portion 12 is thicker than the flanges 14 but, as described above, its actual thickness will vary with optical requirements of the lens implant 10.
  • a typical thickness for the optical portion 12 is about 0.9mm.
  • the implant 10 is formed of a hydrogel material such as HEMA and the flanges 14 are therefore resilient.
  • the optical portion 12 is thick enough to be sufficiently rigid to provide stable optical correction.
  • the flanges 14 have a similar curvature to the posterior face 16.
  • the flanges 14 project forwardly and, as will be described, dispose the implant 10 away from the iris in use.
  • the flanges 14 may be transversely tapered as can be seen in Figure 1. This enables the flanges 14 to be inserted even into a small pupil.
  • the flanges 14 may, for example, taper from 6mm at the optical zone 12 to 2mm at their outer extremities. '
  • the lens implant 10 can be manufactured by any suitable technique such as by forming a blank on a lathe, polishing the lens implant, checking the thicknesses of the various parts of the lens implant, checking in the dry state for any flaws, cleaning to remove residual wax or polish and then bathing the implant in saline solution.
  • the hydrated implant can. then be washed in a Soxhlet system and again, examined for defects in the hydrated state.
  • Other suitable manufacturing techniques include moulding or pressing to form a lens implant in accordance with the present invention.
  • the power of the lens is measured in the hydrated state.
  • the lens dimensions are thus measured in the hydrated state.
  • the lens implant is placed in a sealed vial in a physiologically acceptable electrolyte solution and autoclaved to sterilise it.
  • the electrolyte solution must be a balanced or isotonic salt solution which will hydrate the lens implant 10 and be compatible with the human eye.
  • the vial is preferably a glass vial.
  • FIG 4a there is shown an eye comprising a cornea 22 which has an endothelium layer on its inner face. Behind the cornea there is an anterior chamber 24 which is filled with aqueous fluid. At the rear of the chamber 24 there is located the iris 26 which is in two parts separated by a gap which constitutes the pupil of the eye. At its outer edge the iris 26 is connected to ciliary sulcus 28. The region behind the iris 26 forms a posterior chamber 30 which also contains aqueous fluid. To the front of the ciliary sul ⁇ us 28 is the white 32 of the eye. To the rear of the posterior chamber is the posterior capsule 33 of the eye. As can be seen in Figure 4a the lens implant 10 of Figures 1 and 2 is mounted in the eye in the posterior chamber 30.
  • the lens implant 10 is retained in place by engagement of the flanges 14 in the ciliary sulcus 28.
  • fixation for a posterior chamber lens there are two preferred methods of fixation for a posterior chamber lens in accordance with the present invention.
  • the first method is illustrated in Figure 4a in which the lens is fixed in place by engagement with the ciliary sulcus 28 and in this case the lens width may be from about 12 to 14mm such as about 12.5mm.
  • the second method of fixation is illustrated in Figure 4b and is by means of the capsular bag of the eye. In this case the capsular bag, fixes the lens in place.
  • the lens intended for capsular bag placement would typically have a diameter in the range from about 10 to 12mm such as about 11mm.
  • the lens of Figure 4b is similar to that of Figure 4a.
  • the intraocular lens implant of the present invention can take many forms.
  • Figures 5 to 12 illustrate various modifications of the lens implant shown in Figure 4 and like reference numerals denote like parts.
  • the lens implants of Figures 5, 6, 7 and 11 are intended for posterior chamber placement by engagement with the ciliary sulcus but equivalent lens can be made which are intended for capsule bag placement as shown in Figure 4b.
  • An alternative form of intraocular lens implant 40 according to the present invention intended for implantation in the posterior chamber of the eye is shown in Figure 5.
  • the posterior face 16 is not of uniform curvature throughout but has increased curvature in the optical portion 12.
  • the lens 40 is still of asymmetrical biconvex construction.
  • intraocular lens implant 50 An alternative form of intraocular lens implant 50 according to the present invention intended for implantation in the posterior chamber of the eye is shown in Figure 6.
  • the posterior face 16 has reverse curvature in the optical portion 12 and the lens 50 is of convex-concave construction.
  • An alternative form of intraocular lens implant 60 according to the present invention intended for implant ⁇ ation in the posterior chamber of the eye is shown in Figure 7.
  • the optical portion of the posterior face 16 is located forwardly of the remainder of the posterior face 16 by means of a peripheral lip 62.
  • the lens 60 is of asymmetrical biconvex construction.
  • An alternative form of intraocular lens implant 70 according to the present invention intended for implantation in the anterior chamber of the eye is shown in Figures 8 and 9.
  • the flanges 14 are provided with outwardly projecting feet 72 arranged to engage with the scleral spur or angle of the eye.
  • the anterior face 18 of the implant 70 is of uniform convex curvature through the optical portion 12 and the flanges 14.
  • the posterior face 16 also has a convex curvature so that the lens 70 is of asymmetrical biconvex construction.
  • An alternative form of intraocular lens implant 80 according to the present invention intended for implant ⁇ ation in the anterior chamber of the eye is shown in Figure 10.
  • the lens of Figure 10 is similar to that shown in Figures 8 and 9 and it also comprises the outwardly projecting feet 72.
  • FIG. 11 An alternative form of intraocular lens implant 90 according to the present invention intended for implant ⁇ ation in the posterior chamber of the eye is shown in Figures 11 and 12.
  • the lens of Figures 11 and 12 comprise a pair of lugs 92 which extend upwardly and then outwardly from the anterior face 18.
  • the lugs 92 are each intended to engage with iris 26 of an eye.
  • the lugs 92 hold the lens implant 90 in place by engagement with the iris 26 but not necessarily by engagement with the ciliary sulcus 28.
  • the lens implant 90 is similar to the lens implant shown in Figure 4.
  • a manufactured lens is washed a number of times in double distilled water to remove impurities from it and then autoclaved as described above.
  • the autoelaving may be conducted for 15 to 30 minutes at a pressure in the range from about 120 to 130mm mercury in a sealed vial containing a physiologically acceptable electrolyte solution. Then the sterilised vial is placed inside an internally sterile overpouch which is sealed and the autoclaving process is then repeated to ensure complete sterility of the completed product.
  • OMPI A typical package comprising a sealed vial 100 containing a lens implant 102 and a quantity of physiologically acceptable saline solution 104 all contained within a flexible overpouch 106 is shown in Figure 13.
  • the diameter of the optical portion 12 of a lens implant in accordance with the present invention is preferably from 3 to 10mm, more preferably from 4 to 7mm.
  • the overall length of the lens implant may be from 8 to 15mm.
  • the non-variable optical surface of the optical portion 12 preferably ranges from piano to 10mm in radius of curvature, preferably from 15 to 30mm radius of curvature. As stated above the radius of curvature of the optical surface of varying power is varied to adjust the optical power of the lens implant.
  • the lens implant of the present invention is particularly envisaged for use where a cataract has been removed.
  • the lens implant of the present invention may be used to correct refractive errors an myopia without prior cataract extraction.
  • the lens implants of the present invention usually range from plano-convex to biconvex but as shown in Figure 6 , the posterior and anterior face of the optical portion 12 may have curves facing in the same direction which results in a concave-convex lens.
  • the lens implant of the present invention may include location members such as indentations, recesses or holes to assist in positioning the lens in the middle of the eye.
  • the lens implant can be inserted at the time of cataract extraction or as a secondary implant.
  • the lens can be inserted by the standard procedure.
  • the design of the lens also allows the flanges 14 to be inserted in a folded condition and then be allowed to open out through their own inherent resilience to engage with the ciliary sulcus 28.
  • the flanges 14 avoid the use of prolene hooks or the like which have been used in the past.
  • the lens implant Whilst it is preferred to insert the lens in hydrated condition from a vial as shown in Figure 13, the lens implant could be inserted into the eye dry and hydrated subsequently to hydrate and swell it.
  • the advantage of dry insertion is that it allows the lens implant to be inserted through a small wound in the eye.
  • the lens implant of the present invention may have a built in U.V. filter which is incorporated in the hydrogel.
  • the U.V. filter can be incorporated in the chemical mix as polymerisation takes place or a U.V. absorbing function can be built into the polymeric chain. It is also envisaged that in some cases anterior chamber lens would be incorporated into a posterior chamber of the eye by being reversed.

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  • Health & Medical Sciences (AREA)
  • Ophthalmology & Optometry (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • General Health & Medical Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Transplantation (AREA)
  • Vascular Medicine (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Biomedical Technology (AREA)
  • Engineering & Computer Science (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Cardiology (AREA)
  • Surgery (AREA)
  • Epidemiology (AREA)
  • Prostheses (AREA)

Abstract

Des implants de lentilles intraoculaires (10) entièrement à base d'un hydrogel hydrophile provoquent par contact peu de dégâts endothéliaux. On peut utiliser de l'hydroxyéthyle-méthacrylate (HEMA), des copolymères de pyrrolidone de vinyle avec de l'HEMA ou du méthacrylate de méthyle et des copolymères de méthacrylate de glycérole et de méthacrylate de méthyle et des copolymères de HEMA et de l'acrylamide diacétonique. La lentille (10) peut avoir une pluralité de formes et de dispositifs de fixation (14). Est décrit un procédé de stabilisation et d'emballage. On a découvert que les implants de lentilles intraoculaires à base de polyméthyle-méthacrylate hydrophobe (PMMA) causaient des dégâts à l'endothélium cornéen.
PCT/AU1984/000196 1983-08-30 1984-08-28 Implants de lentilles intraoculaires Ceased WO1985000965A1 (fr)

Priority Applications (4)

Application Number Priority Date Filing Date Title
KR1019850700024A KR890000205B1 (ko) 1983-08-30 1984-08-28 내안 렌즈 이식체
BR8407042A BR8407042A (pt) 1983-08-30 1984-08-28 Implantes de lentes intraoculares
DK198501911A DK172520B1 (da) 1983-08-30 1985-04-29 Selvbærende intraokulær implanterbar linse
NO851735A NO164879C (no) 1983-08-30 1985-04-30 Intraokulare linseimplantater.

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
AUPG1120 1983-08-30
AUPG112083 1983-08-30
AU31730/84A AU582123B2 (en) 1983-08-30 1984-08-08 Intraocular lens implants

Publications (1)

Publication Number Publication Date
WO1985000965A1 true WO1985000965A1 (fr) 1985-03-14

Family

ID=25621914

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/AU1984/000196 Ceased WO1985000965A1 (fr) 1983-08-30 1984-08-28 Implants de lentilles intraoculaires

Country Status (2)

Country Link
AU (1) AU582123B2 (fr)
WO (1) WO1985000965A1 (fr)

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2569557A1 (fr) * 1984-08-31 1986-03-07 Siepser Steven B Lentilles artificielles intra-oculaires ameliorees
GB2180160A (en) * 1985-08-28 1987-03-25 Steven B Siepser Self-centering artificial intraocular lens
US4725277A (en) * 1986-05-14 1988-02-16 Precision-Cosmet Co., Inc. Intraocular lens with tapered haptics
US4808182A (en) * 1986-11-26 1989-02-28 Nestle, S.A. Deswelled, hydrogel intraocular lenses
US4840627A (en) * 1986-04-08 1989-06-20 Michael Blumenthal Artificial eye lens and method of transplanting same
EP0286679A4 (fr) * 1986-10-29 1989-08-09 Mo Nii Microchirurg Cristallin artificiel pour chambre posterieure.
GB2238723A (en) * 1989-12-07 1991-06-12 Ceskoslovenska Akademie Ved Intraocular hydrogel lens with shape memory.
CN1061932C (zh) * 1998-09-14 2001-02-14 郑一仁 一种软性义眼
WO2000067678A3 (fr) * 1999-05-11 2001-03-08 Tassignon Marie Jose B Cristallin artificiel aux proprietes d'accomodation
KR20020036881A (ko) * 2000-11-11 2002-05-17 문경진 연성인공수정체 및 제조방법

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6461384B1 (en) 1999-06-17 2002-10-08 Bausch & Lomb Incorporated Intraocular lenses

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AU510468B2 (en) * 1976-03-24 1980-06-26 Coopervision Inc. Contact lens moulding
US4254509A (en) * 1979-04-09 1981-03-10 Tennant Jerald L Accommodating intraocular implant
AU530687B2 (en) * 1982-07-21 1983-07-28 Hoya Lens Corporation Soft contact lens
GB2114315A (en) * 1982-02-05 1983-08-17 Mazzocco Thomas R Deformable intraocular lens structures and methods and devices for implantation

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4242762A (en) * 1979-07-25 1981-01-06 Tennant Jerald L Posterior encapsuled implant lens

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AU510468B2 (en) * 1976-03-24 1980-06-26 Coopervision Inc. Contact lens moulding
US4254509A (en) * 1979-04-09 1981-03-10 Tennant Jerald L Accommodating intraocular implant
GB2114315A (en) * 1982-02-05 1983-08-17 Mazzocco Thomas R Deformable intraocular lens structures and methods and devices for implantation
AU530687B2 (en) * 1982-07-21 1983-07-28 Hoya Lens Corporation Soft contact lens

Cited By (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2569557A1 (fr) * 1984-08-31 1986-03-07 Siepser Steven B Lentilles artificielles intra-oculaires ameliorees
GB2180160A (en) * 1985-08-28 1987-03-25 Steven B Siepser Self-centering artificial intraocular lens
GB2180160B (en) * 1985-08-28 1989-08-09 Steven B Siepser Self-centering artificial intraocular lens
US4840627A (en) * 1986-04-08 1989-06-20 Michael Blumenthal Artificial eye lens and method of transplanting same
US4725277A (en) * 1986-05-14 1988-02-16 Precision-Cosmet Co., Inc. Intraocular lens with tapered haptics
EP0286679A4 (fr) * 1986-10-29 1989-08-09 Mo Nii Microchirurg Cristallin artificiel pour chambre posterieure.
US4808182A (en) * 1986-11-26 1989-02-28 Nestle, S.A. Deswelled, hydrogel intraocular lenses
WO1990009768A1 (fr) * 1986-11-26 1990-09-07 Alcon Laboratories, Inc. Lentilles intraoculaires d'hydrogel degonflees
GB2238723A (en) * 1989-12-07 1991-06-12 Ceskoslovenska Akademie Ved Intraocular hydrogel lens with shape memory.
GB2238723B (en) * 1989-12-07 1994-04-27 Ceskoslovenska Akademie Ved Intraocular hydrogel lens with shape memory
CN1061932C (zh) * 1998-09-14 2001-02-14 郑一仁 一种软性义眼
WO2000067678A3 (fr) * 1999-05-11 2001-03-08 Tassignon Marie Jose B Cristallin artificiel aux proprietes d'accomodation
KR20020036881A (ko) * 2000-11-11 2002-05-17 문경진 연성인공수정체 및 제조방법

Also Published As

Publication number Publication date
AU582123B2 (en) 1989-03-16
AU3173084A (en) 1985-03-07

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