CA1237851A

CA1237851A - Intraocular lens implants

Info

Publication number: CA1237851A
Application number: CA000461155A
Authority: CA
Inventors: Graham D. Barrett
Original assignee: Ezekiel Nominees Pty Ltd
Current assignee: Iolco Pty Ltd
Priority date: 1983-08-30
Filing date: 1984-08-16
Publication date: 1988-06-14
Also published as: DK191185D0; US4936850A; JPS6364981B2; DK191185A; DE3483738D1; BR8407042A; EP0136807A2; JPS6077765A; DK172520B1; KR850700007A; IE842153L; IE56822B1; US4664666A; DE3486263D1; NZ209291A; EP0136807A3; PT79154A; ZA846570B; PT79154B; IL72779A0

Abstract

ABSTRACT OF THE DISCLOSURE

The present invention relates to an intraocular lens implant formed entirely of a hydrogel.

Description

3~

The present invention relates to intraocular lens. It is known to replace the natural crystalline lens following cataract extraction. Many people on whom cataract operations are performed receive an intraocular lens implant. However, there is a need for a safer and more effective intraocular lens than those which have been available hitherto. The most commonly used material for intraocular lens has been polymethylmethacrylate (PMMA). PMMA has a number of characteristics making it suitable for use as an intraocular lens implant. However, it has been shown to be particularly injurious to the corneal endothelium. The corneal endothelium is a thin layer at the back of the cornea. The maintenance of corneal clarity is dependent on the endothelium which is essentially non-regenerative. There appears to be a bio-physical interaction between the hydrophobic PMMA and the endothelium such that even momentary touch on insertion will cause significant endothelial cell disruption by adherence of the cells to the lens surface.
Loss of endothelial cells at the time of surgery can lead to loss of corneal transparency several years later. There are other problems attendant with the use of PMMA as an implant material.
In accordance with one aspect of the present invention there is provided a self-supporting intraocular lens suitable for implantation in the human eye to replace the natural crystalline lens, characterized by a relatively thick, centrally located, optical portion having an anterior face and a posterior face, said -P ~, ~ l~ `;s~2 ~;~3~

optical portion being sufficielltly thick and rigid to provide stable optical correction; flange means extending la-terally from said optical portion and projecting away from the vertical plane of the optical portion; said flange means functioning to support and retain the lens in place in the eye following implantation without fixation to the iris of the eye; said flange means being sufficiently resilient to function to dispose the lens away from the iris when implanted in the eye; and wherein said lens is formed entirely of a hydrogel.

-2a-~3~

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 methacr~,ilate (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.
Other types of hydrogel which may be used in the present invention are copolymers of vinyl pyrrolidone with HEMA or methyl methacrylate, copolymers of glyceryl methacrylate and methyl methacrylate and copolymersof HEMA and diacetone acrylamide.
The 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 ~hat 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.
Preferably, the intraocular lens implant is of integral construction and comprises a relatively thick optical portion having relatively thin resilient flange means extending away from it, said flange means being arranged to retain the ~3~

implant in place in the eye.
The present invention will now he descri~ed, by way of example, with reference to the accompanying drawings, in which:-Figure 1 is a plan view of an intraocular lens implant inaccordance 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 viewssimilar to that of Figure 4a showing alternative intraocular lens configurations in accordance with the present invention;
Figures 9 and 12 are plan views of the lens shown in Figures 8 and 11 respectively; and Figure 13 is a side elevation of a package containing an intraocular lens implant in accordance with the present invention.
In Figures 1 and 2, the~e is shown 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.
S As can be seen in Figure 2, 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. In other lens constructions, the anterior face 18 may be a non-variable optical surface whilst the posterior face 16 may be an optical surface of varying power. Thus, in the embodiment illustrated in Figure 2, the ~3~

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 ls 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 flange 15 is of similar cross-sectional shape and thickness to the flanges 14.
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.
Further, the optical portion 12 and flanges 14 are formed in an integral 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 0.2mm thick.
More preferably, the flanges 14 are between 0.10 and 0.18mm thick such as about 0.14mm thick. The optical portion 12 ~:378~i~

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.~mm.
The implant 10 i5 formed o~ a hydrogel material such as HEM~
and the flanges 14 are therefore resilient. However, the optical portion 12 is thick enough to be sufficiently rigid to provide stable optical correction.
As can be seen in Figure 2, the flanges 14 have a similar curvature to the posterior face 16. Thus the flanges 14 project forwardly and, as will be described, dispose the implant 10 away from the iris in use.
Further, 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 ~Z3~

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.
Finally, 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.
In Figure 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 2~. The region behind the iris 26 forms a posterior chamber 30 which also contains aqueous fluid. To the front of the ciliary sulcus 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 mount~din the eye in the posterior chamber 30.
The lens implant 10 is retained in place hy engagement of the flanges 14 in the ciliary sulcus 28. There are two preferred methods of fixation for a posterior chamber lens in ~23'7~

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 llmm. In other respects the lens of Figure 4b is sLmilar 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 numexals 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 _ g _ ~3~

in Figure 5. In this case, 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.
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.
In this case~ 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 implantation in the posterior chamber of the eye is shown in Figure 7. In this case, the optical portion o~ 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 constructio.n, An alternative form of intraocular lens implant 70 according ~3~35~

to the present invention intended for implantation in the anterior chamber of the eye is shown in Figures 8 and 9.
In this case, the flanges 14 are provided with outwardly projecting feet 72 arranged to engage with the scleralspur 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 implantation 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 copmrises the outwardly projecting feet 72.
However, the anterior face 18 of the lens is of increased curvature in the optical portion 12 compared to the remainder of the anterior face 18.
An alternativeform of intraocular lens implant 90 according to the present invention intended for implantation 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. As shown in Figure ll, the lugs 92 are each intended to engage with iris 26 of an eye. Thus the lugs 92 hold the lens implant 90 in place by engagement with 3L~37~

the iris 26 but not necessarily by engagement with the cilia~y sulcus 28. In other respects the lens implant 90 is similar to the lens implant shown in Figure 4.
Preferably, 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 autoclaving 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. A typical package comprising a sealed vial 100 containing a lens implant 102 and a quantity of physiological~
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 lOmm, more preferably from 4 to 7mm. The overall length of the lens implant may be from 8 to 15mm.
me non-variable optical surface of the optical portion 12 preferably ranges from plano to lOmm 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.

~237~

The lens implant of the present invention is particularly envisaged ~or use where a cataract has been removed.
However, the lens implant of the present invention may be used to correct refractive errors and myopia without prior 5 cataract extraction.
Thus, the lens implants of the present invention usually range from plano-convex to biconvex but as shown in Figure 6, the posterior and anterior ~ace of tne 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 o~ the lens also allows the flanges 14 to be inserted in a foldéd 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.
Whilst it i5 preferred to in8ert 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. ~he advantage of dry insertion is 78~

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 chenical 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.
Modifications and vari~tions such as would be apparent to a skilled addressee are deemed within the scope of the present invention.

Claims

THE EMBODIMENTS OF THE INVENTION IN WHICH AN
EXCLUSIVE PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED
AS FOLLOWS:

1. A self-supporting, soft intraocular lens suitable for implantation in the human eye to replace the natural crystalline lens, comprising:
an optical portion having an anterior surface and a posterior surface, said optical portion being sufficiently thick and rigid to provide stable optical correction;
flange means having an anterior surface and a posterior surface, said flange means projecting anteriorly in the posterior chamber of the eye, and projecting posteriorly in the anterior chamber of the eye; said flange means function-ing to support and retain the lens in place in the eye fol-lowing implantation without fixation to the iris of the eye and being sufficiently resilient to function to dispose the lens away from the iris when implanted in the eye; said flange means having sufficient strength and flexibility so that the implanted lens can move slightly along the visual axis of the eye when forces are applied to said flange means so as to prevent said lens from being displaced from alignment with the visual axis; and wherein said lens is formed of a hydrogel.

2. An intraocular lens according to claim 1 wherein the posterior surface of the optical portion is convex, and the posterior surface of the flange means and the posterior surface of the optical portion define a single, continuous arc.

3. An intraocular lens according to claim 1 intended for insertion in the posterior chamber of an eye, the optical portion of said lens being of asymmetrical biconvex con-struction with the posterior surface having the larger cur-vature; the lens being retained in position by engagement of the flange means in the ciliary sulcus or capsular bag of the eye.

4. An intraocular lens according to claim 1 charac-terized in that the hydrogel is hydroxyethyl methacrylate.

5. An intraocular lens according to claim 1 charac-terized in that the lens is of integral construction.

6. An intraocular lens according to claim 1, intended for insertion in the posterior chamber of an eye, charac-terized in that the flange means project forwardly and have a curvature in the range of from plano to 10mm radius.

7. An intraocular lens according to claim 5, charac-terized in that the optical portion of the lens is of asymmetrical bi-convex construction.

8. An intraocular lens according to claim 1, charac-terized in that the optical portion has a diameter of from 3 to 10mm.

9. An intraocular lens according to claim 8, charac-terized in that the lens has a length of from 8 to 15mm in a horizontal direction across the lens.

10. An intraocular lens according to claim 1 charac-terized in that the optical portion has a non-variable optical surface having a curvature from plano to 10mm radius.

11. An intraocular lens according to claim 10, charac-terized in that the optical portion has a non-variable optical surface having a curvature from 15 to 30mm radius.

12. An intraocular lens according to claim 1, charac-terized in that the lens is in hydrated form.

13. An intraocular lens according to claim 12, characterized in that said hydrated lens is contained in a sealed vial containing a quantity of physiologically ac-ceptable electrolyte solution.

14. An intraocular lens according to claim 13, charac-terized in that the sealed vial is contained in a sealed overpouch.

15. An intraocular lens according to claim 1, charac-terized in that the ratio of curvature between the curvature of the posterior surface and the curvature of the anterior surface of the optical portion is on the order of 3:1.