JPS6131149A - Intraocular lens, its production and method and apparatus for embedding said lens in human eye - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

[Detailed description of the invention]

BACKGROUND OF THE INVENTION Field of the Invention This invention relates to intraocular lenses of hydrogel material adapted for implantation within the human eye. Description of conventional methods The concept of using intraocular lenses to correct aphakia has a long history. Much of the pioneering work was done by Rold Ridley in London and Pinkhorst in the Netherlands. A detailed history of the development and results of intraocular implantable lenses is presented in Marcel Eugen Nordrone's paper, Docu-menta Opthaln.
logica Vol, 38. December 1974 1
Published on the 6th, it has been reissued on. A summary of the history of various types of artificial lens implants. Annals of 0ptha by P. Choice
lII]ology. Also found in an article published October 1973, pages 1113-1120. In most cases, lenses were made from organic polymers, such as poly(methyl methacrylate), +61Jmer. It has also been proposed to use lenses made of pure silicate glass with embedded glass lenses. Certain glass compositions have been proposed, for example, in the disclosure of US Pat. No. 3,996,627. Although glass has certain advantages as an intraocular implant, it often results in a relatively high weight of the finished lens and has a density that is not optimal for an implant in this regard. An early report by Schifferli in 1975 described an attempt by Cassamata to introduce intraocular lenses after cataract surgery. This lens immediately slipped down toward the fundus. Many patents are directed to the problem of placing intraocular lenses into the eye to allow the eye to perform its intended function with minimal trauma to the eye. For example, U.S. Patent 2,834
,023; 3,711,870; 3,673,
616; 3.866.249; 3,906.511
and 3,913.148; Intra-camera, made of poly(methyl methacrylate) or many other glass-like materials.
ral) lens, i.e., the prosthesis of the excised macroscopic lens has a refractive index of 1.396 of the macroscopic crystalline lens of the human eye.
characterized by substantially larger refractive index values. For example, a poly(methyl methacrylate) type intraocular lens has a 1.5
It has a refractive index around 3. In this way, poly(
The geometry and shape of the implantable lens (methyl methacrylate) differs from that of the naked eye, allowing the artificial lens immersed in a refractive medium (aqueous and vitreous body fluids) to substantially replicate the refractive index properties of the naked eye lens. It can be done. For example, an artificial lens may be shaped with two optical surfaces of substantially smaller curvature than that of a macroscopic lens. However, such changes in the shape of an artificial lens may affect the precision of the space occupied by the macroscopic lens. In addition, a discrepancy is observed in the specific gravity of conventional materials used in intraocular lens fabrication, e.g., approximately 1.25, compared to the specific gravity of artificial lenses (approximately 1.1). As such, IOL implantation of conventional materials immersed in the eye's refractive medium is several times more visible than the macroscopic lens. Although this drawback has been diminished by recent advances in thinner intracameral lens designs, This, however, further increases the shape differences between the artificial lens and the macroscopic lens. Maintaining a compact but relatively heavy intraocular lens system (body and attachment or fixation means) within the desired optical band A number of adaptation methods have been proposed, some of which have been used in practice. U.S. Pat. The patentees disclose that the lens is made of acrylic hybirogel or other biologically acceptable lens material and that the lens is laterally A woven or knitted fibrous material, such as Dacron, is attached to the outer periphery of the antennal-shaped portion, allowing the iris tissue to grow and form a lens. Provides a site capable of forming a permanent anchor. See U.S. Pat. (Lens body, integral antenna type part,
A loop □oop) is inserted into the position previously occupied by the crystalline lens by widening the pupil dilation of the iris to admit this system. U.S. Patent 4,073,
015, column 3, lines 56-66. It is clear from the specification and drawings that the lens body of the patient's intraocular lens system is significantly smaller than the macroscopic lens of the patient's eye. SUMMARY OF THE INVENTION The present invention obviates and/or substantially eliminates many of the problems associated with implanting intraocular lenses (IOLs) into the typical location previously occupied by macroscopic crystalline lenses. The IOL can be inserted by relatively simple means into the empty space after surgical removal of a clouded or opacified macroscopic lens. The IOL hydrogel material substantially fills or occupies the chamber of the eye, thereby often substantially reducing, or in some cases even eliminating the need for lens fixation and positioning means. IOLs have or approximate many of the properties of sterile lenses, including refractive index values close to 1.4, among other notable properties. The process involved is smooth and economically attractive. Technically speaking, IOLs can be fabricated using water-swellable, water-insoluble, highly hydrophilic materials (which are known in the art to be hydrated into hydrogels). The generally anhydrous form of xerogels (known as xerogels) can be formed by mechanical cutting, e.g. It is another object of the present invention to provide an improved intraocular lens of a hydrogel material that is biologically inert, biologically compatible with living tissue, and has a suitable refractive index. It is an object of the present invention to provide an improved method and apparatus for fabricating intraocular lenses by a simple and inexpensive mold casting technique. Another object of the present invention is to provide an improved method and apparatus for fabricating intraocular lenses by a simple and inexpensive mold casting technique. It is a further object of the present invention to provide a unique means for inserting an intralens.It is a further object of the present invention to provide a unique means for inserting an intralens into a surface of the IOL body itself that helps anchor or secure the IOL body in a fixed location within the human eye. It is an object of the present invention to provide an improved intraocular lens body optionally having unique peripheral thread-like means within and in its vicinity. Yet another object of the present invention is to and to provide the human eye with a hydrogel intraocular lens made of a hydrogel material that is typically placed in a space within the human eye. These and other objects will be readily apparent upon consideration of the present disclosure. Will.

[Brief explanation of drawings]

FIG. 1 is a cross-sectional side view of a concave mold 10, in which curves 11, 12, 13, and 14 represent the convex meniscus surface formed by overfilling the mold cavity 4 with a liquid consisting of a polymerizable reactant. Represents a penetrating side part. FIG. 2 is a cross-sectional side view of the intraocular hydrogel lens separated from mold 10. FIG. Curves 1 and 2 in this view of the IOL correspond to the curves defined by the mold cavity side 7 and the convex meniscus side 11 (FIG. 1). DESCRIPTION OF THE INVENTION The present invention is directed to a novel stable intraocular lens body of hydrogel material useful for implantation in place of a macroscopic crystalline lens in a human eye that has been removed by surgical means or otherwise. This inner Hibirogel lens body has a shape substantially defined by two rotationally symmetrical and coaxial optically finished surfaces, at least one of which is convex as long as the focal length of Shinzuke is obtained. For example, double-sided convexity (preferred), plane-convexity, and micro-concave-convexity. In a preferred form, both surfaces of the lens body, e.g. biconvex, have continuous transitions, ie, no sharp edges or boundaries. The intraocular lens consists essentially of a stable, water-swellable, water-insoluble hypergel containing at least about 65-70%, preferably at least about 65-70% by weight, based on the total hydrogel weight. Contains water or saline (approximately 0.9 weight percent saline). The osmotic pressure equilibrium with saline in this hydrogel is about 1.4, preferably about 1.
37 to about 1.45, preferably about 138 to about 142
, and more preferably a refractive index of about 1.39 to about 1.41. The upper limit of water content in the hydrogel is controlled by its ability to be generally shape-retentive with sufficient mechanical strength to function as an artificial lens body replacement for opacified macroscopic lenses. Generally, a water content upper limit of 90% by weight is suitable, with 85-90% by weight being desirable in various embodiments. Hydrogels made via a polymerization process are preferred, in which the concentration and selected starting material(s), such as hexamer(s), are obtained. f It significantly affects the water swelling properties of IJ moms). In the form of an intraocular implant, the hydrogel material is
The following properties: transparency, good optical properties (giving it the ability to function as an IOL), biological inertness, biological compatibility with living tissues, stability in common physiological media. It is further characterized by good mechanical properties such as hardness, softness, elasticity and modulus. Hydrogel materials can be synthetic or natural stable materials or modified products of both types, such as various types of modified collagen and other natural products, polymerization products from ethylenically unsaturated polymerizable monomers, polyisocyanates and polyols (natural and synthetic). ), etc. In a preferred form, the hydrogel is a synthetic derivative. The general shape of the novel intracameral hydrogel lens is similar to the general shape of the macroscopic crystalline lens in the lens. Referring to Figure 2,
Artificial lenses (preferred) have a membrane shape of about 7.5 to about 1
Front surface 1 resembling a flat ellipsoid with a median radius of curvature in the range of about 5 doves; Posterior surface 2 being a spherical or quadratic rotationally symmetric surface with a median radius of curvature ranging from about 5 to 8 doves; Front surface 1 and a central lens thickness (between anterior surface 1 and posterior surface 2) of about 2°5 to about 5°; There is. In one aspect of the invention, suitable intraocular lenses can be made from starting materials used in the manufacture of so-called soft hydrophilic high water content contact lenses and similar hydrogel materials. Desirably, the hydrogel is characterized by a relatively slightly to moderately crosslinked polymer network, and such products are well described in the literature. The operating conditions necessary to carry out suitable reactions, especially polymerization reactions, are of course well known in the art and are described, for illustration, in U.S. Pat.
,036,814;4.095,877;4,2
75.183; 4,361,689; 4.388
,436; and 4,408,023%s seen
To the extent appropriate, these patents are incorporated by reference into this disclosure as if indicated in their entirety. One skilled in the art can select the selected monomer or monomers, including appropriate crosslinking means, catalyst(s), solvents, and the like. Illustrative reactants include hydrophilic monomers such as 2-hydroxyethyl methacrylate, glycidyl methacrylate, N-vinylpyrrolidone, methacrylamide monomethacrylate, alkali metal salts such as itaconic acid, methacrylic acid, and the like. The hydrophilicity of the polymer product can often be increased, for example, by using methacrylic acid as one of the monomers. Crosslinking means include, for example, divinylbenzene, ethylene glycol diacrylate or dimethacrylate, propylene glycol diacrylate or dimethacrylate, and polyacrylate esters such as H+)ol: triethanolamine, glycerin, ]-rimethylolpropane. or polymethacrylate esters. Examples of other crosslinking monomers include N,N-methylene-bis-acrylamide 8 or methacrylamide and sulfonated divinylbenzene. Polymerization can also be carried out in the presence of well-known initiator(s) and/or catalyst(s) such as, for example, organic peroxides, alkyl percarbonates, hydrogen peroxide, and ammonium, sodium, or potassium persulfates. Alternatively, it can be carried out in the absence of radiation (ultraviolet, X-ray, microwave, or other known forms of radiation). Polymerization temperatures can vary from 20°C and below to 100°C and above. The polymerization of the ethylenically unsaturated phase compound is preferably carried out in the presence of a liquid medium and/or a plasticizer and/or a solvent, such as water, glycerin, miscible organic liquid/aqueous medium, and the like. Mixtures of reactants are generally preferred because they allow hydrogels with "% injection" properties to be produced.Mixtures of hydrophilic and hydrophobic reactants at appropriate concentrations are preferred because the resulting polymer product is Exemplary hydrophobic monomers include lower alkyl methacrylates, such as methyl methacrylate. Well described in the patent literature. In one aspect, the present invention provides lens-forming reactant(s) and other ingredients such as water (preferred) and/or miscible organic liquids/water (preferred) or glycerin. The present invention is directed to a new method of making novel intraocular lenses by casting a liquid mixture comprising an organic medium into a preferably open concave mold, the mold forming a wetting angle greater than zero with said mixture. Made from any suitable material. The concave mold cavity has the shape of a spherical or quadratic rotationally symmetric surface, terminating in a horizontal circular sharp green. The liquid mixture of monomer(s) is molded in predetermined amounts. into the cavity, but this amount generally exceeds the volume of the cavity defined by the circular sharp edge.The liquid mixture does not overflow the circular edge. Above this circular edge a convex surface of the type of flat spheroid is formed.In this way, the desired surface of the intraocular lens is formed in situ.In this process,
The wetting angle is greater than zero, as described above. In other words, if the surface is not wettable (e.g. Teflon ■) or is not completely wetted, the liquid mixture that exceeds the volume of the mold cavity will not spill out, but rather will be and a convex meniscus side surface shown as 14 is formed. The larger the wetting angle is, the larger the permissible excess amount is. Of course, surface tension,
There is a point at which adhesive forces and other forces and attractions cannot hold the volume of the liquid mixture inside the convex, convex surface above the circular mold edge. A suitable shape is achieved when the injection volume (of liquid) is about 10 to about 80 volumes less than the volume of the mold cavity itself (below the chain horizontal edge 5). This can be achieved by adjusting the amount of fluid overinjected above the cavity volume. One embodiment of the invention includes an IOL with a planar and even slightly concave anterior surface, as described above. In such cases, the injection volume of the mold cavity 4 with the liquid mixture may slightly exceed the sharp circular mold edge 5 or be horizontal with the mold edge 5, depending on the optical properties of the IC) required by the patient. or even slightly below the mold edge 5. After injection, the liquid mixture of monomer(s) is exposed to polymerization conditions, such as polymerization temperature, in an inert atmosphere or, if a photoinitiator is used, to photochemically effective radiation. Once the polymerization reaction is complete, the molded product may be removed from the mold or the mold and product may be immersed in water where it (the IOL product) can be easily released from the mold after swelling. This product requires no further mechanical treatment since its surface is optically precise and completely smooth.
~do not have. All that is required is the removal of extractable low molecular weight impurities by the necessary water or aqueous alcohol washes and final equilibration with saline. It is then disinfected and stored until used for its intended purpose. The intraocular lens of the present invention can also be produced by mechanical processing (
This anhydrous IOL can then be manufactured to the desired shape but on reduced scale by turning, grinding and polishing);
Swell the replica to the required size in an aqueous medium. This method is somewhat costly (labor intensive) and is not as desirable as the previously described casting technique. Given the soft, elastic, shape-retentive nature of the new intraocular lens, the lens can preferably be conveniently sterilized and stored in a tube-like container, and thus can be used during primary (preferred) or secondary implantation procedures. , ready for use. In one form, the tubular container (e.g., made of a flexible plastic such as polyethylene) has a diameter at one end that is less than the diameter (thickness) of the intraocular lens, and the IOL is a flexible, thin-walled container. By applying pressure to the container toward the narrow end of the container, the IOL can be pushed and deformed into a sufficiently oblique shape to allow exit through the narrow opening of the container. The pressure applied to the container can be conveniently rubbed by applying manual pressure to the extent necessary to cause deformation but not to destroy or damage the integrity of the intraocular lens. In an amiebar fashion, the IOL is then squeezed from its container and then easily assumes its original size and shape. If the inner wall of the container, which is conveniently a flexible container such as plastic, e.g. polyethylene or polypropylene, is made hydrophilic as per techniques known in the art, movement of the IOL therein and It can make it quite easy to get out of the room. The intraocular lens may be secured within the container in such a way that its anterior and posterior surfaces are represented by the container wall. Another aspect of the present invention provides a novel method of inserting this new 10L body into an empty space created, for example, by surgical removal of a clouded lens. If the posterior lens color is not removed, it is generally clear and can act as a natural membrane or foil that precisely delimits the space for an artificial lens of the same size and shape. The most closely fitted intraocular lens can generally be determined according to the shape and volume or weight of the removed macroscopic lens. In this regard, the ophthalmologist can select from a large stock of new intracameral lenses and insert the appropriate lens into the space occupied by the enucleated lens. If the lens color remains intact after extraction of the cloudy lens, and if the adjacent ciliary muscles have not degenerated, this new IOL is sufficiently soft and elastic to be visible to the naked eye. Because it occupies the space occupied by the lens,
It can be at least partially deformed by the muscles (similar to the function of a normal macroscopic lens), thereby imparting at least a partial accommodative effect on the patient's eye. The aqueous phase IOL enters the back chamber of the eye through a pupillary aperture smaller than the normal relaxed diameter of the IOL or through a small acceptable surgical opening into the posterior chamber (using a tubular container of the principles previously described). ) can be introduced. Given the ability of the intraocular lens to temporarily transform into an amiba-like shape, the surgical opening for introducing the new IOL into the cavity by the novel technique described above is 1111I to 2m+ (and the necessary If so, it can be of the order of magnitude (greater than that). In principle, the IOL can be inserted through the pupillary aperture in a partially or essentially dry state (as the lens dimensions are measurably smaller in this state). Such lenses assume their final dimensions after several hours in the eye by swelling to equilibrium in the surrounding vitreum. If the IOL does not maintain its correct position in the human eye, thread-like attachment means such as textile fibers such as Dacron/or absorbable surgical material are advantageously attached to the IOL.
It can be arranged in a ring around the periphery and applied to 10L. Such measures should be minimally disturbing to the optical bandwidth of the intraocular lens. A novel cast polymerization technique can be used, for example, to create a pre-shaped reinforcing structure (e.g. thread-like or filament-shaped), which can be crimped if necessary.
K may be included near the sharp edges around the mold (inside the concave mold) to impart tensile and elongation properties. In its preferred form, the resulting IOL lens product is thus embedded. possesses an essentially undisturbed optical zone from the implanted attachment means. Such attachment means may be anchored within the eye, such as the iris, by known surgical methods. In one embodiment, the attachment means It may consist of a thread-like or knitted material extending outward from the lens body (preferably near the toroid surface 3). Such material, a fabric and/or an absorbable suture, is in contact with the ocular tissue in its vicinity. interlocking,
Tissue growth and mixing with the above substances occur over time. Non-absorbable threads are permanently interlocked with tissue growth, and absorbable threads are predictably absorbed into the tissue. The intraocular lens fixation technique in the manner described above is effective and permanent without traumatic symptoms to the eye. However, as previously discussed, it is not necessary to secure IOL implantation by surgical means. ■If the shape and dimensions of the OL are chosen appropriately and the OL is properly inserted into the posterior chamber, the aftermath of permanent IOL implantation is uneventful, especially if the posterior surface of the lens is intact. Example 1-4 10-2-hydroxyethyl methacrylate, 0.
03-ethylene glycol-luminium> methacrylate, 0.
A solution is prepared using 169 sodium methacrylate and 10-glycerin. 0.01 to this solution
5F ammonium perokene disulfate is added as a polymerization catalyst in the form of a 25% aqueous solution. The resulting transparent liquid was loaded into the concave cavities of four separate propylene molds as shown in Figure 1, and the cavities had a central spherical shape with a radius of 6 and a width of 9 fins, which were continuously connected to the surface of the annular facepiece. It is formed from a cap. The toroidal surface is formed by a rotation in a meridian of diameter 1, and its center is 3.71 degrees away from the axis. The annular face piece surface has a diameter of 9.
4+, terminates in a sharp circular edge of m, which edge is 2
．． The depth of the mold 8 in the direction of the arrow is determined to be 9 moi. The cavity volume of this mold is 134 microliters. The volumes of clear polymerizable liquid injected into each of the four molds were 18], 214.247. and 27
It was 8 microliters. The resulting convex meniscus surface of the injection mold 1'' is conveniently shown in 11.12. in FIG.
13 and 14. The mall was kept in a horizontal position throughout and carefully inserted into a tunnel heated to 75°C with an inert atmosphere maintained by a gentle flow of nitrogen. Practically complete conversion is achieved after 30 minutes of polymerization. The mold containing the gelled molded product is soaked in distilled water at room temperature for 24 hours. The lens is then demolded from the mold. To achieve complete cleaning, the molded lenses are
Heat to 80° C. in 0% aqueous isopropyl alcohol for several days (use fresh aqueous isopropyl alcohol daily). Perform a similar wash with distilled water for several days,
The cleaning lens is made of 0.6% NaCt and 0.43% NaH.
Finally, it is stored in a form ready for surgical applications in an aqueous solution containing CO3. Based on the injection amount of the four liquid mixtures mentioned above, the intraocular lens has the characteristics shown in Table 1 below.Table 1 1 4.1 15 13
1.41 9,72 4.9 1
0 15 1.41 9.
73 5.6 8 16.5 1,41
9,74 6.3 7 18 1.
41 9.7fa) Median curvature of the anterior surface (b) Refraction during saline immersion Figure 1 shows that the anterior surface of the four intraocular lenses is 11.12°13,
and 14, which correspond to the curve defined by . If the polymerizable liquid combination is prepared by diluting the stated amount of monomer with an amount of glycerin that is not 10-, intraocular lenses with the same shape but different dimensions are obtained. Its dimensions differ from the original IOL dimensions by a factor f: f== (0,4+0.04V)-3≦, where ■ is the amount of added glycerin indicated by -. Therefore, by diluting the monomer mixture with only 7-glycerin, the dimensions, ie, diameter, thickness, and radius of curvature, are increased by a factor of 1.14. On the other hand, dilution with 20-glycerin causes the IOL lens to shrink by a factor of 0.94. Since the dilution of the 7-mer mixture does not substantially affect the resulting refractive index of the gel, the refraction changes accordingly and the above value should be divided by the appropriate factor f. The slightly cross-linked hydrophilic polymers, preferably having a refractive index between about 1.38 and 1.44 at equilibrium with saline, can be used as well as gels of the type described above.

[Brief explanation of drawings]

FIG. 1 is a cross-sectional side view of the concave mold 10, and the curve 1
Reference numerals 1, 12, 13 and 14 represent side cross sections passing through the surface of a convex meniscus formed by over-injecting a liquid comprising a polymerizable reactant into the cavity 4 of the mold 5. Is the second figure a mold? 10 is a cross-sectional side view of an intraocular hydrogel lens that has been released from mold 10. FIG. Curves 1 and 2 in this figure correspond to the curves defined by the mold cavity side section 7 and the convex meniscus side section 11 (FIG. 1). Figure 1

Claims (1)

[Scope of Claims] 1. Consisting essentially of an intraocular lens body having a shape substantially defined by two rotationally symmetric and coaxial optically finished surfaces, at least one surface of which is convex. human eye, wherein the lens body consists essentially of a water-swellable, water-insoluble, stable hydrogel material containing at least about 60% water by weight, and wherein the hydrogel material has a refractive index of about 1.4. An artificial intraocular lens adapted to be implanted in the posterior chamber of the eye. 2. Intraocular lens according to claim 1, wherein said two optically finished surfaces are convex and characterized by a continuous transition. 3. An intraocular lens according to claim 1, wherein there is an implantable attachment means near the toroidal face surface of the lens for fixing the lens in a fixed position within the human eye. 4. There is an implanted filamentous attachment means for anchoring said lens in a fixed position in the human eye, and the optical band of said lens is essentially undisturbed by said implanted attachment means. The intraocular lens according to item 3. 5. The hydrogel material is a polymer of 2-hydroxyethyl methacrylate, in which case the hydrogel material contains 60-90% water by weight and about 1.38 to about 1
．． 4. Intraocular lens according to claim 3, having a refractive index in the range of .42. 6. A method for producing an intraocular lens with predetermined dimensions; a. A liquid mixture comprising a reactant capable of forming an intraocular lens;
introducing said liquid mixture into said mold cavity having a concave surface corresponding to the convex shape of one surface of the predetermined intraocular lens product and defined by a sharp edge around the cavity; b. introducing in an amount at least sufficient to approximately reach the level of said sharp edge periphery of the mold; c. allowing the lens-forming reactant to react for a sufficient period of time to form an eye having at least one convex surface; forming an intraocular lens product; d. equilibrating the intraocular lens by repeated washing in an aqueous medium; and e. then forming an intraocular lens product characterized by at least one optically finished convex surface. storing and maintaining a predetermined intraocular lens hydrogel in osmotic equilibrium with a physiological solution. 7. said liquid mixture comprising a polymerizable ethylenically unsaturated compound, said liquid mixture exceeding the volume of said mold cavity and thereby being bound above the sharp edge periphery of the mold by said edge periphery; introduced into the mold cavity in a predetermined amount to form a convex body; and the resulting intraocular lens hydrogel is characterized by two optically finished convex surfaces; Method. 8. The liquid mixture comprises 2-hydroxyethyl methacrylate, a preformed reinforcing structure is included in the mold cavity near the sharp edge of the mold, and the resulting intraocular lens hydrogel optically 8. A method as claimed in claim 7, including close to the surface and essentially undisturbed the optical zone of the lens. 9. An artificial intraocular lens body adapted to be implanted in the posterior chamber of a human eye; an intraocular lens body having a shape defined by the above, at least one surface of which is convex, the lens body being comprised of a water-swellable, water-insoluble stable hydrogel material; b. is contained in an aqueous medium and in osmotic equilibrium, thereby obtaining its final dimensions; and c. after obtaining its final dimensions, said intraocular lens has a diameter of at least about 60 mm.
wt% aqueous medium, refractive index of about 1.4, good optical properties,
A lens characterized by biological inertness, biological compatibility with living tissues, stability in normal physiological media, and good mechanical properties, including softness and elasticity; . 10. Intraocular lens according to claim 9, wherein said two optical finishing surfaces are convex and characterized by continuous transitions. 11. The intraocular lens of claim 10, wherein there are implanted anchoring means near the toroidal surface of the lens to anchor the lens in a fixed position within the human eye. 12. An implanted filamentous anchoring means is present to anchor the lens in a fixed location within the human eye, and the optical zone of the lens is essentially free from interference with the implanted anchoring means;
An intraocular lens according to claim 10. 13. The hydrogel material is a polymer of 2-hydroxyethyl methacrylate, and the intraocular lens is immersed in a physiological solution and in osmotic equilibrium and placed in a sterile sealed container. Intraocular lenses as described in section. 14. A container according to claim 13, which is substantially tubular in shape, one closed end of which is defined by a narrow diameter smaller than the thickness of the intraocular lens. 15. The wall of the tube-shaped container is flexible, and when the lens is removed from the container, the lens is deformed by manual pressure, but deformed to an extent that does not cause destruction of the lens. 15. A container according to claim 14 for obtaining a container. 16. The container according to claim 15, wherein the inner wall of the tubular container is made hydrophilic. 17. A container according to claim 15, wherein the walls of the container are made of plastic material.