EP1443875A1

EP1443875A1 - Intraocular lenses provided with angled edges to prevent posterior capsular opacification

Info

Publication number: EP1443875A1
Application number: EP02793203A
Authority: EP
Inventors: Joel Pynson
Original assignee: Bausch and Lomb Inc
Current assignee: Bausch and Lomb Inc
Priority date: 2001-10-31
Filing date: 2002-10-31
Publication date: 2004-08-11
Also published as: AU2002358867B2; KR20050042034A; HK1069758A1; CN1582137A; US20040042073A1; AR037173A1; JP2005507286A; FR2831423B1; CA2464705A1; FR2831423A1; CN100339058C; WO2003037225A1

Abstract

The invention concerns an intraocular refractive lens comprising an optic portion (34) with an outer peripheral edge (36) and one or more, preferably two, three or four equidistant haptic elements (38). Each haptic element (38) has the same shape, with a trapezoid or rhomboid cross-section. The edge of the outer rear surface of each haptic element (38) and the edge of the rear optic element are shaped like acute angles to prevent posterior capsular opacification.

Description

Intraocular lenses with angled edges to prevent posterior capsular clouding.

The present invention relates to intraocular lenses (IOLs) and a method of making and using them. More particularly, the present invention relates to IOLs with angled edges to prevent posterior capsular clouding in aphakic eyes from which the natural lens of the eye has been surgically removed.

Cataract extraction is one of the most commonly performed operations in the United States and around the world. The eye lens is located inside a so-called capsular bag or lens capsule located in the posterior chamber of the eye. To gain access to a lens affected by cataracts, an incision is made in the limbus of the eye in order to introduce a surgical instrument into the anterior chamber of the eye. In the case of extracapsular cataract extraction, a capsulo-hexis procedure is followed in which a portion of an anterior membrane of the lens capsule adjacent to the iris of the eye is extracted using a cutting surgical instrument to provide direct access to the lens with cataracts from the anterior chamber. The lens with cataracts is then extracted using various known methods, including phacoemulsification. Phacoemulsification is a procedure that involves applying ultrasonic energy to the lens with cataracts to break the lens into small pieces that can be aspirated from the lens capsule. With the exception of the portion of the anterior membrane of the lens capsule removed during the capsulo-hexis procedure, the lens capsule remains essentially intact for the duration of an extracapsular cataract extraction. Following the extraction of the lens affected by cataracts, an implant artificial intraocular lens (IOL), as discussed in more detail below, is typically implanted within the lens capsule to mimic the refractive function of the extracted natural lens. Implants of the IOL have been used for years in the aphakic eyes from which the natural lens of the eye has been extracted. Many different designs of the IOL have been developed in the past few years and have been used successfully in the eyes of the apostle. At present, successful IOL designs mainly include an optical portion with its supports, called haptics, connected to and surrounding at least part of the optical portion. The haptic portions of an IOL are designed to support the optical portion of the IOL in the lens capsule, the anterior chamber, or the posterior chamber of an eye. Commercially successful IOLs have been made from a variety of biocompatible materials, ranging from stiffer materials such as polymethylmethacrylate (PMMA) to more flexible materials capable of being folded or compressed such as silicones and certain acrylics. Haptic portions of the IOLs were formed separately from the optical portion and then subsequently connected to this portion by processes such as heat, physical stapling and / or chemical bonding. LIOs with haptics attached in this way are commonly called "multi-room" LIOs. IOLs are also commonly produced with haptics formed as an integral part of the optical portion in what is commonly called "monoblock" IOLs.

Softer, softer IOLs have grown in popularity in recent years due to their ability to compress, bend, roll or otherwise deform. These softer IOLs can be deformed before their insertion through an incision in the cornea of the eye. Following the insertion of the IOL in the eye, the IOL returns to its original form before deformation due to the memory characteristics of soft matter.

Softer, more flexible IOLs such as those just described can be implanted in one eye through an incision which is much smaller, i.e. 2.8 to 3.2 mm, than that necessary for more rigid IOLs, i.e. 4.8 to 6.0 mm. A larger incision is necessary for more rigid IOLs because the lens must be inserted through an incision in the cornea slightly larger than that of the diameter of the optical portion of the rigid IOL. As a result, stiffer IOLs have become less popular in the market as it has been found that larger incisions are associated with an increased incidence of post-operative complications such as induced astigmatism.

Although removal of the implanted cataract portion of the IOL offers considerable benefits to most cataract patients, this is not always the case. It is estimated that up to thirty percent (30%) of all patients who receive an IOL implant inside the lens capsule of the eye then develop posterior capsular clouding (OCP) or secondary cataracts in the five years after surgery. OCP is a clouding of IOL implants caused by the deposition of cells and fibers on the posterior surface of the IOL implant and on the posterior capsular membrane. These cell and fiber deposits obstruct the passage of light through the IOL implant and obscure the patient's vision. The main cause of OCP is the migration and proliferation of residual lens epithelial cells on the capsular membrane.

Due to the observed shortcomings of past and current IOL designs, there is a need for IOL implants designed to prevent OCP. Intraocular lenses (IOLs) made in accordance with the present invention have an optical portion having an outer peripheral edge and two or more, but preferably two, three or four equidistant haptic elements to support the optical portion in a patient's eye. Preferably, each of the haptic elements is of similar shape to obtain a "helix" effect to facilitate the implantation, rotation and centering of the IOL. The helix effect also improves accessibility inside the capsule for cleaning cortical remains. Each of the haptic elements has an internal portion and an external portion. The internal portion of each haptic element comprises an enlarged fixing portion permanently connected to the external peripheral edge of the optical portion. The outer portion of each haptic element includes a rounded free end. Each haptic element comprises an elongated central portion in the form of an arc which extends between the enlarged fixing portion and the rounded free end. From the enlarged fixing portion and all along the elongated central portion in the form of an arc, the dimensions of the haptic element may be stable or may vary. The particular angular shape of the haptic elements allows the rotation of the IOLs and prevents posterior capsular clouding.

Therefore, an object of the present invention is to provide intraocular lenses for use in aphakic eyes.

Another object of the present invention is to provide intraocular lenses for use in aphakic eyes capable of being implanted through a small incision.

Another object of the present invention is to provide intraocular lenses which prevent posterior capsular clouding.

Another object of the present invention is to provide intraocular lenses which allow greater ease of implantation, rotation and centering of said lenses. Another object of the present invention is to provide intraocular lenses which are biocompatible for use in aphakic eyes.

Yet another object of the present invention is to provide intraocular lenses which are resistant to decentering inside the eyes.

These objects and other objectives and advantages according to the present invention, some of which are described in a specific manner and others not, will be demonstrated in the detailed description, in the drawings and the claims below, in which the same characteristics are designated by the same numbers.

Figure 1 is a schematic representation of the interior of a human eye comprising a natural lens and a refractive IOL implanted in the lens capsule of the eye; Figure 2 is a plan view of an IOL with two haptics made in accordance with the present invention;

Figure 3 is a side view of the IOL of Figure 2;

Figure 4 is a cross-sectional view of an optical portion of the IOL of Figure 2 taken along line 4-4; Figure 5 is a cross-sectional view of a haptic element of the IOL of Figure 2 taken along line 5-5;

Figure 6 is a cross-sectional view of a haptic element of the IOL of Figure 2 taken along line 6-6;

Figure 7 is a cross-sectional view of a haptic element of the IOL of Figure 2 taken along line 7-7;

Figure 8 is a plan view of another embodiment of an IOL with two haptics made in accordance with the present invention;

Figure 9 is a side view of the IOL of Figure 8;

Figure 10 is a cross-sectional view of an otic part of the IOL of Figure 8 taken along line 10-10; Figure 11 is a cross-sectional view of a haptic element of the IOL of Figure 8 taken along line 11-11;

Figure 12 is a cross-sectional view of a haptic element of the IOL of Figure 8 taken along the line 12-12; Figure 13 is a cross-sectional view of a haptic element of the IOL of Figure 8 taken along line 13-13;

Figure 14 is a plan view of another embodiment of an IOL with three haptics made in accordance with the present invention;

Figure 15 is a side view of the IOL of Figure 14; Figure 16 is a cross-sectional view of an otic part of the IOL of Figure 14 taken along line 16-16;

Figure 17 is a cross-sectional view of a haptic element of the IOL of Figure 14 taken along line 17-17;

Figure 18 is a cross-sectional view of a haptic element of the IOL of Figure 14 taken along line 18-18; and

Figure 19 is a cross-sectional view of a haptic element of the IOL of Figure 14 taken along line 19-19.

Figure 1 is a schematic view of an eye 10 showing the structures which are related to implantation of intraocular lenses (IOL) 12 according to the present invention. The eye 10 comprises an optically clear cornea 14 and an iris 16. A lens capsule 18 and a retina 20 are placed behind the iris 16 of the eye 10. The eye 10 also comprises an anterior chamber 22 situated in front of the iris 16 and a posterior chamber 24 located between the iris 16 and the lens capsule 18. The IOL 12 is preferably implanted in the lens capsule 18 of the aphakic eye. When used in aphakic eyes, IOLs 12 are used to replace diseased natural lenses that have been surgically removed, for example after cataract surgery. The eye 10 also includes an optical axis OA-OA which is an imaginary line passing through the center optic 28 of the anterior surface 30 and the posterior surface 32 of the lens capsule 18. The optical axis OA-OA in the human eye 10 is generally perpendicular to a portion of the cornea 14, to the lens capsule 18 and to the retina 20. The IOLs according to the present invention, represented in FIGS. 2, 8 and 14, generally designated by the reference numeral 12, are designed to be implanted preferably in the lens capsule 18 of an aphakic eye. . The IOL 12 has an optical portion 34 with an outer peripheral edge 36. Two or more, but preferably two, three or four equidistant haptic elements 38 are preferably formed integrally on the peripheral edge 36 of the optical portion 34. Each haptic element 38 has a similar shape to obtain a "helix" appearance to facilitate rotation and centering of IOL 12 during implantation inside the eye 10 and to obtain rotation of IOL 12 as described more in detail below.

Each haptic element 38 is manufactured so as to have an internal portion 40 and an external portion 42. The internal portion 40 of each haptic element 38 comprises an enlarged fixing portion 44 preferably formed integrally and permanently connected with the external peripheral edge 36 of the optical portion 34. As a variant, however, the enlarged fixing portion 44 of each haptic element 38 can be permanently fixed to the optical portion 34 by stapling, chemical polymerization or by other methods known to those skilled in the art. . Each haptic element 38 also comprises on the external portion 42 a rounded free end 46 designed to avoid contact with the internal surfaces 48 of the lens capsule 18 of the aphakic eye 10.

The haptic elements 38 are formed with elongated, arcuate central portions 50 which extend between the enlarged attachment portions 44 and the free ends 46. As best illustrated in Figures 5-7, 11-13 and 17-19, from the enlarged fixing portion 44 and all along the elongated central portion in in the form of an arc 50, the cross section of the haptic element 38 has a trapezoidal or, alternatively, rhomboid shape in order to obtain the desired characteristics for preventing OCP.

As seen in Figures 5 to 7, the section of the haptic element 38 along lines 5/5, 6/6 and 7/7 are trapezoidal, the outer side 60 of the trapezoid having at its lower part an acute angle 52 and at its upper part an obtuse angle 71.

The particular shape of the haptic elements 38 produces two effects: on the one hand thanks to the acute haptic edge 52, the migration of the capsular cells along the posterior surface 32 is blocked and on the other hand thanks to the obtuse external anterior haptic edge 71, rapid shuttering between the anterior surface 30 and the posterior surface 32 is possible. This closure comes from the phenomenon known as symphysis according to which, when the capsular bag has been emptied, the two walls 30 and 32 of said bag stick against one another. When they are so stick, there is no more migration of the capsular cells.

Preferably the acute angle 52 is between 10 and 45 °.

The haptic element 38 can be stable or its dimensions can vary from the enlarged fixing portion 44 and all along the central portion 50 on the plane 68-68 substantially perpendicular to the optical axis OA-OA. The haptic elements 38 with regular dimensions from the enlarged fixing portion 44 and all along the central portion 50 can be illustrated in the best way by FIGS. 6, 12 and 18 and by the dimensions which are proposed there. However, due to the increasing complexity of the embodiments having varying dimensions, they are discussed in more detail below.

In the embodiments with haptic elements whose dimensions vary, from the enlarged fixing portion 44 to the rounded free end 46, the width of the haptic element 38 gradually narrows on the plane 68-68 . Approximately toward the enlarged attachment portion 44, the anterior surface 62 has a width of about 1.2 1.4 mm. The front surface 62 is preferably narrower by about 30 percent than the rear surface 64 which is preferably about 1.6 to 1.9 mm wide, as illustrated by the embodiments of the Figures 5, 11 and 17. As illustrated by the embodiments of Figures 6, 12 and 18, approximately at mid-section 56, the anterior surface 62 has a width of about 1.0 to 1.2 mm . The anterior surface 62 is preferably about 15 percent narrower than the posterior surface 64 which is preferably about 1.2 to 1.5 mm wide. As illustrated by the embodiments of FIGS. 7, 13 and 19, roughly towards the rounded free end 46, the anterior surface 62 and the posterior surface 64 have approximately the same width of approximately 0.5 to 1 , 0 mm.

Going from the enlarged fixing portion 44 towards the rounded free end 46, the haptic element 38 has a uniform thickness all along the plane 66-66 parallel to the optical axis OA-OA. As illustrated by the embodiments of Figures 5-7 and 17-19, the surface of the haptic internal edge 58 has a thickness of about 0.20 to 0.80 mm but, most preferably, about 0 , 34 to 0.48 mm. As illustrated by the embodiments of Figures 11-13, the surface of the internal haptic edge 58 may alternatively be angular rather than perpendicular to the anterior surface of the IOL 62 and to the posterior surface of the IOL 64 for forming an acute internal anterior haptic edge 79 along the anterior surface of the IOL 62. The surface of the external haptic edge 60, as illustrated by the embodiments of Figures 5-7, 11-13 and le- 19, is angular rather than perpendicular to the anterior surface of IOL 62 and the posterior surface of IOL 64 to form an acute external posterior haptic edge 52 along the posterior surface of IOL 64. Generally, when goes from the enlarged fixing portion 44 towards the external portions 42, the width of the haptic elements 38 can decrease on plane 68-68 while the thickness on plane 66-66 remains homogeneous.

LA LIO 12 is preferably produced with an optical portion 34 having a diameter of approximately 4.5 to 9.0 mm, but preferably approximately 5.0 to 6.0 mm and more precisely 6.0 mm and a thickness of about 0.2 mm to 1.0 mm, but preferably about 0.2 to 0.8 mm and more precisely 0.3 to 0.5 mm on the peripheral edge 36, as illustrated by the embodiment of FIG. 2. As a variant, as illustrated by the embodiments of FIGS. 8 and 14, the peripheral edge 36 of the optical portion 34 is angled rather than perpendicular with respect to the anterior surface of the IOL 62 and to the posterior surface of the IOL 64. By thus angulating the peripheral edge 36, an acute posterior optical edge 54 is formed along the posterior surface of the IOL, as best illustrated in FIGS. 10 and 16.

As can be seen in FIG. 10, the peripheral edge 36 is arranged in the extension of the surface of the optical part 34.

The haptic elements 38 extend from the optical portion 34 in the form of an arc in general and their overall length increases or decreases as a function of the diameter of the otic portion 34. When the diameter of the optical portion 34 increases, the overall length of the haptic elements 38 decreases. Likewise, when the diameter of the optical portion 34 decreases, the overall length of the haptic elements 38 increases. Generally, the haptic elements are formed to have a length of about 2.6 to 6.0 mm, but preferably about 3.4 to 5.5 mm and, more specifically, about 4.8 mm, measured between the center of the enlarged fixing portion 44 and the center of the rounded free end 46. The IOL preferably measures between 1 1 and 13 mm in total, between the contact area 72 and the opposite contact area 72.

During implantation, the IOL 12 is preferably positioned with the contact zones 72 of the external posterior haptic edges 52 in contact with the internal surfaces 48 of the lens capsule 18. The haptic elements 38 of the IOL 12 are inclined outward to maintain constant contact between the contact zones 72 and the internal surfaces 48. By thus positioning the IOL 12 inside the lens capsule 18, the central portions 50 of the haptic elements 38 are slightly bent inwards on the plane 68-68. The central portions 50 therefore flex under the compressive forces because they have a reduced width compared to that of the enlarged fixing portions 44. When the haptic elements 38 bend at the central portions 50, the surfaces of the internal haptic edge 58 approach the external peripheral edge 36. During implantation, the external posterior haptic edges 52, preferably with the posterior optical edge 54 of the IOL 12 come into contact with the internal surfaces 48 of the lens capsule 18 to prevent OCP. The outer posterior haptic edges 52 and the posterior optical edge 54 prevent OCP by serving as a barrier to cell migration and proliferation inside the lens 18. Therefore, when the IOL 12 is used as a refractive lens, obtains a stable and reliable refractive correction. Materials suitable for the production of IOLs 12 include, but are not limited to, pliable or compressible materials such as silicone polymers, hydrocarbon and fluorinated hydrocarbon polymers, soft acrylic polymers without water content, with a low water content and with a high water content, polyesters, polyamides, polyurethane, silicone polymers with hydrophilic monomer units, polysiloxane elastomers containing fluorine and combinations thereof. The preferred material for the production of LIO 12 according to the present invention is a hydrophilic or hydrophobic acrylic material such as those known to those skilled in the art. Poly (hydroxyethyl methacrylate-co-hydroxyhexyl methacrylate) (poly (HEMA-co-HOHEXMA) and methyl methaciylate-hydroxyethyl methacrylate (MMA-HEMA) are the preferred hydrophilic acrylic materials useful for the manufacture of LIO 12 because of the contents of equilibrium water of between about 17 and about 27 percent by weight and the high refractive index of about 1.46 or more, which is higher than that of the aqueous humor of the eye, it i.e. 1.33. A high refractive index is a desirable characteristic for the production of IOLs to impart high optical power with minimal optical thickness. By using a material with a high refractive index, visual acuity defects can be corrected using a thinner IOL. Poly (HEMA-co-HOHEXMA) and MMA-HEMA are also desirable materials for the production of LIO 12 because of their mechanical strength which is suitable for withstanding considerable physical manipulation. Poly (HEMA-co-HOHEXMA) and MMA-HEMA also have desirable memory properties suitable for the use of IOLs. IOLs made from a material with good memory properties such as poly (HEMA-co-HOHEXMA) and MMA-HEMA unfold in an eye in a controlled rather than explosive way to take their predetermined shape. Explosive unfolding of IOLs is undesirable due to the potential damage to delicate tissue inside the eye. Poly (HEMA-co-HOHEXMA) and MMA-HEMA also have non-deformability in the eye.

LIO 12 can similarly be made from a variety of materials with varying physical characteristics. For example, the IOLs 12 can be manufactured to have an optical portion 34 made of a hydrophilic acrylic material with a high refractive index, haptic elements 38 made of a more rigid material than that of the optical portion 34 and contact zones 72 made of the same material as that of the optical portion 34 or of another material having a lower refractive index and a higher glass transition temperature. Although the teachings of the present invention are preferably applied to soft or pliable IOLs made of a pliable or compressible material, it is also the same for lenses harder, less flexible made in a relatively rigid material such as polymethyl methyl acrylate (PMMA) having flexible haptics made either in the same material or in a different material. The optical portion 34 of the IOL 12 can be a lens with positive power between 0 and approximately +40 diopters or a lens with negative power between 0 and approximately -30 diopters. The optical portion 34 can be biconvex, piano-convex, piano-concave, biconcave or concave-convex (meniscus) depending on the power necessary to obtain the central and peripheral thickness for efficient handling.

Optionally, the optical portion 34 of the IOL 12 can be formed with a brightness reduction zone 74 having a width of about 0.25 to 0.75 mm but preferably about 0.3 to 0.6 mm and most preferably 0.5 mm adjacent to the outer peripheral edge 36 for reduced brightness when the outer peripheral edge 36 of the IOL 12 is struck by the light which enters the eye 10 in high light or at other times when pupil 76 is dilated. The brightness reduction zone 74 is typically made of the same material as that of the optical portion 34, but it can be opaque, colored or conventionally designed to block or scatter light in the plane having the optical axis OA-OA.

LIO 12 is preferably manufactured by first producing discs of one or more materials from one or more selected materials as described in US Pat. Nos. 5,217,491 and 5,326,506. The IOL 12 can then be machined from the material discs in a conventional manner. Once machined, the IOL 12 can be polished, cleaned, sterilized and packaged using a conventional process known to those skilled in the art.

The IOL 12 is used in the eye 10 by making an incision in the cornea 14 and by inserting the IOL 12 in the posterior chamber 24 and by closing the incision according to the methods known to those skilled in the art.

However, IOL 12 can preferably be used in the eye 10 by making an incision in the cornea 14 and the lens capsule 18, extracting the natural lens, inserting the IOL 12 into the lens capsule 18 and closing the incision according to methods known to those skilled in the art. The IOL 12 according to the present invention provides a refractive lens suitable for use in the lens capsule 18 or in the posterior chamber 24, but preferably in the lens capsule 18 because of its OCP preventive characteristics. . The IOL 12 has haptic elements 38 of similar shape to minimize or eliminate the decentering of the LIO 12 and the distortion of vision. The similar shape of the haptic elements 38 similarly allows the rotation of the IOL 12 for better positioning and better adjustment inside the lens capsule 18. This better fitting inside the lens capsule 18 has an advantage because one or a few lens sizes suitably fit most eye dimensions 10. By providing a "universal" lens such as that according to the present invention, clinical risks for patients are minimized by poorly dimensioned lenses. Likewise, the need for manufacturers to produce many sizes of IOLs to adjust them to the many dimensions of eyes is eliminated, thereby reducing the costs of production of storage which result therefrom. also benefit from IOL 12 in that they save time by eliminating the need to determine the size of each patient's eye and the costs associated with maintaining large stocks of lenses of various sizes.

Another characteristic of the IOL 12 illustrated by the embodiment of FIG. 14 is one or more, but preferably between one and three surface edge grooves 78. The surface edge grooves 78 allow more complete surgical irrigation, and thus better cleaning of the viscoelastic residues and residues of crystalline cortex inside the lens capsule 18. During surgical irrigation, a fluid is circulated inside the lens capsule 18 to remove viscoelastic and various other residues. The edge surface grooves 78 improve the circulation of the fluid by providing a clear path for the passage of the fluid. We therefore proceed to a more complete cleaning inside the lens capsule 18 using this reinforced fluid circulation.

Although some specific embodiments of the present invention are shown and described herein, it is obvious to those skilled in the art that various modifications can be made without departing from the spirit and scope of the concept of the invention underlying and that the above is not limited to the particular forms shown and described here.

Claims

1. An intraocular lens to be implanted inside an eye generally perpendicular to the optical axis of the eye comprising: an anterior surface (34); a posterior surface (64); an outer peripheral edge 36 between said anterior surface and said posterior surface defining an optical portion 34 with at least a portion of said outer peripheral edge 36 and said anterior surface forming an obtuse angle and at least a portion of said outer peripheral edge 36 and said posterior surface forming an acute angle; two or more haptic elements 38 of the same trapezoidal or rhomboidal cross section permanently connected to said external peripheral edge 36; and acute external posterior haptic edges 52 on said haptic elements 38.

2. An intraocular lens to be implanted in a lens capsule generally perpendicular to the optical axis of the eye to prevent posterior capsular opacification comprising: an anterior surface (34); a posterior surface (64); an outer peripheral edge 36 between said anterior surface (34) and said posterior surface (64) defining an optical portion 34 with at least a portion of said outer peripheral edge 36 and said posterior surface forming an acute angle; two or more haptic elements 38 of the same trapezoidal or rhomboidal cross section permanently connected to said external peripheral edge 36; and acute posterior external haptic edges 52 on said haptic elements 38.

3. Intraocular lens according to claim 1 or 2, wherein the haptic elements 38 and the optical portion 34 are both formed of a foldable or compressible material.

4. Intraocular lens according to claim 1 or 2, wherein said lens is formed from a material selected from the group comprising silicone polymers, hydrocarbon and fluorinated hydrocarbon polymers, hydrogels, soft acrylic polymers, polyesters, polyamides, polyurethane, silicone polymers with hydrophilic monomer units, fluorine-containing polysiloxane elastomers and combinations thereof.

5. Intraocular lens according to claim 1 or 2, wherein said lens is formed from a hydrophilic acrylic material.

6. An intraocular lens according to claim 1 or 2, wherein said lens is formed from a hydrophilic acrylic material which contains between 17 and 27 percent by weight of water.

7. Intraocular lens according to claim 1 or 2, wherein said lens is formed of poly (HEMA-co-HOHEXMA).

8. Intraocular lens according to claim 1 or 2, wherein said lens is formed from a material or more materials with at least one material having a refractive index greater than 1.33.

9. An intraocular lens according to claim 1 or 2, wherein said lens is formed from a material or more materials with at least one material which is an acrylic material.

10. Intraocular lens according to claim 1 or 2, wherein said lens is formed from a material or more materials with at least one material which is a silicone material.

11. Intraocular lens according to claim 1 or 2, wherein said haptic elements 38 have a homogeneous thickness.

12. Intraocular lens according to claim 1 or 2, in which a brightness reduction zone 74 is formed adjacent to the external peripheral edges 36 of the optical portion 34.

13. A method of manufacturing intraocular lenses according to claim 1 or 2, comprising: forming a disc of one or more suitable materials, and machining said lenses from said disc.

14 ° Intraocular lens to be implanted inside an eye, in the posterior chamber of said eye, perpendicular to the optical axis of said eye comprising: an anterior surface; a posterior surface; an outer peripheral edge 36 between said anterior surface and said posterior surface defining an optical portion 34 with at least a portion of said outer peripheral edge 36 and said posterior surface forming an acute angle; two or more haptic elements 38 of the same trapezoidal or rhomboidal cross section permanently connected to said external peripheral edge 36; and acute external posterior haptic edges 52 on said haptic elements 38.

15. Intraocular lens according to claim 1 or 2, in which said external peripheral edge 36 and said posterior surface intersect at an acute angle between said haptic elements 38.

16. Intraocular lens according to claim 1 or 2, in which said external peripheral edge 36 and said anterior surface intersect at an obtuse angle between said haptic elements 38.

17. Intraocular lens according to any one of the preceding claims, in which the haptic elements (38) have a trapezoidal section so as to have an acute angle (52) which blocks migration. capsular cells along the posterior surface (64) of the optical portion (34).

18. Intraocular lens according to any one of the preceding claims, in which the haptic elements (38) have a rhomboidal section so as to have an acute angle (52) which blocks the migration of the capsular cells along the posterior surface (64). of the optical part (34).

19. Intraocular lens according to either of claims 17 and 18 in which the trapezoidal or rhomboidal shape of the haptic elements (38) promotes the phenomenon of symphysis, that is to say the adhesion one against the other of the walls (30) and (32) of the capsular bag which completely stops the migration of the capsular cells.