HK1069758B - Intraocular lenses provided with angular edges to prevent posterior capsular opacification - Google Patents

Description

Intraocular lens with angled edges to prevent posterior capsular opacification

Technical Field

The present invention relates to intraocular lenses (IOLs) and methods of producing and using such lenses. In particular, the present invention relates to IOLs having angled edges to prevent opacification of the posterior capsule of the aphakic eye following surgical removal of the eye's natural lens.

Background

Cataract extraction surgery forms part of the most common surgery in the united states and throughout the world. The lens is located in the so-called capsular bag (capsular sac) or lens capsule of the posterior chamber of the eye. Access to the lens of a cataractous eye is typically achieved by making an incision in the edge of the eye to allow surgical instruments to enter the anterior chamber of the eye. In the case of extracapsular cataract extraction, a capsulorhexis follows. Wherein the portion of the inner membrane of the lens capsule adjacent the iris of the eye is removed using surgical instruments to create a direct access from the anterior chamber into the lens affected by the cataract. The lens affected by the cataract is removed using various known methods, including phacoemulsification. Phacoemulsification is a procedure that involves applying ultrasonic energy to a cataractous lens to fragment the lens into small pieces that can be sucked out of the lens capsule. The lens capsule remains substantially intact throughout the extracapsular cataract extraction process except for the anterior membrane portion of the lens capsule. Removal of a lens containing a cataract, as will be described below, implantation of an artificial intraocular lens (IOL) is implanted in the lens capsule in the usual manner to stimulate the refractive function of the removed natural lens.

Implants have been used in aphakic eyes for many years where the natural lens has been removed, and over the past many years, a variety of different IOL designs have been used and have also been successful in aphakic eyes. Successful IOL designs now primarily include an optic portion having supports, referred to as haptics, attached to and at least partially surrounding the optic portion. The haptics of the IOL are configured to support the IOL optic within the lens capsule, either in the anterior chamber or the posterior chamber of the eye.

Commercially successful IOLs have been manufactured from a variety of biocompatible materials, ranging from relatively rigid materials, such as Polymethylmethacrylate (PMMA), to relatively flexible materials capable of being flexed or compressed, such as silicones and certain acrylic materials. The haptics of the IOL are manufactured separately from the optic and then the optic is attached thereto by methods such as heat, physical fixation and/or chemical bonding. IOLs having haptics attached in this manner are commonly referred to as "multi-piece" IOLs. IOLs are also commonly manufactured to have haptics integrally formed with the optic portion and are commonly referred to as "one-piece" IOLs.

The softest and most flexible IOLs have been expected to increase in recent years due to their reliability in compressing, bending, rolling or undergoing other deformation. These softer IOLs may be deformed prior to implantation through an incision in the cornea of an eye. After the IOL is implanted in the eye, it returns to its original pre-deformed shape due to the memory characteristics of the soft material.

Softer, more flexible IOLs such as those already described may be implanted through a relatively small incision, say 2.8 to 3.2mm, in comparison to the incision required for stiffer IOLs, say 4.8 to 6.0 mm. A larger incision is required for more rigid IOLs because the lens must be implanted through an incision in the cornea slightly larger in diameter than the optic portion of the rigid IOL. As a result, stiffer IOLs are less popular in the market place because of the need for larger incisions, which often leads to increased incidence of postoperative complications, such as induced astigmatism.

While the removal of the cataractous portion and replacement with an IOL implant provides considerable benefit to most cataract patients, this is not always the case. It is estimated that up to thirty percent (30%) of all patients receiving an IOL implant in the lens capsule of the eye, thereafter, develop Posterior Capsule Opacification (PCO) or secondary characteristics within five years after surgery. PCO is an IOL implant opacification resulting from cell and fiber deposition on the posterior surface and on the posterior capsule membrane of the IOL implant. These deposits of cells and fibers block the passage of light through the implanted IOL and obscure the patient's vision. The main causes of PCO are migration and opacification of the capsular membrane by the residual epithelial cells of the lens.

In view of the deficiencies seen with past and present IOL designs, it is desirable to construct IOL implants to prevent PCO.

Disclosure of Invention

Intraocular lenses (IOLs) made in accordance with the present invention have an optic portion with an outer periphery and two or more, but preferably two, three or four balanced haptic elements to support the optic portion within a patient's eye. Preferably, each haptic element has the same shape to achieve a helical effect to facilitate implantation, rotation and centering of the IOL. The spiral effect also improves accessibility to the interior of the bladder to facilitate cleaning of cortical residue. Each haptic element has an inner portion and an outer portion. The inner portion of each haptic element includes an enlarged fixation portion permanently attached to the outer periphery of the optic portion. The outer portion of each haptic element includes a rounded free end. Each haptic element includes an arcuate elongated central portion extending between the enlarged fixation portion and a rounded free end. The haptic element may be of constant or variable size from an enlarged fixation portion and the entirety of the elongated portion along the center of the arc. The particular angular shape of the haptics allows the IOL to rotate and prevent posterior capsule opacification.

It is therefore an object of the present invention to provide an intraocular lens for use in an aphakic eye.

It is another object of the present invention to provide an intraocular lens for use in an aphakic eye which can be implanted through a very small incision.

It is another object of the present invention to provide an intraocular lens for use in an aphakic eye which is capable of preventing posterior capsular opacification.

It is another object of the present invention to provide an intraocular lens for use in an aphakic eye which improves the ease of implantation and the ease of rotation and centering of the lens.

It is another object of the present invention to provide an intraocular lens for use in an aphakic eye that is biocompatible for use in an aphakic eye.

It is a further object of the present invention to provide an intraocular lens for use in an aphakic eye which prevents decentration within the eye.

Drawings

These and other objects and advantages in accordance with the present invention, some of which will be described in detail and others which will not, will become apparent from the following detailed description, from the drawings and from the claims, wherein like features have been given like reference numerals.

FIG. 1 is a schematic view of the interior of a human eye including a natural crystalline lens and a refractive IOL implanted in the capsule of the crystalline lens of the eye;

FIG. 2 is a top view of an IOL made according to the present invention having two haptics;

FIG. 3 is a side view of the IOL of FIG. 2;

FIG. 4 is a cross-sectional view of the optic portion of the IOL of FIG. 2 taken along line 4-4 of FIG. 2;

FIG. 5 is a cross-sectional view of the haptic elements of the IOL of FIG. 2 taken along line 5-5 of FIG. 2;

FIG. 6 is a transverse view of the haptic elements of the IOL of FIG. 2, taken along line 6-6 of FIG. 2;

FIG. 7 is a transverse view of the haptic elements of the IOL of FIG. 2, taken along line 7-7 of FIG. 2;

FIG. 8 is a top view of another embodiment of an IOL having two haptics made in accordance with the present invention;

FIG. 9 is a side view of the IOL of FIG. 8;

FIG. 10 is a cross-sectional view of the optic portion of the IOL of FIG. 8 taken along line 10-10 of FIG. 8;

FIG. 11 is a cross-sectional view of the haptic elements of the IOL of FIG. 8 taken along line 11-11 of FIG. 8;

FIG. 12 is a cross-sectional view of the haptic elements of the IOL of FIG. 8 taken along line 12-12 of FIG. 8;

FIG. 13 is a cross-sectional view of the haptic elements of the IOL of FIG. 8 taken along line 13-13 of FIG. 8;

FIG. 14 is a top view of another embodiment of an IOL having three haptics made in accordance with the present invention;

FIG. 15 is a side view of the IOL of FIG. 14;

FIG. 16 is a cross-sectional view of the optic portion of the IOL of FIG. 14 taken along line 16-16 of FIG. 14;

FIG. 17 is a cross-sectional view of the haptic elements of the IOL of FIG. 14 taken along line 17-17 of FIG. 14;

FIG. 18 is a cross-sectional view of the haptic elements of the IOL of FIG. 14 taken along line 18-18 of FIG. 14;

FIG. 19 is a cross-sectional view of the haptic elements of the IOL of FIG. 14 taken along line 19-19 of FIG. 14;

Detailed Description

FIG. 1 is a schematic diagram of an eye showing the structure of the eye involving implantation of an intraocular lens (IOL)12 according to the present invention. The eye includes a clear cornea 14 and iris 16. The lens capsule 18 and retina 20 are disposed behind the iris 16 of the eye 10. Eye 10 also includes an anterior chamber 22 located in front of iris 16 and a posterior chamber 24 located between iris 16 and lens 18. The IOL is preferably implanted in the lens capsule 18 of an aphakic eye. IOL 12 is used to replace surgically removed diseased natural lenses when they are used in aphakic eyes, for example after cataract surgery. Eye 10 also includes an optical axis OA-OA that is an imaginary line passing through the optical centers of anterior surface 30 and posterior surface 32 of lens capsule 18. Optical axis OA-OA in human eye 10 is generally perpendicular to retina 14, perpendicular to lens 18 and cornea 20.

An IOL according to the present invention is shown in figures 2, 8 and 14 and designated by reference numeral 12 and is configured for implantation preferably within the lens capsule 18 of an aphakic eye. The IOL 12 has an optic portion 34, the optic portion 34 having an outer periphery 36. Two or more, preferably two, three or four equally spaced haptic elements 38 are preferably integrally formed with the peripheral edge 36 of the optic portion 34. Each haptic element 38 has the same shape to achieve a helical appearance to facilitate rotation and centering of IOL 12 and to achieve rotation of IOL 12 when implanted in eye 10, as described in greater detail below.

Each haptic element 38 is manufactured to have an inner portion 40 and an outer portion 42. Inner portion 40 of each haptic element 38 includes a fixed portion 44 that is preferably integrally formed and permanently connected to outer periphery 36 of optic portion 34. However, as a modification, the enlarged fixation portion of each haptic element 38 may be permanently fixed to optic portion 34 using staples, chemical polymerization, or other methods known to those skilled in the art. Each haptic element 38 also includes a free rounded end 46 on outer portion 42 that is configured to avoid contact with an inner surface 48 of the lens capsule 18 of the aphakic eye 10.

Haptic element 38 has an arcuate elongated central portion 50 extending between enlarged fixation portion 44 and free end 46. As shown in fig. 5-7, 11-13, and 17-19, the cross-section of haptic element 38 has a trapezoidal shape, or as a modification, a rhombus shape, from enlarged fixation portion 44 and all elongated portions 50 along the arc to achieve the desired PCO prevention feature.

As seen in FIGS. 5-7, the haptic elements 38 are trapezoidal in cross-section at lines 5-5, 6-6 and 7-7, with the outer side 60 of the trapezoid including an acute angle 52 at its lower portion and an obtuse angle 71 at its upper portion.

The particular shape of the tactile element produces two effects: on the one hand, the migration of the capsular cells along the posterior surface is blocked due to the acute tactile edge 52, while on the other hand, a rapid occlusion between the anterior surface 30 and the posterior surface 32 is possible due to the obtuse outer anterior tactile edge 71. This occlusion is caused by a known phenomenon known as syngeney, according to which the two walls 30 and 32 of the capsular bag (capsular sac) are joined to each other when the capsular bag is empty. When they are so bound together, the bursa cells are no longer moving.

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

Haptic elements 38 may be constant or may vary in size from enlarged fixation portion 44 and along the entirety of central portion 50 in planes 68-68 substantially perpendicular to optical axis OA-OA. Haptic elements 38 of regular size throughout from enlarged fixation portion 44 and along central portion 50 are best shown in fig. 6, 12 and 18. However, having varying sizes increases the complexity of the embodiments, which are dealt with in more detail below.

In a production mode of the haptic element where the size varies from the enlarged fixation portion 44 to the rounded free end 46, the width of the haptic element 38 gradually increases in the planes 68-68, and the width of the front surface 62 is 1.2 to 1.4mm approximately at the enlarged fixation portion. The front surface 62 is preferably about 30% narrower than the rear surface 64, and the rear surface 64 is preferably 1.6 to 1.9mm wide, as shown in the embodiments of fig. 5, 11 and 17. As shown in the embodiments of fig. 6, 8 and 16, the width of the front surface 62 is about 1.0 to 1.2mm at about the middle portion 56. The front surface 62 is preferably about 15% narrower than the rear surface 64, and the rear surface 64 preferably has a width of 1.2 to 1.5 mm. As shown in fig. 7, 13 and 19, the front surface 62 and the rear surface 64 have about the same width, approximately 0.5 to 1.0mm, approximately forward of the rounded free end 46.

From enlarged fixation portion 44 toward rounded free end 46, haptic element 38 has a uniform thickness along plane 66-66 parallel to optical axis OA-OA. As shown in fig. 5-7 and 17-19, the surface of the inner edge 58 of the haptic element has a thickness of about 0.20 to 0.80mm, preferably 0.34 to 0.48 mm. As a modification, the surfaces of haptic inner edges 58 may be inclined at any given angle relative to the IOL's anterior surface 62 and IOL's posterior surface 64 to form an inner anterior haptic edge 70 along the IOL's anterior surface 62, as shown in the embodiment of figures 11 through 13. As shown in Figs. 5-7 and 17-19, the surface of the haptic outer edge 60 is not perpendicular to the IOL's anterior surface 62 and IOL's posterior surface 64 but is angled to form an acute angle of the outer posterior haptic edge 52 along the IOL's posterior surface 64.

Generally speaking, the width of haptic element 38 may decrease in planes 68-68 while the thickness in planes 66-66 remains constant when moving from enlarged fixation portion 44 toward end 42.

IOL 12 is preferably manufactured to have an optic portion 34 with a diameter of about 4.5 to 9.0mm, preferably 5.0 to 6.0mm, and more preferably 6.0mm, and a peripheral edge 36 with a thickness of 0.2 to 1.0mm, preferably 0.2 to 0.8mm, and more preferably 0.3 to 0.5mm, as shown in the embodiment of FIG. 2. As a modification, as shown in the embodiment of FIGS. 8 and 14, the peripheral edge 36 of optic portion 34 is not perpendicular to the IOL's posterior surface 64 but is angled. With such an angled peripheral edge 36, an acute posterior optic edge 54 is formed along the posterior surface of the IOL as shown in figures 10 and 16.

As seen in fig. 10, the perimeter 36 is provided as an extension of the surface of the optic portion 34.

Haptic elements 38 extend generally in an arcuate fashion from optic portion 34 and increase or decrease in length depending on the diameter of the optic portion. As the diameter of optic portion 34 increases, the overall length of haptic element 38 decreases, and similarly, as the diameter of optic portion 34 decreases, the overall length of haptic element 38 increases. Generally, the length of the tactile element, measured between the center of the enlarged anchoring portion 44 and the center of the rounded free end 46, is between about 2.6 to 6.0mm, preferably 3.4 to 5.5mm, and more preferably 4.8 mm. The IOL preferably has an overall length of between 11 and 13mm, measured between the contact area 72 and the opposing contact area 72.

During implantation, IOL 12 is preferably positioned such that contact area 72 of outer posterior haptic edge 52 is in contact with inner surface 48 of lens capsule 18. Haptic elements 38 of IOL 12 are angled outwardly into continuous contact between contact region 72 and inner surface 48. This positions IOL 12 within lens capsule 18 with central portions 50 of haptic elements 38 deflected slightly inward in planes 68-68. The central portions 50 are thus deflected under pressure because they have a reduced width relative to the width of the enlarged fixing portion 44. During deformation (flex) of the central portion of haptic element 38, the surface of inner haptic edge 58 moves closer to outer perimeter 36. During implantation, the outer posterior haptic edge 52, preferably together with the posterior optic edge 54 of IOL 12, contacts the inner surface 48 of the lens capsule 18 to prevent PCO. The outer posterior haptic edge 52 and the posterior optic edge 54 prevent PCO by acting as a barrier to migration and cell proliferation within the lens 18. As a result, stable and reliable refractive correction is achieved when IOL 12 is used as a refractive lens.

Suitable materials for producing IOLs include, but are not limited to, flexible or compressible materials such as silicone polymers, hydrocarbon and fluorinated hydrocarbon polymers, anhydrous, low water and high water acrylic polymers, polyesters, polyamides, polyurethanes, silicone polymers with hydrophilic monomer additives, fluorine-containing silicone elastomers, and combinations of the various materials listed above. Preferred materials for making IOL 12 according to the present invention are hydrophilic or hydrophobic acrylic materials, such as those known to those skilled in the art. Poly (hydroxyethyl methacrylate-co-hydroxyhexyl methacrylate) (poly (HEMA-co-HOHEXMA)) and methyl methacrylate-hydroxyethyl methacrylate (MMA-HEMA) are preferred hydrophilic acrylic materials for use in the manufacture of IOLs because they have a balanced water content of between about 17 and 27 percent by weight, a high refractive index of about 1.46 or greater, which is higher than the refractive index of the eye's hydrated (crystalline) body, which is 1.33. High refractive index is a desirable property for producing IOLs that can produce high power with minimal optical thickness, and by using materials with high refractive indices, vision resolution defects can be corrected with thicker IOLs. Poly (HEMA-co-HOHEXMA) and MMA-HEMA are also desirable materials for fabricating IOLs because their mechanical resistance is suitable for physical manipulation comparable to resistance. Poly (HEMA-co-HOHEXMA) and MMA-HEMA also have desirable memory properties suitable for use as IOLs. With materials having good memory properties, such as poly (HEMA-co-HOHEXMA) and MMA-HEMA, IOLs are made that peel away from the eye in a controlled manner, rather than a sudden manner, to maintain their intended shape. Burst detachment of the IOL is undesirable because it can cause potential damage to delicate tissues within the eye. Poly (HEMA-co-HOHEXMA) and MMA-HEMA also have non-deformability in the eye.

Similarly, IOLs may be manufactured from a variety of materials having a variety of different physical characteristics. For example, the IOL may be produced with optic portion 34 made of a hydrophilic acrylic material having a high refractive index, haptic elements 38 made of a material that is more rigid than optic portion 34, and contact regions 72 made of the same material as the optic portion or another material having a lower refractive index and a higher glass transition temperature.

Although the present disclosure is preferably applied to soft or flexible IOLs made of flexible or compressible materials, harder, less flexible lenses made of more rigid materials such as Polymethylmethacrylate (PMMA) are also applicable, with soft haptics made of the same material or different materials.

The optic portion 34 of the IOL may be a lens having a positive function (power) between 0 and about +40 diopters or a lens having a negative function between 0 and about-30 diopters. The optical portion may be biconvex, planoconvex, biconcave or convex-concave (crescent-shaped) according to the necessary function to obtain a central and edge thickness for efficient operation.

Alternatively, IOL optic 34 may be formed with a reduced brightness region 74 adjacent outer edge 36 having a width of about 0.25 to 0.75mm, preferably 0.3 to 0.6mm, and more preferably 0.5mm to reduce brightness when outer edge 36 of IOL 12 is illuminated by light passing through the eye in high light conditions or when pupil 76 dilates at other times. The reduced brightness region 74 is characterized as being fabricated from the same material as the optic portion 34, but may be opaque, colored or otherwise conventionally configured to block or scatter light in a plane OA-OA having an optical axis.

IOL 12 is preferably first manufactured from disks produced from one or more materials selected from the group consisting of the one or more materials described in U.S. Pat. Nos. 5,217,491 and 5,326,506. IOL 12 can thus be processed from sheet stock in a conventional manner. After processing, IOL 12 may be polished, cleaned, sterilized and packaged in a conventional manner known to those skilled in the art.

An incision is made in cornea 14, IOL 12 is implanted in posterior chamber 24 and the incision is closed, and IOL 12 can be used in an eye, according to methods known to those skilled in the art. However, the IOL can be used in the eye by making an incision, preferably in the cornea 14 and lens capsule 18, removing the natural lens, implanting IOL 12 in the lens capsule 18 and closing the incision by methods known to those skilled in the art.

IOL 12 according to the present invention provides a refractive lens suitable for use in lens capsule 18 and posterior chamber 24, but is preferably used in lens capsule 18 because of its features to prevent PCO. IOL 12 has similarly shaped haptics 38 to minimize or limit decentration and visual deformation of IOL 12. The similar shape of haptic elements 38 allows them to rotate in the same manner as IOL 12 for better positioning and accommodation within the lens capsule 18. A better accommodation within the lens capsule 18 has advantages because one or several sizes of the lens accommodate most sizes of the eye 10 in a suitable manner. By providing a "universal" lens, such as a lens according to the present invention, medical risks to the patient due to improper size of the lens are minimized. Also, the manufacturer need not produce IOLs of various sizes to accommodate them in the various sizes of the eye, which will reduce the cost of production and thus storage. Ophthalmologists also benefit from IOLs, saving time and the associated costs of maintaining an inventory of lenses of various sizes, as there is no need to determine the size of each patient's eye.

Another feature of the IOL shown in the embodiment of FIG. 14 is one or more, preferably between one and three, external edge grooves 78. The outer edge groove 78 allows for more thorough surgical irrigation and thus better cleaning of the viscous elastomer and lens cortex residues within the lens capsule 18 to remove viscous elastomer residues and other residues. The outer edge groove 78 improves fluid circulation by providing a clean path for the fluid to pass through. This enables a more thorough cleaning of the interior of the lens capsule 18 by means of an enhanced fluid circulation.

While particular embodiments of the present invention have been illustrated and described above, it will be obvious to those skilled in the art that various changes may be made without departing from the spirit and scope of the inventive concept and that the claims are not limited to the particular shapes illustrated and described herein.

Claims (19)

1. An intraocular lens for implantation within an eye generally perpendicular to an optical axis of the eye, comprising:

a front surface (34);

a rear surface (64);

an outer perimeter (36) between the front and back surfaces defining an optic portion (34), wherein the outer perimeter (36) forms an obtuse angle with at least a portion of the front surface and the outer perimeter (36) forms an acute angle with at least a portion of the back surface;

two or more haptic elements (38) having the same transverse trapezoidal or rhombus cross-section permanently attached to the outer perimeter (36); and

an acute outer rear tactile edge (52) on the tactile element (38).

2. An intraocular lens for implantation within the lens capsule generally perpendicular to the optical axis of the eye to prevent posterior capsular opacification comprising:

a front surface (34);

a rear surface (64);

an outer perimeter (36) between said anterior surface (34) and said posterior surface (64) defining an optic portion (34), wherein said outer perimeter (36) and at least a portion of said posterior surface form an acute angle;

two or more haptic elements (38) having the same transverse trapezoidal or rhombus cross-section permanently attached to the outer perimeter (36); and

an acute outer rear tactile edge (52) on the tactile element (38).

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

4. An intraocular lens according to claim 1 or 2, wherein said lens is made of a material selected from the group consisting of silicone polymers, hydrocarbon and fluorinated hydrocarbon polymers, hydrogels, soft acrylic polymers, polyesters, polyamides, polyurethanes, silicone polymers with hydrophilic monomer additives, fluorine-containing silicone elastomers and combinations of the foregoing.

5. An intraocular lens according to claim 1 or 2, wherein said lens is made of a hydrophilic acrylic material.

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

7. An intraocular lens according to claim 1 or 2, wherein the lens is manufactured with poly (hydroxyethyl methacrylate-co-yl hydroxyhexyl methacrylate).

8. An intraocular lens according to claim 1 or 2, wherein the lens is made of one or more materials, wherein at least one material has a refractive index of more than 1.33.

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

10. An intraocular lens according to claim 1 or 2, wherein said lens is made of one or more materials, at least one of which is a silicone material.

11. Intraocular lens according to claim 1 or 2, wherein said haptic elements (38) have the same thickness.

12. An intraocular lens according to claim 1 or 2, wherein a zone of reduced brightness (74) is formed adjacent the outer periphery (36) of the optic portion (34).

13. Intraocular lens according to claim 1 or 2, wherein said outer periphery (36) and said posterior surface form an acute angle between said haptic elements (38).

14. Intraocular lens according to claim 1 or 2, wherein said outer periphery (36) and said anterior surface form an obtuse angle between said haptic elements (38).

15. For implanting an intraocular lens in an eye positioned in a posterior chamber of the eye generally perpendicular to an optical axis of the eye, comprising:

a front surface;

a rear surface;

an outer perimeter (36) between the anterior and posterior surfaces defining an optic portion (34), wherein the outer perimeter (36) and at least a portion of the posterior surface form an acute angle;

two or more haptic elements (38) having the same transverse trapezoidal or rhombus cross-section permanently attached to the outer perimeter (36); and

an acute outer rear tactile edge (52) on the tactile element (38).

16. Intraocular lens according to claim 1, 2 or 15, wherein the haptic elements (38) have a trapezoidal cross section so as to have an acute angle (52) blocking the migration of capsular cells along the posterior surface (64) of the optical portion (34).

17. Intraocular lens according to claim 16, wherein the trapezoidal cross-sectional shape of the haptic elements (38) promotes syngeneic phenomena, i.e. the adhesion of the walls (30) and (32) of the capsular bag against each other, which completely prevents the migration of the capsular cells.

18. Intra-confined lens according to claim 1, 2 or 15, wherein the haptic elements (38) have a rhombus-shaped cross-section so as to have an acute angle (52) that blocks the migration of capsular cells along the posterior surface (64) of the optical portion (34).

19. Intraocular lens according to claim 18, wherein the rhombus-shaped cross-sectional shape of the haptic elements (38) promotes synbiosis, i.e. the adhesion of the walls (30) and (32) of the capsular bag against each other, which completely prevents the migration of the capsular cells.