CA2093097A1

CA2093097A1 - Corrective lens

Info

Publication number: CA2093097A1
Application number: CA002093097A
Authority: CA
Inventors: Svyatoslav N. Fedorov; Viktor K. Zuev; Paul U. Fechner; Christine F. Kreiner; Alexander Serester
Original assignee: Adatomed Pharmazeutische und Medizintechnische GmbH
Current assignee: Adatomed Pharmazeutische und Medizintechnische GmbH
Priority date: 1992-04-03
Filing date: 1993-03-31
Publication date: 1993-10-04
Also published as: EP0563602B1; EP0563602A1; ES2098572T3; ATE146667T1; JP3173910B2; DE59304849D1; JPH06277242A; DE4211265C1

Abstract

ABSTRACT OF THE INVENTION

A correction lens which is implantable at the front of a natural lens of an eye includes an optical lens portion and a haptic around at least part of the optical portion. The haptic comprises an inwardly disposed haptic portion and an outwardly disposed haptic portion. The inward haptic portion and the optical lens portion have a unitary radius of curvature which is adapted to the outside surface of the natural lens. The outward edge zone of the haptic at the rear face thereof is of a configuration which differs from the radius of curvature of the rear face of the optical lens portion and the inner haptic portion, so that that differing configuration tends to lift away from the surface of the natural lens.

Description

2093~97 The present invention concerns a correction lens which is implantable on to the front side of the natural crystalline lens of an eye.
An implantable correction lens which can be used for the treatment of myopia, hypermetropia and astigmatism is fitted by implantation on to the front side of the nautral crystalline lens of the eye requiring correction. The correction lens has an optical lens portion which is normally of a circular configuration, a positioning portion and a support portion adjoining same. When the correction lens is in the implanted condition, the positioning portion and the support portion are between the iris and the front surface of the natural lens of the eye.
The implanted lens thus serves as a substitute for conventional spectacle lenses, contact lenses which are fitted on to the cornea or other correction procedures such as the removal of layers of the cornea.
According to the present invention there is provided a correction lens which is implantable at the front of a natural lens of an eye, comprising an optical lens portion and a haptic at least partially surrounding the optical lens portion, wherein the haptic is subdivided in a radial direction into an inner haptic portion around the optical lens portion and an outer haptic portion, the haptic portions having outer boundary lines which lie at least partly on circular arcs, wherein the outer haptic portion at its rear side which in the implanted condition of the correction lens is towards the natural lens has a geometrical configuration which differs from the configuration of the surface geometry of the rear faces of the optical lens portion and the inner haptic portion, and wherein beginning at the outer boundary line of the inner haptic portion and extending towards the outer edge of the outer haptic portion , the rear side of the outer haptic portion extends perpendicularly to the optical axis of the optical lens portion.

2093~97 As will be seen in greater detail hereinafter, in the implantable correction lens according to the invention, the haptic which comprises an inner haptic portion at least partially surrounding the optical lens portion and an outer haptic portion or support portion which forms the outward edge region of the correction lens is of such a configuration in the outer haptic portion that the rear side thereof extends at least substantially perpendicularly to the optical axis of the optical lens portion. The outer haptic portion or support portion has, at its front and rear sides, flat surfaces which extend at least substantially straight and parallel to each other. In the implanted condition of the lens, that geometrical configuration means that, in the outer haptic portion or outward edge region, the haptic doe s not curve round to follow the curvature of the natural crystalline lens of the eye but lifts away from the surface thereof.
As a result, even in a situation involving capillary adhesion between the implanted correction lens and the front surface of the natural lens of the eye, the haptic, in the outward portion thereof, has a tendency to lift progressively away from the surface of the natural lens. That considerably reduces the chafing effect on the zonule fibers, when the natural lens of the eye performs its natural movements. The overall diameter of the correction lens is preferably such that the outward haptic portion lies in the region of the zonule fibers which extend between the natural lens of the eye and the ciliary muscle. The fact that the rear side of the outer haptic portion extends substantially per,oe ndicularly relative to the lens axis, with the rear side thereof being substantially matched to the radial configuration of the zonule fibers ensures reliable contact such as properly to define the position of the correction lens, while however the area of contact with the natural lens of the eye is as small as possible in order not to impair the metabolic procedure involved.

2 0 ~ 7 Preferably the lens has a circular optical lens portion while the haptic p~rtion may be made up of a plurality of parts. mus, to provide a reduction in lens surface area, the haptic may have lateral boundary edges which depart frcm an arcuate shape, at the nine o'clock and three o'clock sides. The lateral boundary edges extend at least substantially parallel to each other. The upper and lower boundary edges at the twelve o'clock side and the six o'clock side extend in a continuous arcuate shape between the respective ends of the lateral boundary edges which extend in at least substantially straight line.
The two arcuate lines may have a common center point which coincides with the optical axis of the lens. They are arcs which extend concentrically around the circular optical lens portion, the center point of which is also on the optical axis of the lens.
As indicated above, extending between the outer edge portion or outer haptic portion, which forms the support portion thereof, and the optical lens portion, is the inner haptic portion which constitutes a positioning portion for the lens. The front side of the positioning portion or inner haptic portion is of such a configuration as to ensure, in conjunction with the iris lying thereagainst, that the correction lens is positioned in the desired position, relative to the natural lens of the eye. In that condition the optical axes of the natural lens and the correction lens should at least approximately coincide. The front side of the inner or positioning portion of the haptic forms a sliding surface for movement of the iris thereover.
That front side of the inner haptic portion may be of a concave, flat or convex configuration. Preferably the inner haptic portion is such that, beginning from the circular junction between the inner haptic portion and the optical lens portion, the inner haptic portion decreases in thickness, for example tapers, towards the outer edge of the correction lens.
The junction between the inner haptic portion and the outer haptic portion or support portion also extends along two arcs which are concentric relative to the circular edge of the optical lens portion and the two upper and lower arcuate boundary edges of the outer haptic portion. The tw~ arcs defining the junctions between the inner haptic portion and the outer haptic portion also extend continuously between the boundary edges at the tw~ sides of the lens.
The overall geometrical configuration of the correction lens, in the implanted condition, ensures that the surface of the natural lens of the eye remains accessible for the metabolism procedure which occurs at that location. The haptic may additionally be provided with openings or holes so that the area of the natural lens, which is covered by the correction lens, is still further reduced. All boundary edges of the lens can be rounded off so that the lens does not have any sharp edge configurations.
In order to provide that the implanted lens is fitted in position in such a way as to give the best possible floating effect, it is of a specific weight which is approximately equal to that of the eye chamber fluid, namely about 1.1.
So that the correction lens is prevented from turning after being implanted in the eye, the respective peripheral portion of the haptic, which is in the region of the ciliary sulcus of the eye,may be of a non-uniform or variable curved configuration which however only insignificantly departs from the circular shape of the ciliary sulcus.
That further provides for gentle engagement between the ~espective peripheral portion of the haptic of the correction lens and the adjoining eye tissue. The variable curved configuration at the respective peripheral portions of the haptic may be polygonal or may involve convex and/or concave configurations. The respective peripheral portion of the haptic may be fonmed alternately by planar, convex or concave and circular contour segments. The depth or the height of the respective convex or concave configurations, relative to the adjacent peripheral portions, are such that they are only a ~093~97 fraction of their longitudinal dimension in the peripheral direction.
That ensures that, upon implantation of the ~, the concave or convex portions which thus constitute projections on or recesses in the haptic do not lose their desired shape and form a reliable means for preventing the implanted lens from turning in the eye in which it is implanted. The periphery of the lens retains a configuration which approximates to an arcuate shape.
Preferably, the correction lens according to the invention has tw~ peripheral haptic parts which are arranged diametrally opposite relative to the axis of the lens and which, after implantation of the correction lens, are disposed in the region of the ciliary sulcus of the eye. The boundary lines of the contour segments at the peripheral parts of the haptic may be straight or arcuate. At the transitions between contour segments of different configurations, for example between contour segments which are of a straight and an arcuate configuration respectively, that arrangement provides anchorage points for the adjacent tissue of the eye without the latter beccming irritated and inflamed. The above-mentioned transitions or intersections further contribute to ensuring that the correction lens is prevented frcm turning in the eye, in the desired manner.
Preferably, the above-mentioned concave or convex portions at the respective peripheral parts of the haptic may be of a depth or height respectively, relative to the adjacent peripheral regions, which corresponds to between about one sixth and one third of their longitudinal extent in the peripheral direction. Thus, the depth or height thereof respectively may be between about 0.2 and 0.4 mm while the longitudinal dimension may be between about 0.8 and 1.4 mm in the peripheral direction.
Embodiments of the corrections lens according to the present invention will now be described by way of example with reference to the accompanying drawings in which:

2093~97 Figure 1 is a view in section through a first embodiment of a correction lens according to the invention, Figure 2 is a plan view of the lens shown in Figure 1, Figure 3 is a plan view of a second embodiment of a lens according to the invention, Figure 4 is a plan view of a third embodiment of a lens according to the invention, Figure 5 is a plan view of a fourth embodiment of a lens according to the invention, Figure 6 is a plan view of a fifth embodiment of a lens according to the invention, Figure 7 is a plan view of a sixth embodiment of a lens according to the invention, Figure 8 is a plan view of a seventh embodiment of a lens according to the invention, Figure 9 is a plan view of an eighth embodiment of a lens according to the invention, and Figure 10 is a plan view of a ninth embodiment of a lens according to the invention.
Referring firstly to Figures 1 and 2, as shcwn therein the lens body of the illustrated correction lens according to the invention comprises an optical lens portion generally indicated at and a haptic which is disposed at least in part around the optical lens portion 1. The haptic illustrated camprises first and second portions, namely an inner haptic portion or positioning portion 2 which adjoins and at least partially surrounds the optical lens portion 1, and an outer haptic portion or support portion which adjoins the positioning portion 2 and which is made up of first and second parts 3 and 4. In the illustrated embodiment the optical lens 20~3097 portion 1 is circular and its optical axis, which is the axis of the correction lens, is identified by the line A. The optical lens portion 1 fonms the actual correction portion of the lens and is of a biconcave shape having a front side 5 and a rear side 6. The rear side 6 has a radius of curvature which is matched to the outside of the natural crystalline lens of the eye to be corrected by implantation of the correction lens. The radius of curvature R of the rear side 6 of the optical lens portion 1 is for ex.ample about 10 mm + 1 mml while the diameter of the optical lens portion 1, as indicated at Dl, is for example about 4 mm + 1 mm.
At a circular annular connecting location as indicated at 13 in Figures 1 and 2, the optical lens portion 1 passes into the haptic, more specifically the inner haptic portion or positioning portion 2.
Starting fram the connecting location 13, the cross-section of the inner haptic portion 2 decreases in a tapering configuration in an outward direction, as can be seen in particular fram Figure 1. In the illustrated embodiment the inner haptic portion 2 is of a biconcave configuration. It is also possible however for the inner haptic portion 2 to be of a plane-concave configuration, in which case the rear side 8 of the inner haptic portion 2 is of the same radius of curvature R as the rear side 6 of the optical lens portion 1. The front side 7 of the inner haptic portion 2 can be of a concave or planar configuration. It is also possible however for the front side 7 to be convex. The inner haptic portion 2 fonms a sliding surface for iris movement, in particular for the pupil. The configuration of the front side 7 of the inner haptic portion, namely concave, planar or convex, depends on the thickness of the optical lens portion 1.
Adjoining the inner haptic portion 2 which surrounds the optical lens portion 1 in the form of a one-piece surface, in a radially outward direction, is the outer haptic portion defined by first and second edge regions or support parts as indicated at 3 and 209~097 4. As can be seen in particular from Figure 1, the rear face 10 of the support parts 3 and 4 differs considerably from the configuration of the rear faces 6 and 8 of the optical lens portion 1 and the inner haptic portion 2. The rear faces 10 are of a flat configuration and S extend at least substantially perpendicularly to the axis A of the lens. In the illustrated embodiment, the front sides 9 of the su~port parts 3 and 4 also extend at least substantially perpendicularly to the optical axis A and are also of a flat configuration. The thickness d of the support parts 3 and 4 is for exdl~le about 0.1 mm. The junctions, as indicated at 11, between the inner haptic portion 2 and the support parts 3 and 4, are of an arcuate configuration. The two arcs defining the junctions 11 have a co~mon center point which lies on the axis A of the lens. The arcuate junctions 11 terminate at lateral boundary edges 14 and 15 which are at least substantially straight edges. In the illustrated embodiment, the arcuate junctions 11 extend over an angular region as indicated at a in Figure 2, of about 90. That angular region may also be for example between about 80 and about 100, depending on the width B of the lens, being defined by the spacing between the two lateral boundary edges 14 and lS of the lens. In the illustrated embodiment the width B of the lens body is about 6 mm ~ 1 mm.
The two outer edge regions or support parts 3 and 4 defining the outer haptic portion also have outer boundary edges as indicated at 16 and 17, which are also of a continuous arcuate configuration and which each terminate at the ends of the respective lateral boundary edgs 14 and 15. The two arcs providing the boundary edges 16 and 17 may also have a common center point which lies on the axis A of the lens.
The overall diameter of the lens body, as indicatedat D3 in Figure 2, that is to say, the spacing between the two arcuate boundary edges 16 and 17, is for example about 11 mm, in the illustrated embcdiment. It will be appreciated however that the overall diameter 2093~97 of the lens body can be varied according to the eye into which the correction lens is to be implanted. Such variations are generally in a range of about t 1 mm.
In the illustrated embodiment, the diameter D2 illustrated in Figure 1, being the spacing between the tw~ arcuate junctions 11, is about 8 mm, that is to say approximately double the diameter Dl of the optical lens portion 1. The diameter D2 can also vary, in dependence on the diameter D3. The diameter D2 is such that it is less than three quarters of the diameter D3.
Reference will now be made to Figures 3 and 4 showing another embodiment of the lens according to the invention, in which the two lateral boundary edges 19 and 20 of the lens body are of such a shape as to extend arcuately, possibly in a circular configuration in an inward direction so that they are concave. m e embodiment shown in Figure 3 further has concave portions formed by recesses 21 and 22, approximately in the middle of the tw~ edge regions or support parts 3 and 4 of the outer haptic portion. Both the concavely shaped lateral boundary edges 19 and 20 and also the recesses 21 and 22 contribute to improving the metabolism procedure at the outward face of the natural crystalline lens cn which the correction lens according to the invention is implanted, by virtue of the reduction in the surface area of the correction lens.
Looking now at Figure 5, shown therein is an embodiment of the correction lens which is of a generally star-shaped configuration.
Reference numeral 1 again denotes the optical lens portion and reference numeral 2 shows the inner haptic portion. The outer haptic portion which adjoins the inner haptic portion 2 is formed by the projections 23, 24 and 25 which are at an angular spacing from each other of about 120. It will be seen that the inner haptic portion 2 is formed by a circular ring.
The lens body consisting of the optical lens portion 1 and 2~93097 the haptic may be made in one piece. A transparent biocompatible material can be used as the material for the lens, and it is preferably in the form of a soft and/or resilient material. The lens material is preferably also hydrophilic and/or gas-permeable, in particular being permeable to oxygen. ~he lens mate~ial may be for ex~l~le silicone rubber, polyhydroxy ethyl methacrylate, a copolymer of silicone and methyl methacrylate, polyvinylpyrrolidone and other materials which are compatible with the eye tissue.
It may be noted at this point that, in order further to reduce the surface area of the correction lens and to improve accessibility to the surface of the natural crystalline lens of the eye, for example for the metabolism procedure, the lens body may also be provided in the region of its haptic with openings as indicated at 18 in Figure 2, for example in the form of round holes or the like.
Referring now to Figures 6 through 10, the embodiments illustrated therein again comprise the optical lens portion 1 which is surrounded by the haptic formed by an inner haptic portion 2 and an outer haptic p~rtion as indicated at 3. In the illustrated embodiments the haptic has the substantially straight lateral boundary edges 14 and 15. It will be a~preciated however that it is also possible for the lateral boundary edges to be of an inwardly curved or concave configuration.
The outer haptic portion has tw~ peripheral parts, one thereof being shown in each of Figures 6 through 10. In the implanted condition of the correction lens, the peripheral part constituting a support part 3 as illustrated in Figures 6 through 10 lies in the region of the ciliary sulcus. The tw~ peripheral parts of the haptic extend over an angular range as indicated at a, relative to the optical axis A of the lens. That angle a may be of the order of magnitude of between about 50 and 90.

20~3as7 In the illustrated embodiments, the haptic peripheral parts have a non-uniform or variable curved configuration at their peripheral edge.
Looking more specifically at the embodiments shown in Figures 6 and 7, the curved configuration of the haptic periphery is a polygon, within the angular range a.
In the embodiment shown in Figure 7, it is a pure polygon which comprises three sides indicated at 26, 27 and 28.
On the other hand, in the emb~diment shown in Figure 6, concave recesses 29 and 30 are provided in the sides 26 and 28 of the polygon, that is to say in the two outer sides of the polygon illustrated therein, with the middle side 27 of the polygon being straight. The concave recesses 29 and 30 are so arranged that their inward ends are disposed at intersections 31 and 32 between the sides 26 and 28 respectively, and the side 27 disposed therebetween. However the concave recesses 29 and 30 may also be arranged in the middle or at another location along the sides 26 and 28 of the polygon.
In the embodiment shown in Figure 8 the haptic peripheral part, within the angular range a, is of a substantially arcuate configuration with convex projections 34 and 35 extending outwardly therefrom.
In the Figure 9 embodiment, the haptic peripheral part is once again of a substantially arcuate configuration, with concave recesses 29 and 30 extending radially inwardly therefrom.
In the Figure 10 embodiment, the haptic peripheral part is of a polygonal configuration made up of the sides 26, 27 and 28 which intersect at the intersections indicated at 31 and 32. Provided in the region of the sides26 and 28 of the polygon are convex portions or raised portions 34 and 35, which thus project outwardly relative to the polygon peripheral configuration of the haptic portion. The two inner ends of the convex portions 34 and 35 æ e disposed at the 20s3as7 intersections 31 and 32 where the respective sides 26 and 28 of the polygon, meet the side 27 which is therebetween.
The depth of the concave recesses 29 and 30 in the e~bodiments shown in Figures 6 and 9, relative to the adjacent peripheral region, is between about 0.2 and 0.4 mm. In the embodiment shown in Figure 6, the depth is measured in relation to the extension, as shown in broken lines, of the respective sides of the polygon, in the region of the recesses 29 and 30.
In the embodiment shown in Figure 9, the depth is similarly measured in relation to the extension shown in broken line of the arcuate peripheral edge, in the region of the recesses 29 and 30.
In the embodiments shown in Figures 8 and 10, the height of the convex portions or projections 34 and 35 is measured in relation to the continuation, shown in broken lines, of the adjacent arcuate segments 33, in the region of the projections 34 and 35 (Figure 8) or in relation to the broken-line extension of the sides 26, 27 and 28 of the polygon, in the region of the projections 34 and 35 (Figure 10).
In the embodiments of Figures 6, 8, 9 ar.d 10 the longitudinal extent in the peripheral direction of the concave recesses 29 and 30 and the convex portions or projections 34 and 35 is between about 0.8 and 1.4 mm.
In the embodiments shown in Figures 6 through 10, the non-uniform or varying curved configuration of the peripheral part of the haptic still approximates to an arcuate shape. That arcuate shape is of a diameter which is suited to the inside diameter of the ciliary sulcus of the eye in which the lens is to be implanted. That diameter is generally in the region of between about 11.0 and 13.5 mm. The variations in contour which cause the curved configuration to be non-uniform, namely the recesses 29 and 32, and the projections 34 and 35, as well as the transitions between those recesses or projections and the other parts of the peripheral configuration provided by the sides 20~0~7 26 through 28 of the polygon or the arcs 33, provide a holding means which prevents the correction lens from turning in the eye, about the optical axis A of the lens, when the lens is in the implanted condition. That point also applies in regard to the embodiment shcwn S in Figure 7, in which the peripheral contour is a pure polygon. It will be appreciated that although the polygon in the illustrated e~bcdiment in Figure 7 has three sides 26, 27 and 28, it is also possible to use a different number of sides for the polygon and in particular more sides. The intersections 31, 32 between the sides of the polygon provide the necessary holding effect to prevent the co,L~ction lens from turning.
Th.e embodiments shown in Figures 6, 7 and 10 in which the basic contour of the periphery of the haptic portion is a polygon further afford the advantage that the lens body can be cut to size from a larger lens body blank, as a basic shape, to adapt it to the diameter of the ciliary sulcus of the eye into which the correction lens is to be implanted. In that way, it is possible exactly to adapt the overall diameter of the diametrally oppositely disposed haptic peripheral parts, to the corresponding dimension of the eye in which the correction lens is to be implanted.
In the embodiments illustrated in the drawings the optical lens portion 1 is generally of a diameter of about 4.0 mm while the width of the haptic portion 2 from one side edge 14 to the other is for example about 6.0 mm.
When the correction lens is a high-myopia lens with a strength of about -50 dpt, the diameter of the optical lens portion is about 0.2 nm.
The embodiments illustrated in Figures 6 through 10 may be of a cross-section like that illustrated in Figure 1. It will be appreciated that the embodiments shown in Figures 6 through 10 are also suitable for myopia lenses with haptics of a different 2~3097 configuration, for example haptics which are not subdivided into tw~
regions. In that case also the illustrated edge shapes provide that the correction lens is prevented from turning in the eye in ~hich it is implanted.
S The correction lens according to the invention is preferably used to deal with severe myopia, for which purpose the optical lens p~rtion 1 is in the form of a negative lens. Instead of the biconcave configuration of the optical lens portion it may also be of a concave-convex or toric shape.
Upon implantation of the correction lens, the pupil of the eye is enlarged so that the correction lens, with its diameter D3, can be fitted between the iris and the outside surface of the natural lens of the eye. The optical lens portion 1 can then be aligned with its lens axis A on the optical axis of the natural lens of the eye. The edge regions or support parts 3 and 4 forming the outer haptic portion are then in the region of the zonule fibers. The natural movement of those fibers is not or only slightly impeded, by virtue of the specific configuration of the above-mentioned edge regions of the haptic portion.
The implantable correction lens can ensure satisfactory positioning and fixing thereof relative to the crystalline lens of the eye requiring correction and for example can be suitably fixed in position by capillary adhesion, while at least substantially reducing a chafing effect on the zonule fibers extending between the natural lens of the eye and the ciliary muscle upon natural lens movement.
It will be appreciated that the above-described embodiments of the correction lens according to the invention have been set forth solely by way of example and illustration of the principles of the invention and that various other modifications and alterations may be made therein without thereby departing from the spirit and scope of the invention.

Claims

1. A correction lens which is implantable at the front of a natural lens of an eye, comprising an optical lens portion and a haptic at least partially surrounding the optical lens portion, wherein the haptic is subdivided in a radial direction into an inner haptic portion around the optical lens portion and an outer haptic portion, the haptic portions having outer boundary lines which lie at least partly on circular arcs, wherein the outer haptic portion at its rear side which in the implanted condition of the correction lens is towards the natural lens has a geometrical configuration which differs from the configuration of the surface geometry of the rear faces of the optical lens portion and the inner haptic portion, and wherein beginning at the outer boundary line of the inner haptic portion and extending towards the outer edge of the outer haptic portion the rear side of the outer haptic portion extends pependicularly to the optical axis of the optical lens portion.

2, A correction lens as set forth in claim 1 wherein the outer haptic portion comprises at least first and second parts.

3. A correction lens as set forth in claim 1 wherein the cross-section of the inner haptic portion decreases from an outer boundary line of the optical lens portion to the outer boundary line of the inner haptic portion.

4. A correction lens as set forth in claim 1 wherein in the six o'clock/twelve o'clock direction of the lens the extent of the optical lens portion and the inner haptic portion is less than three quarters of the total extent of the lens in said direction.

5. A correction lens as set forth in claim 1 wherein the optical lens portion is circular and in a six o'clock/twelve o'clock direction of the lens the diameter of the optical lens portion is approximately half the diameter of the inner haptic portion in said direction.

6. A correction lens as set forth in claim 1 wherein at the nine o'clock side and the three o'clock side the lens is of a configuration which departs from a circular arcuate shape towards the interior of the circle.

7. A correction lens as set forth in claim 6 wherein at the nine o'clock side and the three o'clock side the lens has at least substantially parallel and straight boundary edges.

8. A correction lens as set forth in claim 6 wherein the lens has concavely extending boundary edges at the nine o'clock and the three o'clock sides.

9. A correction lens as set forth in claim 1 wherein the lens is of a star-like configuration.

10. A correction lens as set forth in claim 1 wherein at the twelve o'clock side and the six o'clock side of the lens the boundary edges of the outer haptic portion extend along continuous circular arcs extending from a lateral boundary edge to the other lateral boundary edge.

11. A correction lens as set forth in claim 10 wherein the center point of the arcs lies at least substantially on the axis of the lens.

12. A correction lens as set forth in claim 1 wherein the junctions between the inner haptic portion and the outer haptic portion lie on two circular arcs whose common center point lies at least substantially on the axis of the lens.

13. A correction lens as set forth in claim 12 wherein each of the two arcs extends over an angle which is between about 80 and 100°.

14. A correction lens as set forth in claim 13 wherein said angle is about 90°.

15. A correction lens as set forth in claim 10 wherein the boundary edges are rounded off.

16. A correction lens as set forth in claim 1 wherein the boundary edges of the outer haptic portion have concave recesses therein.

17. A correction lens as set forth in claim 1 wherein the front side and the rear side of the outer haptic portion are of an at least substantially planar configuration from the junction with the inner haptic portion to the outer boundary edge of the outer haptic portion, and extend in mutually parallel relationship.

18. A correction lens as set forth in claim 1 and further including openings in the outer haptic portion.

19. A correction lens as set forth in claim 1 and further including openings in the inner haptic portion.

20. A correction lens as set forth in claim 2 wherein the outer haptic portion comprises respective peripheral parts in the region of the ciliary sulcus of the eye, which parts are of a non-uniform curve configuration.

21. A correction lens as set forth in claim 20 wherein each said peripheral part is of a polygonal configuration.

22. A correction lens as set forth in claim 20 wherein each said peripheral part has concave portions whose respective depth relative to the adjacent peripheral region is a fraction of their longitudinal extent in the peripheral direction.

23. A correction lens as set forth in claim 20 wherein each said peripheral part has convex portions whose respective height relative to the adjacent peripheral region is a fraction of their longitudinal extent in the peripheral direction.

24. A correction lens as set forth in claim 20 wherein each said concave portion has an end arranged at a respective intersection of adjacent sides of the polygon.

25. A correction lens as set forth in claim 20 wherein each said convex portion has an end arranged at a respective intersection of adjacent sides of the polygon.

26. A correction lens as set forth in claim 21 wherein the respective peripheral part has three polygon sides.

27. A correction lens as set forth in claim 22 wherein the concave portions are of a depth, relative to the adjacent peripheral regions, which corresponds to between one sixth and one third of their longitudinal extent in the peripheral direction.

28. A correction lens as set forth in claim 22 wherein the convex portions are of a height, relative to the adjacent peripheral regions, which corresponds to between one sixth and one third of their longitudinal extent in the peripheral direction.

29. A correction lens as set forth in claim 22 wherein the concave portions have arcuate boundary lines.

30. A correction lens as set forth in claim 22 wherein the convex portions have arcuate boundary lines.

31. A correction lens as set forth in claim 22 wherein the concave portions are of a depth of between about 0.2 and 0.4 mm and have a longitudinal extent of between about 0.8 and 1.4 mm in the peripheral direction.

32. A correction lens as set forth in claim 22 wherein the convex portions are of a height of between about 0.2 and 0.4 mm and have a longitudinal extent of between about 0.8 and 1.4 mm in the peripheral direction.

33. A correction lens as set forth in claim 1 wherein the optical lens portion is in the form of a concave lens.

34. A collection lens as set forth in claim 33 wherein the concave lens is of a diameter of about 2.0 mm.