CA2315338C - Adjustable intraocular lens and method for its production - Google Patents
Adjustable intraocular lens and method for its production Download PDFInfo
- Publication number
- CA2315338C CA2315338C CA002315338A CA2315338A CA2315338C CA 2315338 C CA2315338 C CA 2315338C CA 002315338 A CA002315338 A CA 002315338A CA 2315338 A CA2315338 A CA 2315338A CA 2315338 C CA2315338 C CA 2315338C
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- Canada
- Prior art keywords
- lens body
- adjustment means
- lens
- haptic arms
- haptic
- Prior art date
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- Expired - Lifetime
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- 238000004519 manufacturing process Methods 0.000 title claims description 5
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- 238000005266 casting Methods 0.000 claims description 5
- 238000006073 displacement reaction Methods 0.000 claims 1
- 210000000695 crystalline len Anatomy 0.000 description 137
- 210000004087 cornea Anatomy 0.000 description 9
- 239000000463 material Substances 0.000 description 7
- 238000002513 implantation Methods 0.000 description 5
- 239000007943 implant Substances 0.000 description 4
- 210000001525 retina Anatomy 0.000 description 3
- 210000002159 anterior chamber Anatomy 0.000 description 2
- 239000002775 capsule Substances 0.000 description 2
- 239000012530 fluid Substances 0.000 description 2
- 239000000017 hydrogel Substances 0.000 description 2
- 230000007246 mechanism Effects 0.000 description 2
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- 206010002091 Anaesthesia Diseases 0.000 description 1
- 241000282472 Canis lupus familiaris Species 0.000 description 1
- 208000002177 Cataract Diseases 0.000 description 1
- 102000008186 Collagen Human genes 0.000 description 1
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
- A61F2/16—Intraocular lenses
- A61F2/1613—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
- A61F2/1624—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside
- A61F2/1629—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside for changing longitudinal position, i.e. along the visual axis when implanted
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
- A61F2/16—Intraocular lenses
- A61F2002/1681—Intraocular lenses having supporting structure for lens, e.g. haptics
- A61F2002/1683—Intraocular lenses having supporting structure for lens, e.g. haptics having filiform haptics
- A61F2002/1686—Securing a filiform haptic to a lens body
Abstract
The invention relates to an adjustable intraocular lens with a lens body 1, haptic arms 3 for fixing the lens body 1 in the eye, and an adjustment means for moving the lens body 1 relative to the haptic arm 3 in the direction of the optic axis 27 of the lens body 1 and for adjusting the extent of the movement. The haptic arms 3 are each directly connected to the lens body 1 via one of their ends. The haptic arms 3 preferably have a bifurcation 31, 33, and only one of the two fork ends 31 is connected to the lens body 1. The adjustment means, preferably with an adjusting screw 37, is screwed through one of the two fork ends 31, 33 and changes the distance between the two fork ends 31, 33. The intraocular lens according to the invention is easy and inexpensive to produce.
Description
Adjustable intraocular lens and method for its production -Technical field The invention relates to an intraocular lens and in particular to an intraocular lens in which the focus can be adjusted after implantation. The invention also relates to a method for production of such a lens.
Prior art In patients affected by grey cataract, for example, it is at present customary to remove the diseased and opaque crystalline lens and to replace it with an implant, a so-called intraocular lens (IOL).
An example of an intraocular lens of this type is shown in Figures 1 and 2. The lens consists of a lens body 1 and of two haptic arms 3 connected to the lens body 1. Fig. 2 shows a side view of the lens from Fig. 1.
The lens is preferably made of a soft or foldable material so that it can be folded or rolled along the broken line (A-A). For implantation, after the diseased crystalline lens has been removed, the intraocular lens is inserted into the eye by being folded together during the insertion along the broken line so that the incision in the cornea can be made as small as possible. The lens is unfolded within the eye and is secured in its position, usually in the capsule of the removed lens.
The lenses, which are usually made of a synthetic material such as polyurethane elastomer, silicone elastomer, hydrogel polymer or collagen, can be formed in one piece and are therefore economical to produce. As they can be rolled up or folded up, they can be inserted through a small slit, with the result that the eye rapidly heals after the operation.
However, a disadvantage of these lenses is that incorrect fitting can easily occur, with the result that, even after the operation, the patient requires a means for correcting vision, for example glasses or contact lenses, because the focus of the lens lies before or behind the retina.
To rectify this problem, an adjustable intraocular lens has been proposed in US 5,800,533 and in US 5,728,155. Such a lens is shown in Fig. 3. This prior art lens, which forms the preamble of Claim 1, consists of a cylindrical lens body 1 with an external thread 5, a support device 7 which is annular and has an internal thread 9 matching the external thread 5 of the lens body 1, and haptic arms 3 which are secured to the support device or are formed in one piece with the latter. As the lens body is screwed to a greater or lesser extent into the support device, the distance between the lens body and the retina, and thus the focus, is adjusted.
US 5,728,155 also shows that a flexible lens body can be fitted into the support device, so that it is possible subsequently to exchange the lens via a small incision made through the cornea. This publication additionally discloses that the lens body can also be moved relative to the support device by means other than an internal thread and an external thread. For example, the lens can be moved using a worm gear secured on the support device.
However, these adjustable intraocular lenses have a number of disadvantages. On the one hand, they are difficult to produce because they are made up of several parts which have to fit each other with very tight tolerances. In particular, movement mechanisms using worm gears and the like are elaborate, complicated and expensive to produce.
A further disadvantage is that the lens body is held in an annular support device. The latter is usually rigid, so that a large incision is needed for implantation. Moreover, the support device reaches close to the field of vision of the patient, with the result that undesired reflexes and disturbances can be caused by the thick support device.
Further adjustable intraocular lenses are known from US 5,203,788 and from US 5,288,293. In particular, US
5,288,293 discloses an intraocular lens in which the angle between the haptic arms and the lens body can be adjusted by an adjustment means, so that the lens body can be moved relative to the haptic arms in the direction of the optic axis. The adjustment means is a material formed at the juncture between the haptic and which connect to the implant lens. This material may be more readily subjectable to hydration, or in other cases to dehydration, such as the type of hydrogel or colagene. Thus, modifying the haptic-optic angle through laser energy treatment provides for an effect in the change of implant power. However, this kind of adjustment is not very precise and can be done only once. The adjustment is not reversible. Furthermore, the material placed at the boarder of the implant lens may cause undesired optical disturbance The object of the invention is to make available an adjustable intraocular lens which is easy and inexpensive to produce and which avoids the stated disadvantages.
Summary of the invention According to one advantageous aspect of the invention, the whole lens can be folded or rolled so that it can be inserted through a small incision in the cornea.
In a particularly advantageous embodiment, the lens body and the haptic arms are made in one piece in one casting procedure.
According to a further advantageous embodiment of the invention, the adjustment means is a commercially available screw which can be re-adjusted after implantation, either by means of a very small incision through the cornea and engagement of an instrument in the screw, or non-invasively using a magnetic screwdriver.
A further aspect of the invention provides for the lens being adjusted by means of an electric motor, for example a piezoelectric element.
An advantage of the invention lies in the provision of an adjustable intraocular lens having an adjustment mechanism which does not cause optical disturbance. ' A further advantage of the present invention lies in the fact that the adjustable intraocular lens can be adjusted repeatedly and reversibly.
In one aspect of the present invention, there is provided an adjustable intraocular lens comprising: a lens body; haptic arms, to fix the lens body in the eye; and an adjustment means to hold the lens body so as to be repeatedly and reversibly displaceable in the direction of the optic axis of the lens body; the haptic arms each being connected at one end to the lens body; and the haptic arms each being subdivided into two portions connected via the adjustment means, and the haptic arms comprising the end pieces;
the adjustment means having a cylindrical or disc-shaped end piece and a hallow-cylindrical or flange-like end piece which encloses the cylindrical or disc-shaped end piece, the end pieces together forming the adjustment means; wherein one end piece is held by a clamping effect in the other end piece, and their relative position to one another is mechanically displaceable.
In another aspect of the present invention, there is provided an adjustable intraocular lens comprising: a lens body; haptic arms to fix the lens body in the eye; and an adjustment means to hold the lens body so as to be repeatedly and reversibly displaceable in the direction of the optic axis of the lens body; a part of the adjustment means being designed in the form of a through-hole at the edge of the lens body, into which an end piece of a haptic arm engages axially; wherein the end piece is cylindrical or disc-shaped and is held in the through-hole by a clamping effect, the relative position to one another being mechanically displaceable.
In yet another aspect of the present invention, there is provided a method for production of an adjustable intraocular lens comprising: a lens body; haptic arms, to fix the lens body in the eye; and an adjustment means to hold the lens body so as to be repeatedly and reversibly displaceable in the direction of the -4a-optic axis of the lens body; the haptic arms each being connected at one end to the lens body; and the haptic arms each being subdivided into two portions connected via the adjustment means, and the haptic arms comprising the end pieces; the adjustment means having a cylindrical or disc-shaped end piece and a hallow-cylindrical or flange-like end piece which encloses the cylindrical or disc-shaped end piece, the end pieces together forming the adjustment means; wherein one end piece is held by a clamping effect in the other end piece, and their relative position to one another is mechanically displaceable, comprising the following stages: producing the lens body with the haptic arms attached thereto, forming a bifurcation in the haptic arms, forming a threaded hole in a bifurcation of the haptic arms.
Brief description of the drawings The invention is now explained with reference to the attached drawings, in which:
Fig. 1 shows a plan view of a known lens which is not adjustable;
Fig. 2 shows a side view of the lens in Fig. 1;
Fig. 3 shows an adjustable lens according to the prior art;
Fig. 4 shows a transverse section through a human eye from which the crystalline lens has been removed;
Fig. 5 shows a plan view of a lens according to the invention;
Fig. 6a shows a side view of a lens according to the invention, at maximum adjustment;
Fig. 6b shows a side view of a lens according to the invention, at minimum adjustment;
Fig. 7 shows a side view of a further lens according to the invention;
Fig. 8 shows a side view of a further lens according to the invention.
Fig. 9 shows a side view of a further lens according to the invention;
Fig_ 10 shows a side view of a further lens according to the invention;
Prior art In patients affected by grey cataract, for example, it is at present customary to remove the diseased and opaque crystalline lens and to replace it with an implant, a so-called intraocular lens (IOL).
An example of an intraocular lens of this type is shown in Figures 1 and 2. The lens consists of a lens body 1 and of two haptic arms 3 connected to the lens body 1. Fig. 2 shows a side view of the lens from Fig. 1.
The lens is preferably made of a soft or foldable material so that it can be folded or rolled along the broken line (A-A). For implantation, after the diseased crystalline lens has been removed, the intraocular lens is inserted into the eye by being folded together during the insertion along the broken line so that the incision in the cornea can be made as small as possible. The lens is unfolded within the eye and is secured in its position, usually in the capsule of the removed lens.
The lenses, which are usually made of a synthetic material such as polyurethane elastomer, silicone elastomer, hydrogel polymer or collagen, can be formed in one piece and are therefore economical to produce. As they can be rolled up or folded up, they can be inserted through a small slit, with the result that the eye rapidly heals after the operation.
However, a disadvantage of these lenses is that incorrect fitting can easily occur, with the result that, even after the operation, the patient requires a means for correcting vision, for example glasses or contact lenses, because the focus of the lens lies before or behind the retina.
To rectify this problem, an adjustable intraocular lens has been proposed in US 5,800,533 and in US 5,728,155. Such a lens is shown in Fig. 3. This prior art lens, which forms the preamble of Claim 1, consists of a cylindrical lens body 1 with an external thread 5, a support device 7 which is annular and has an internal thread 9 matching the external thread 5 of the lens body 1, and haptic arms 3 which are secured to the support device or are formed in one piece with the latter. As the lens body is screwed to a greater or lesser extent into the support device, the distance between the lens body and the retina, and thus the focus, is adjusted.
US 5,728,155 also shows that a flexible lens body can be fitted into the support device, so that it is possible subsequently to exchange the lens via a small incision made through the cornea. This publication additionally discloses that the lens body can also be moved relative to the support device by means other than an internal thread and an external thread. For example, the lens can be moved using a worm gear secured on the support device.
However, these adjustable intraocular lenses have a number of disadvantages. On the one hand, they are difficult to produce because they are made up of several parts which have to fit each other with very tight tolerances. In particular, movement mechanisms using worm gears and the like are elaborate, complicated and expensive to produce.
A further disadvantage is that the lens body is held in an annular support device. The latter is usually rigid, so that a large incision is needed for implantation. Moreover, the support device reaches close to the field of vision of the patient, with the result that undesired reflexes and disturbances can be caused by the thick support device.
Further adjustable intraocular lenses are known from US 5,203,788 and from US 5,288,293. In particular, US
5,288,293 discloses an intraocular lens in which the angle between the haptic arms and the lens body can be adjusted by an adjustment means, so that the lens body can be moved relative to the haptic arms in the direction of the optic axis. The adjustment means is a material formed at the juncture between the haptic and which connect to the implant lens. This material may be more readily subjectable to hydration, or in other cases to dehydration, such as the type of hydrogel or colagene. Thus, modifying the haptic-optic angle through laser energy treatment provides for an effect in the change of implant power. However, this kind of adjustment is not very precise and can be done only once. The adjustment is not reversible. Furthermore, the material placed at the boarder of the implant lens may cause undesired optical disturbance The object of the invention is to make available an adjustable intraocular lens which is easy and inexpensive to produce and which avoids the stated disadvantages.
Summary of the invention According to one advantageous aspect of the invention, the whole lens can be folded or rolled so that it can be inserted through a small incision in the cornea.
In a particularly advantageous embodiment, the lens body and the haptic arms are made in one piece in one casting procedure.
According to a further advantageous embodiment of the invention, the adjustment means is a commercially available screw which can be re-adjusted after implantation, either by means of a very small incision through the cornea and engagement of an instrument in the screw, or non-invasively using a magnetic screwdriver.
A further aspect of the invention provides for the lens being adjusted by means of an electric motor, for example a piezoelectric element.
An advantage of the invention lies in the provision of an adjustable intraocular lens having an adjustment mechanism which does not cause optical disturbance. ' A further advantage of the present invention lies in the fact that the adjustable intraocular lens can be adjusted repeatedly and reversibly.
In one aspect of the present invention, there is provided an adjustable intraocular lens comprising: a lens body; haptic arms, to fix the lens body in the eye; and an adjustment means to hold the lens body so as to be repeatedly and reversibly displaceable in the direction of the optic axis of the lens body; the haptic arms each being connected at one end to the lens body; and the haptic arms each being subdivided into two portions connected via the adjustment means, and the haptic arms comprising the end pieces;
the adjustment means having a cylindrical or disc-shaped end piece and a hallow-cylindrical or flange-like end piece which encloses the cylindrical or disc-shaped end piece, the end pieces together forming the adjustment means; wherein one end piece is held by a clamping effect in the other end piece, and their relative position to one another is mechanically displaceable.
In another aspect of the present invention, there is provided an adjustable intraocular lens comprising: a lens body; haptic arms to fix the lens body in the eye; and an adjustment means to hold the lens body so as to be repeatedly and reversibly displaceable in the direction of the optic axis of the lens body; a part of the adjustment means being designed in the form of a through-hole at the edge of the lens body, into which an end piece of a haptic arm engages axially; wherein the end piece is cylindrical or disc-shaped and is held in the through-hole by a clamping effect, the relative position to one another being mechanically displaceable.
In yet another aspect of the present invention, there is provided a method for production of an adjustable intraocular lens comprising: a lens body; haptic arms, to fix the lens body in the eye; and an adjustment means to hold the lens body so as to be repeatedly and reversibly displaceable in the direction of the -4a-optic axis of the lens body; the haptic arms each being connected at one end to the lens body; and the haptic arms each being subdivided into two portions connected via the adjustment means, and the haptic arms comprising the end pieces; the adjustment means having a cylindrical or disc-shaped end piece and a hallow-cylindrical or flange-like end piece which encloses the cylindrical or disc-shaped end piece, the end pieces together forming the adjustment means; wherein one end piece is held by a clamping effect in the other end piece, and their relative position to one another is mechanically displaceable, comprising the following stages: producing the lens body with the haptic arms attached thereto, forming a bifurcation in the haptic arms, forming a threaded hole in a bifurcation of the haptic arms.
Brief description of the drawings The invention is now explained with reference to the attached drawings, in which:
Fig. 1 shows a plan view of a known lens which is not adjustable;
Fig. 2 shows a side view of the lens in Fig. 1;
Fig. 3 shows an adjustable lens according to the prior art;
Fig. 4 shows a transverse section through a human eye from which the crystalline lens has been removed;
Fig. 5 shows a plan view of a lens according to the invention;
Fig. 6a shows a side view of a lens according to the invention, at maximum adjustment;
Fig. 6b shows a side view of a lens according to the invention, at minimum adjustment;
Fig. 7 shows a side view of a further lens according to the invention;
Fig. 8 shows a side view of a further lens according to the invention.
Fig. 9 shows a side view of a further lens according to the invention;
Fig_ 10 shows a side view of a further lens according to the invention;
Fig. 11 shows a side view of a further lens according to the invention;
Fig. 12 shows a side view of a further lens according to the invention;
Fig. 13 shows a side view of a further lens according to the invention;
Fig. 14 shows a view of a further adjustment means;
Fig. 15 shows a side view of a further lens according to the invention;
Fig. 16 shows a side view of a further lens according to the invention;
Fig. 17 shows a plan view of one of the fork ends from Fig. 16;
Fig. 18 shows a side view of a further lens according to the invention; and Fig. 19 shows a plan view of a further lens according to the invention.
Detailed description of the invention The human eye is shown in section in Fig. 4, the crystalline lens having been removed. Situated behind the cornea 11 consisting of transparent tissue is the anterior chamber 13 of the eye. This anterior chamber 13 is delimited by the iris 15 and the pupil 17. Adjoining it is the posterior chamber 19 which, for its part, is delimited on one side by the iris 15 and the pupil 17 and on the other side by the vitreous membrane 21 and the vitreous body 23. The intraocular lens is usually arranged in the posterior chamber, the haptic arms 3 bearing against the margin of the posterior chamber or against the capsule 22 and holding the lens in position.
Fig. 5 shows a plan view of a lens according to the invention. The lens comprises a lens body 1, which is adjoined by two haptic arms 3 lying opposite each other. The haptic arms 3 have adjustment means 25 for moving the lens body 1 relative to the haptic arms 3 in the direction of the optic axis 27 of the lens body 1 and for adjusting the extent of the movement.
Fig. 6a shows a side view of part of a lens according to the invention, one of the haptic arms 3 with the adjustment means 25 being shown in the maximum extended position, while Fig. 6b shows the same part of the lens with the haptic arm 3 and the adjustment means 25 in the maximum drawn-in position.
At its end 29 directed towards the lens body, the haptic arm 3 has a bifurcation with two fork ends 31, 33. The fork end 31 is connected to the lens b6dy 1. It is made flexible, at least at its connection points to the lens body 1 and to the other fork end 33, so that a relative movement of the two fork ends is possible. The whole haptic arm 3 is preferably made of a synthetic material having a certain elasticity.
Moreover, the other fork end 33 is preferably stiffer than the fork end 31. This can be realized by suitable choice of material or by giving the two fork ends suitable thicknesses. In the embodiment shown, the fork end 33 is many times thicker than the fork end 31.
At its end directed towards the lens, the fork end 33 is provided with a rounded edge, so that when the lens is fitted there is no projecting part on which the lens could become hooked with the iris or cornea.
The rear part of the haptic arms 3, from which the two fork ends 31, 33 extend, can be made of a relatively soft, elastic material. The use of a material with a "memory" effect, which returns to its original shape on heating after deformation, is also possible.
In this embodiment, the fork end 31 carries the adjustment means 25. The latter consists of a threaded hole 35 extending through the fork end 31 in the direction of the optic axis 27. An adjusting screw 37 is screwed into the threaded hole 35 in such a way that its front end bears on the other fork end 33 and is pressed against it by the spring force of the elastic fork elements 31, 33.
Fig. 12 shows a side view of a further lens according to the invention;
Fig. 13 shows a side view of a further lens according to the invention;
Fig. 14 shows a view of a further adjustment means;
Fig. 15 shows a side view of a further lens according to the invention;
Fig. 16 shows a side view of a further lens according to the invention;
Fig. 17 shows a plan view of one of the fork ends from Fig. 16;
Fig. 18 shows a side view of a further lens according to the invention; and Fig. 19 shows a plan view of a further lens according to the invention.
Detailed description of the invention The human eye is shown in section in Fig. 4, the crystalline lens having been removed. Situated behind the cornea 11 consisting of transparent tissue is the anterior chamber 13 of the eye. This anterior chamber 13 is delimited by the iris 15 and the pupil 17. Adjoining it is the posterior chamber 19 which, for its part, is delimited on one side by the iris 15 and the pupil 17 and on the other side by the vitreous membrane 21 and the vitreous body 23. The intraocular lens is usually arranged in the posterior chamber, the haptic arms 3 bearing against the margin of the posterior chamber or against the capsule 22 and holding the lens in position.
Fig. 5 shows a plan view of a lens according to the invention. The lens comprises a lens body 1, which is adjoined by two haptic arms 3 lying opposite each other. The haptic arms 3 have adjustment means 25 for moving the lens body 1 relative to the haptic arms 3 in the direction of the optic axis 27 of the lens body 1 and for adjusting the extent of the movement.
Fig. 6a shows a side view of part of a lens according to the invention, one of the haptic arms 3 with the adjustment means 25 being shown in the maximum extended position, while Fig. 6b shows the same part of the lens with the haptic arm 3 and the adjustment means 25 in the maximum drawn-in position.
At its end 29 directed towards the lens body, the haptic arm 3 has a bifurcation with two fork ends 31, 33. The fork end 31 is connected to the lens b6dy 1. It is made flexible, at least at its connection points to the lens body 1 and to the other fork end 33, so that a relative movement of the two fork ends is possible. The whole haptic arm 3 is preferably made of a synthetic material having a certain elasticity.
Moreover, the other fork end 33 is preferably stiffer than the fork end 31. This can be realized by suitable choice of material or by giving the two fork ends suitable thicknesses. In the embodiment shown, the fork end 33 is many times thicker than the fork end 31.
At its end directed towards the lens, the fork end 33 is provided with a rounded edge, so that when the lens is fitted there is no projecting part on which the lens could become hooked with the iris or cornea.
The rear part of the haptic arms 3, from which the two fork ends 31, 33 extend, can be made of a relatively soft, elastic material. The use of a material with a "memory" effect, which returns to its original shape on heating after deformation, is also possible.
In this embodiment, the fork end 31 carries the adjustment means 25. The latter consists of a threaded hole 35 extending through the fork end 31 in the direction of the optic axis 27. An adjusting screw 37 is screwed into the threaded hole 35 in such a way that its front end bears on the other fork end 33 and is pressed against it by the spring force of the elastic fork elements 31, 33.
As can be seen from Fig. 6a and Fig. 6b, the position of the lens body 1 relative to the fork end 33 changes as the adjusting screw 37 is screwed in and out. Accordingly, after inserting the adjustable intraocular lens, the ophthalmic surgeon is able to adjust the focus of the lens accurately to the retina of the patient.
To do this, the intraocular lens can first be fitted in the eye without the adjusting screw, that is to say with the fork ends 31, 33 bearing against each other. After the results of this operation have healed, the vision defect of the patient can be determined.
Then, in a minor intervention performed under local anaesthesia, the cornea can be opened directly above the threaded hole 35, and adjusting screws 37 of the required length can be screwed in. To do this, only a very small corneal incision is required, which lies outside the field of vision and rapidly heals.
Alternatively, the intraocular lens can be fitted together with the inserted adjusting screw 37, in which case the adjusting screw is preferably screwed in to about half way.
By selecting a screw of suitable length, a lens adjustment of up to 5 dioptres (3.25 mm) can be achieved without problem.
The lens itself can be produced in a casting procedure, after which the bifurcation into the fork ends 31, 33 is made by cutting through the haptic arms 3. A threaded hole 35 is subsequently formed in the bifurcation 31. Alternatively, the lens can be produced together with its haptic arms 3, the bifurcation and the threaded hole 35 all in one casting procedure.
The intraocular lens according to the invention is economical to produce, uncomplicated and easy to handle and it offers the surgeon a wide range of adjustment possibilities.
Fig. 7 shows a further embodiment of the invention. The embodiment shown in Fig. 7 differs from that in Figures 6a and 6b in the following respects.
To do this, the intraocular lens can first be fitted in the eye without the adjusting screw, that is to say with the fork ends 31, 33 bearing against each other. After the results of this operation have healed, the vision defect of the patient can be determined.
Then, in a minor intervention performed under local anaesthesia, the cornea can be opened directly above the threaded hole 35, and adjusting screws 37 of the required length can be screwed in. To do this, only a very small corneal incision is required, which lies outside the field of vision and rapidly heals.
Alternatively, the intraocular lens can be fitted together with the inserted adjusting screw 37, in which case the adjusting screw is preferably screwed in to about half way.
By selecting a screw of suitable length, a lens adjustment of up to 5 dioptres (3.25 mm) can be achieved without problem.
The lens itself can be produced in a casting procedure, after which the bifurcation into the fork ends 31, 33 is made by cutting through the haptic arms 3. A threaded hole 35 is subsequently formed in the bifurcation 31. Alternatively, the lens can be produced together with its haptic arms 3, the bifurcation and the threaded hole 35 all in one casting procedure.
The intraocular lens according to the invention is economical to produce, uncomplicated and easy to handle and it offers the surgeon a wide range of adjustment possibilities.
Fig. 7 shows a further embodiment of the invention. The embodiment shown in Fig. 7 differs from that in Figures 6a and 6b in the following respects.
The adjustment means in this embodiment consists of an unthreaded through-hole 43 in the fork end 31, an adjusting screw 37, and a blind threaded hole on the other fork end 33. The adjustment of the lens body 1 in this case is effected by an instrument engaging through the unthreaded through-hole 43 into the head of the adjusting screw 37, which bears from underneath on the fork end 31, that is to say in the space between, the two fork ends 31, 33. By turning the screw 37, the fork end 31 can be raised or lowered relative to the fork end 33. Since the fork end 33 of the haptic arm 3 is made substantially thicker than the fork end 31, adjustment is thus possible over a large range, without changing the screw and without projections protruding from the lens and possibly damaging the eye.
Besides the embodiments shown, there are other adjustment possibilities. For example, the screw in the embodiments in Figures 6a, 6b and 8 can be replaced by a piezoelectric element which forces the two fork ends 31, 33 away from each other. Alternatively, spacer elements, for example wedge-shaped spacer elements, can be pushed in between the two fork ends. It is also possible to position an elastic, fluid-filled cushion between the two fork ends and to deliver or aspirate fluid for purposes of adjustment.
The haptic arms 3 can also consist of two arm layers which are connected firmly to each other over a first section.
The soft lens body 1 can also have a solid thin outer ring which can preferably be folded via two hinges together with the lens. This outer ring can additionally carry two catch elements which, after implantation, hold the lens body in the unfolded position.
Fig. 8 shows the side view of a further lens according to the invention. In the lens shown, the haptic arms 3 are not bifurcated, and instead they have an adjustment means 25 in the form of a worm gear. The haptic arms 3 are divided in two. A first section 39 extends between the lens body 1 and the adjustment means 25. A second section 41 extends from the adjustment means 25 away from the lens. In this embodiment, the adjustment means 25 is preferably a worm gear, so that the position of the section 39 of the haptic arm 3 can be adjusted relative to the section 41 of the haptic arm 3.
This embodiment has the advantage that adjustment of the lens by 3.25 mm is possible without replacement of the screw. Since the worm gear is positioned at a distance from the lens via the section 39 of the haptic arm 3, it does not lie in the patient's field of vision and does not cause unwanted reflexes.
The worm gear can be designed such that it allows the lens body 1 together with the sections 39 of the haptic arms 3 to be replaced without the other sections 41 of the haptic arms 3 having to be replaced.
In this way, it is possible, for example in children, to take account of the changes in the eye over the course of time, without major surgery being needed.
Other different embodiments of the intraocular lens according to the invention are shown in Figures 9 to 19.
The adjustable intraocular lens in Fig. 9 has a wedge-shaped spacer element 51 between the fork ends 31, 33, which spacer element can be moved in order to change the lens position.
Further adjustable intraocular lenses are shown in Figures 10 and 11. Here, the adjusting screw 37, the threaded hole 35 and the through-hole 43 are inclined relative to the optic axis 27. In this way, the point of intervention on the cornea, for post-operative adjustment, moves outwards and away from the patient's field of vision.
In the lens according to Fig. 12, an eccentric disc is provided as spacer element 53.
Besides the embodiments shown, there are other adjustment possibilities. For example, the screw in the embodiments in Figures 6a, 6b and 8 can be replaced by a piezoelectric element which forces the two fork ends 31, 33 away from each other. Alternatively, spacer elements, for example wedge-shaped spacer elements, can be pushed in between the two fork ends. It is also possible to position an elastic, fluid-filled cushion between the two fork ends and to deliver or aspirate fluid for purposes of adjustment.
The haptic arms 3 can also consist of two arm layers which are connected firmly to each other over a first section.
The soft lens body 1 can also have a solid thin outer ring which can preferably be folded via two hinges together with the lens. This outer ring can additionally carry two catch elements which, after implantation, hold the lens body in the unfolded position.
Fig. 8 shows the side view of a further lens according to the invention. In the lens shown, the haptic arms 3 are not bifurcated, and instead they have an adjustment means 25 in the form of a worm gear. The haptic arms 3 are divided in two. A first section 39 extends between the lens body 1 and the adjustment means 25. A second section 41 extends from the adjustment means 25 away from the lens. In this embodiment, the adjustment means 25 is preferably a worm gear, so that the position of the section 39 of the haptic arm 3 can be adjusted relative to the section 41 of the haptic arm 3.
This embodiment has the advantage that adjustment of the lens by 3.25 mm is possible without replacement of the screw. Since the worm gear is positioned at a distance from the lens via the section 39 of the haptic arm 3, it does not lie in the patient's field of vision and does not cause unwanted reflexes.
The worm gear can be designed such that it allows the lens body 1 together with the sections 39 of the haptic arms 3 to be replaced without the other sections 41 of the haptic arms 3 having to be replaced.
In this way, it is possible, for example in children, to take account of the changes in the eye over the course of time, without major surgery being needed.
Other different embodiments of the intraocular lens according to the invention are shown in Figures 9 to 19.
The adjustable intraocular lens in Fig. 9 has a wedge-shaped spacer element 51 between the fork ends 31, 33, which spacer element can be moved in order to change the lens position.
Further adjustable intraocular lenses are shown in Figures 10 and 11. Here, the adjusting screw 37, the threaded hole 35 and the through-hole 43 are inclined relative to the optic axis 27. In this way, the point of intervention on the cornea, for post-operative adjustment, moves outwards and away from the patient's field of vision.
In the lens according to Fig. 12, an eccentric disc is provided as spacer element 53.
In the lens according to Fig. 13, the adjustment means is in the form of a clamp guide parallel to the optic axis 27.
In this preferred embodiment, one section 41 of the haptic arm, arranged with one end on the lens, has a cylindrical or disc-shaped end-piece 41' aligned with the optic axis 27 at the other end. The other section 39 of the haptic arm has, at one end, a hollow cylindrical or flange-like end-piece 39' which encloses the disc-shaped end-piece 41'. The section 41 of the haptic arm protrudes through a preferably continuous slot in the wall of the end-piece 39'.
The interior of the hollow cylindrical end-piece 39' and the outer contour of the disc-shaped end-piece 41' are matched to each other. The end-piece 41' can be held in the other end-piece 39' by a clamping effect, and their relative position can be mechanically adjusted.
The two end-pieces 39' and 41' together form the adjustment means. The two end-pieces 39' and 41' are preferably formed in such a way that they cannot twist relative to each other; for example, the hollow cylinder and the disc can each have oval shapes. Other forms are also possible, however, such as semicircles, polygons or "dogs' bones". In this description, the term "hollow cylinder" is therefore not to be understood as being restricted to circular cylinders.
The clamping principle can also be modified such that a relatively thin flange as one end-piece comprises a longer pin than the other end-piece.
The hollow cylindrical end-piece 39' and the section 41 of the haptic arm 3 can be made in one piece from metal, whereas the disc-shaped end-piece 41' together with the lens - preferably in one piece- is made of a plastic material.
It is also preferable for the section 39 and the end-piece 39' to be ensheathed in a biocompatible plastic.
In this preferred embodiment, one section 41 of the haptic arm, arranged with one end on the lens, has a cylindrical or disc-shaped end-piece 41' aligned with the optic axis 27 at the other end. The other section 39 of the haptic arm has, at one end, a hollow cylindrical or flange-like end-piece 39' which encloses the disc-shaped end-piece 41'. The section 41 of the haptic arm protrudes through a preferably continuous slot in the wall of the end-piece 39'.
The interior of the hollow cylindrical end-piece 39' and the outer contour of the disc-shaped end-piece 41' are matched to each other. The end-piece 41' can be held in the other end-piece 39' by a clamping effect, and their relative position can be mechanically adjusted.
The two end-pieces 39' and 41' together form the adjustment means. The two end-pieces 39' and 41' are preferably formed in such a way that they cannot twist relative to each other; for example, the hollow cylinder and the disc can each have oval shapes. Other forms are also possible, however, such as semicircles, polygons or "dogs' bones". In this description, the term "hollow cylinder" is therefore not to be understood as being restricted to circular cylinders.
The clamping principle can also be modified such that a relatively thin flange as one end-piece comprises a longer pin than the other end-piece.
The hollow cylindrical end-piece 39' and the section 41 of the haptic arm 3 can be made in one piece from metal, whereas the disc-shaped end-piece 41' together with the lens - preferably in one piece- is made of a plastic material.
It is also preferable for the section 39 and the end-piece 39' to be ensheathed in a biocompatible plastic.
The design of the hollow cylindrical end-piece 39' of metal with a continuous longitudinal slit in the outer wall has the advantage of an elastic or resilient adaptation of the end-piece 39' to the end-piece 41' received therein.
Alternatively, the hollow cylindrical end-piece can also be formed on the section 41 of the haptic arm, that is to say on the side towards the lens body. , In a presently preferred embodiment, shown in Fig. 19, a through-hole is made for this purpose in the edge of the lens body, parallel to the optic axis. A
longitudinal slit permits connection to the other section 39 of the haptic arm. In other words, in this embodiment the adjustment means is formed in the edge of the lens body, and not connected to the lens body via a section 41 of the haptic arm.
Fig. 14 shows a further possibility in which, after positioning, the lens can be secured by an arrest means 55, for example a screw.
In the adjustable intraocular lens in Fig. 15, the adjustment means 25 has a pin 47 which extends in the direction of the optic axis 27 and which is firmly connected to one of the two sections 39 of the haptic arm 3, while the other section 41 is mounted so that it can move along the pin 47.
Horseshoe-shaped spacers 53 can be pushed firmly onto the pin 47 between the two sections 39, 41 and fix the distance between the sections 39, 41.
Alternatively, as has been mentioned, the sections 39, 41 can also be held in their relative position by a clamping effect.
In the intraocular lens according to the invention in Fig. 16, at least one of the fork ends 31, 33 has, on the side facing towards the other fork end 33, 31, a toothing 49, similar to a toothed rack, where a spacer element 51 can be moved along the fork ends 31, 33 and can be fixed in position by engagement in the toothing. Fig. 17 shows a plan view of the outwardly directed fork end 31. The latter is preferably provided with a cental longitudinal slit through which access to the spacer element is possible.
Further adjustable intraocular lenses are shown in Figures 10 and 11. Here, the adjusting screw 37, the threaded hole 35 and the through-hole 43 are inclined relative to the optic axis 27. In this way, the point of intervention on the cornea, for post-operative adjustment, moves outwards and away from the patient's field of vision.
Fig. 18 shows a further lens according to the invention. This differs from the lens in Figures 6a and 6b in that an extension element is provided in the fork end 31 between the threaded hole 35 and the bifurcation point, in order to better take up the change in length of the fork end 31. Such an extension element can also be provided at suitable points in the other embodiments of the invention. In Fig. 18, the extension element is an accordion-shaped section in the fork end 31.
Although a number of preferred embodiments have been set out in the above description, the invention is not limited thereto. Changes and modifications within the scope of the skilled person are also encompassed.
Alternatively, the hollow cylindrical end-piece can also be formed on the section 41 of the haptic arm, that is to say on the side towards the lens body. , In a presently preferred embodiment, shown in Fig. 19, a through-hole is made for this purpose in the edge of the lens body, parallel to the optic axis. A
longitudinal slit permits connection to the other section 39 of the haptic arm. In other words, in this embodiment the adjustment means is formed in the edge of the lens body, and not connected to the lens body via a section 41 of the haptic arm.
Fig. 14 shows a further possibility in which, after positioning, the lens can be secured by an arrest means 55, for example a screw.
In the adjustable intraocular lens in Fig. 15, the adjustment means 25 has a pin 47 which extends in the direction of the optic axis 27 and which is firmly connected to one of the two sections 39 of the haptic arm 3, while the other section 41 is mounted so that it can move along the pin 47.
Horseshoe-shaped spacers 53 can be pushed firmly onto the pin 47 between the two sections 39, 41 and fix the distance between the sections 39, 41.
Alternatively, as has been mentioned, the sections 39, 41 can also be held in their relative position by a clamping effect.
In the intraocular lens according to the invention in Fig. 16, at least one of the fork ends 31, 33 has, on the side facing towards the other fork end 33, 31, a toothing 49, similar to a toothed rack, where a spacer element 51 can be moved along the fork ends 31, 33 and can be fixed in position by engagement in the toothing. Fig. 17 shows a plan view of the outwardly directed fork end 31. The latter is preferably provided with a cental longitudinal slit through which access to the spacer element is possible.
Further adjustable intraocular lenses are shown in Figures 10 and 11. Here, the adjusting screw 37, the threaded hole 35 and the through-hole 43 are inclined relative to the optic axis 27. In this way, the point of intervention on the cornea, for post-operative adjustment, moves outwards and away from the patient's field of vision.
Fig. 18 shows a further lens according to the invention. This differs from the lens in Figures 6a and 6b in that an extension element is provided in the fork end 31 between the threaded hole 35 and the bifurcation point, in order to better take up the change in length of the fork end 31. Such an extension element can also be provided at suitable points in the other embodiments of the invention. In Fig. 18, the extension element is an accordion-shaped section in the fork end 31.
Although a number of preferred embodiments have been set out in the above description, the invention is not limited thereto. Changes and modifications within the scope of the skilled person are also encompassed.
Claims (13)
1. An adjustable intraocular lens comprising:
a lens body;
haptic arms, to fix the lens body in the eye; and an adjustment means to hold the lens body so as to be repeatedly and reversibly displaceable in the direction of the optic axis of the lens body;
the haptic arms each being connected at one end to the lens body; and the haptic arms each being subdivided into two portions connected via the adjustment means, and the haptic arms comprising the end pieces;
the adjustment means having a cylindrical or disc-shaped end piece and a hallow-cylindrical or flange-like end piece which encloses the cylindrical or disc-shaped end piece, the end pieces together forming the adjustment means;
wherein one end piece is held by a clamping effect in the other end piece, and their relative position to one another is mechanically displaceable.
a lens body;
haptic arms, to fix the lens body in the eye; and an adjustment means to hold the lens body so as to be repeatedly and reversibly displaceable in the direction of the optic axis of the lens body;
the haptic arms each being connected at one end to the lens body; and the haptic arms each being subdivided into two portions connected via the adjustment means, and the haptic arms comprising the end pieces;
the adjustment means having a cylindrical or disc-shaped end piece and a hallow-cylindrical or flange-like end piece which encloses the cylindrical or disc-shaped end piece, the end pieces together forming the adjustment means;
wherein one end piece is held by a clamping effect in the other end piece, and their relative position to one another is mechanically displaceable.
2. An adjustable intraocular lens according to claim 1, wherein the lens body is foldable or rollable.
3. An adjustable intraocular lens according to claim 1, wherein the adjustment means has a piezoelectric element which effects the displacement of the adjustment means.
4. An adjustable intraocular lens according to claim 1, wherein at least one of the haptic arms has an expansion element.
5. An adjustable intraocular lens comprising:
a lens body;
haptic arms to fix the lens body in the eye; and an adjustment means to hold the lens body so as to be repeatedly and reversibly displaceable in the direction of the optic axis of the lens body;
a part of the adjustment means being designed in the form of a through-hole at the edge of the lens body, into which an end piece of a haptic arm engages axially;
wherein the end piece is cylindrical or disc-shaped and is held in the through-hole by a clamping effect, the relative position to one another being mechanically displaceable.
a lens body;
haptic arms to fix the lens body in the eye; and an adjustment means to hold the lens body so as to be repeatedly and reversibly displaceable in the direction of the optic axis of the lens body;
a part of the adjustment means being designed in the form of a through-hole at the edge of the lens body, into which an end piece of a haptic arm engages axially;
wherein the end piece is cylindrical or disc-shaped and is held in the through-hole by a clamping effect, the relative position to one another being mechanically displaceable.
6. Adjustable introcular lens according to claim 1, wherein the adjustment means is designed in the form of an adjustable step in the haptic arm.
7. Adjustable intraocular lens with: a lens body, haptic arms for fixing the lens body in the eye, and an adjustment means for moving the lens body repeatedly and reversibly in the direction of the optic axis of the lens body, wherein the haptic arms are each connected to the lens body via one end;
wherein the haptic arms have, at their end, two deformable fork ends perpendicular to the optic axis, the lens body is connected to only one of the two fork ends, and the adjustment means adjusts the distance between the fork ends.
wherein the haptic arms have, at their end, two deformable fork ends perpendicular to the optic axis, the lens body is connected to only one of the two fork ends, and the adjustment means adjusts the distance between the fork ends.
8. Adjustable intraocular lens according to claim 7, wherein the adjustment means comprises a threaded hole running in the direction of the optic axis through one of the two fork ends, and an adjusting screw which can be screwed into the threaded hole in such a way that the adjusting screw bears with one of its ends against the second fork end.
9. Adjustable intraocular lens according to claim 1, wherein the adjustment means has a pin which extends in the direction of the optic axis and which is firmly connected to one of the two portions of the haptic arms, while the other portion is mounted so as to move along the pin.
10. Adjustable intraocular lens according to claim 9, wherein the adjustment means additionally has horseshoe-shaped spacers which can be pushed tightly onto the pin between the two portions and which fix the distance between the portions.
11. Method for production of an adjustable intraocular lens comprising:
a lens body;
haptic arms, to fix the lens body in the eye; and an adjustment means to hold the lens body so as to be repeatedly and reversibly displaceable in the direction of the optic axis of the lens body;
the haptic arms each being connected at one end to the lens body; and the haptic arms each being subdivided into two portions connected via the adjustment means, and the haptic arms comprising the end pieces;
the adjustment means having a cylindrical or disc-shaped end piece and a hallow-cylindrical or flange-like end piece which encloses the cylindrical or disc-shaped end piece, the end pieces together forming the adjustment means;
wherein one end piece is held by a clamping effect in the other end piece, and their relative position to one another is mechanically displaceable, comprising the following stages:
producing the lens body with the haptic arms attached thereto, forming a bifurcation in the haptic arms, and forming a threaded hole in a bifurcation of the haptic arms.
a lens body;
haptic arms, to fix the lens body in the eye; and an adjustment means to hold the lens body so as to be repeatedly and reversibly displaceable in the direction of the optic axis of the lens body;
the haptic arms each being connected at one end to the lens body; and the haptic arms each being subdivided into two portions connected via the adjustment means, and the haptic arms comprising the end pieces;
the adjustment means having a cylindrical or disc-shaped end piece and a hallow-cylindrical or flange-like end piece which encloses the cylindrical or disc-shaped end piece, the end pieces together forming the adjustment means;
wherein one end piece is held by a clamping effect in the other end piece, and their relative position to one another is mechanically displaceable, comprising the following stages:
producing the lens body with the haptic arms attached thereto, forming a bifurcation in the haptic arms, and forming a threaded hole in a bifurcation of the haptic arms.
12. Method according to claim 11, in which the haptic arms and the lens body are cast in one casting procedure.
13. Method according to claim 11, in which the bifurcations and the internal thread are formed simultaneously in the casting procedure.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE19936666A DE19936666C2 (en) | 1999-08-04 | 1999-08-04 | Adjustable intraocular lens and method of making it |
| DE19936666.7 | 1999-08-04 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2315338A1 CA2315338A1 (en) | 2001-02-04 |
| CA2315338C true CA2315338C (en) | 2008-01-15 |
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| CA002315338A Expired - Lifetime CA2315338C (en) | 1999-08-04 | 2000-08-03 | Adjustable intraocular lens and method for its production |
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| US (1) | US6443984B1 (en) |
| EP (1) | EP1074228B1 (en) |
| JP (1) | JP4190708B2 (en) |
| AT (1) | ATE324086T1 (en) |
| CA (1) | CA2315338C (en) |
| DE (2) | DE19936666C2 (en) |
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| DE10105080B4 (en) * | 2001-02-05 | 2007-01-18 | Marianne Jahn | Adjustable intraocular lens and associated adjustment device |
| IL145015A0 (en) | 2001-08-21 | 2002-06-30 | Nun Yehoshua Ben | Accommodating lens |
| US6533813B1 (en) * | 2001-09-07 | 2003-03-18 | Chwen Yih Lin | Intraocular lens that may accommodate automatically |
| DE10155345C2 (en) * | 2001-11-10 | 2003-12-11 | Fraunhofer Ges Forschung | Holder for an artificial intraocular lens (IOL) |
| WO2003057081A2 (en) * | 2001-12-21 | 2003-07-17 | Bausch & Lomb Incorporated | In-vivo adjustable intraocular lens |
| US20030171809A1 (en) * | 2002-03-05 | 2003-09-11 | Phillips Andrew F. | Axial-displacement accommodating intraocular lens |
| IL161706A0 (en) | 2004-04-29 | 2004-09-27 | Nulens Ltd | Intraocular lens fixation device |
| CA2601351A1 (en) | 2005-03-30 | 2006-10-05 | Nulens Ltd | Accommodating intraocular lens (aiol) assemblies, and discrete components therfor |
| USD702346S1 (en) | 2007-03-05 | 2014-04-08 | Nulens Ltd. | Haptic end plate for use in an intraocular assembly |
| US8273123B2 (en) * | 2007-03-05 | 2012-09-25 | Nulens Ltd. | Unitary accommodating intraocular lenses (AIOLs) and discrete base members for use therewith |
| ES2377456T3 (en) | 2008-07-24 | 2012-03-27 | Nulens Ltd | Accommodative intraocular lens capsules (IOLs) |
| MX2011009196A (en) * | 2009-03-04 | 2011-11-18 | Aaren Scientific Inc | System for forming and modifying lenses and lenses formed thereby. |
| US8646916B2 (en) | 2009-03-04 | 2014-02-11 | Perfect Ip, Llc | System for characterizing a cornea and obtaining an opthalmic lens |
| US8292952B2 (en) | 2009-03-04 | 2012-10-23 | Aaren Scientific Inc. | System for forming and modifying lenses and lenses formed thereby |
| EP2424467B1 (en) * | 2009-04-30 | 2014-04-23 | Promacon Italia Oftalmologia S.R.L. | Intraocular lens with system of laser adjustable haptics |
| US9220590B2 (en) * | 2010-06-10 | 2015-12-29 | Z Lens, Llc | Accommodative intraocular lens and method of improving accommodation |
| US8500806B1 (en) | 2012-01-31 | 2013-08-06 | Andrew F. Phillips | Accommodating intraocular lens |
| US9381081B2 (en) | 2012-03-12 | 2016-07-05 | Doci Innovations GmbH (Claus Simandi) | Intraocular lens having helical haptics of shape memory |
| US9364318B2 (en) | 2012-05-10 | 2016-06-14 | Z Lens, Llc | Accommodative-disaccommodative intraocular lens |
| US8998984B2 (en) | 2013-01-14 | 2015-04-07 | Andrew F. Phillips | Adjustable toric intraocular lens |
| JP2016535652A (en) * | 2013-11-04 | 2016-11-17 | ビジョンケア オフサルミック テクノロジーズ，インコーポレイティド | Method and apparatus for making an intraocular lens and inserting it into a patient's eyeball |
| US10201415B2 (en) | 2013-11-04 | 2019-02-12 | Visioncare, Inc. | Method and apparatus for preparation and insertion of an intraocular lens into the eye of a patient |
| US9333072B2 (en) * | 2014-04-29 | 2016-05-10 | Chukyo Medical Co., Inc. | Intraocular lens |
| JP6218681B2 (en) * | 2014-06-17 | 2017-10-25 | オリンパス株式会社 | How to set up a medical system |
| IL245775A0 (en) | 2016-05-22 | 2016-08-31 | Joshua Ben Nun | Hybrid accommodating intraocular lens |
| JP7074960B2 (en) | 2016-08-24 | 2022-05-25 | カール ツァイス メディテック アーゲー | Dual Mode Adjustable-Non-Adjustable Intraocular Lens |
| CN107694022B (en) * | 2017-11-10 | 2023-11-28 | 芜湖天人智能机械有限公司 | Length adjuster for training instrument component |
| GB2578639A (en) | 2018-11-02 | 2020-05-20 | Rayner Intraocular Lenses Ltd | Hybrid accommodating intraocular lens assemblages including discrete lens unit with segmented lens haptics |
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1999
- 1999-08-04 DE DE19936666A patent/DE19936666C2/en not_active Expired - Lifetime
-
2000
- 2000-08-01 AT AT00116621T patent/ATE324086T1/en active
- 2000-08-01 JP JP2000233507A patent/JP4190708B2/en not_active Expired - Lifetime
- 2000-08-01 EP EP00116621A patent/EP1074228B1/en not_active Expired - Lifetime
- 2000-08-01 DE DE50012635T patent/DE50012635D1/en not_active Expired - Lifetime
- 2000-08-03 US US09/631,727 patent/US6443984B1/en not_active Expired - Lifetime
- 2000-08-03 CA CA002315338A patent/CA2315338C/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| EP1074228A1 (en) | 2001-02-07 |
| JP4190708B2 (en) | 2008-12-03 |
| US6443984B1 (en) | 2002-09-03 |
| ATE324086T1 (en) | 2006-05-15 |
| DE50012635D1 (en) | 2006-06-01 |
| EP1074228B1 (en) | 2006-04-26 |
| DE19936666C2 (en) | 2002-05-23 |
| CA2315338A1 (en) | 2001-02-04 |
| JP2001087287A (en) | 2001-04-03 |
| DE19936666A1 (en) | 2001-03-15 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKEX | Expiry |
Effective date: 20200803 |