Intraocular lens

Abstract

The present invention relates to an intraocular lens comprising: an optical body (3); a loop element (4) mounted on the optical body (3) and having a loop curvature, and having a plurality of grooves (21) on the side of the loop element (4) facing the optical body (3); a first actuator (8) configured to reversibly change the loop curvature of the loop element (4) by means of changing the characteristics of the first actuator (8), such that the loop element (4) moves away from the optical body (3) from its rest position; and a support arm (5). Mounted on the optical body (3), and the longitudinal end (22) of the support arm away from the optical body (3) is configured to be disposed in one of the grooves (21) when the loop element (4) is in the rest position of the loop element (4); and a second actuator (9) configured to reversibly change the support arm curvature of the support arm (5) by means of changing the characteristics of the second actuator (9), so that the longitudinal end (22) of the support arm to be disposed in the groove (21) can be adjusted by means of the characteristics of the second actuator (9).

Description

[0001] This invention relates to an artificial lens.

[0002] In cataract treatment, a corneal incision is routinely made, large enough to allow a cannula to be inserted into the eye. After the corneal incision, the eye's lens is broken up using phacoemulsification and then aspirated from the capsular bag. An intraocular lens (IOL) is then inserted into the capsular bag using an injector. The IOL comprises an optic and a loop element, which holds the optic within the capsular bag.

[0003] The function of the loop element is to position the optical body as close as possible to the center of the eye to generate the highest quality image on the retina. Furthermore, the optical body should be fixed within the capsular bag with maximum positional stability. The loop element also prevents the optical body from rotating about its optical axis. This is particularly important when the optical body is a toric optic used to correct corneal curvature, as an incorrectly oriented toric optic in the capsular bag can lead to image deviation on the retina.

[0004] Once an intraocular lens (IOL) is inserted into the capsular bag, it may be positioned incorrectly within the bag. This could be caused, for example, by uneven fibrosis. If the IOL is positioned incorrectly within the capsular bag, it may be necessary to correct its position during surgical intervention or even replace the IOL. Remedial measures can be provided by using an IOL with a correctable position after insertion.

[0005] Therefore, the problem solved by the present invention is to provide an artificial lens that has an orthostatic position after being inserted into the capsule of the eye.

[0006] The intraocular lens of the present invention comprises: an optical body; a loop element mounted on the optical body and having a loop curvature, and having a plurality of grooves on the side of the loop element facing the optical body; a first actuator configured to reversibly change the loop curvature of the loop element by means of changing the characteristics of the first actuator, such that the loop element moves away from the optical body from a rest position of the loop element; a support arm mounted on the optical body, and the longitudinal end of the support arm away from the optical body is configured to be disposed in one of the grooves when the loop element is in the rest position of the loop element; and a second actuator configured to reversibly change the support arm curvature of the support arm by means of changing the characteristics of the second actuator, such that the groove to which the longitudinal end of the support arm is to be disposed can be adjusted by means of the characteristics of the second actuator.

[0007] When the intraocular lens is inserted into the eye's capsular bag and the loop element is in its rest position, the longitudinal end of the support arm is positioned in the original groove among these recesses. The characteristics of the first actuator can then be altered by irradiating it with electromagnetic radiation, for example, by means of a laser. As a result, the loop element moves away from the optical body from its rest position, and the longitudinal end of the support arm leaves the original groove. Then, a second actuator can be irradiated with electromagnetic radiation, for example, by means of a laser. In this way, the characteristics of the second actuator can be altered, which changes the curvature of the support arm. Depending on the significance of the change in the characteristics of the second actuator, the groove in which the longitudinal end of the support arm is positioned can then be selected when the first actuator moves backward toward the initial position to a new rest position. It is conceivable that the longitudinal end of the support arm is positioned in a groove other than the original groove among these recesses. By selecting which groove the longitudinal end of the support arm is now positioned in, the loop element presents a different position relative to the optical body. In this way, the position of the optical body within the capsular bag can be changed. Since all that is needed for this purpose is to irradiate the first and second actuators with electromagnetic radiation, it is advantageously unnecessary to introduce surgical instruments into the capsule through the cornea of ​​the eye.

[0008] For example, the characteristics of a first actuator can be its temperature and / or its phase state. Similarly, the characteristics of a second actuator can be its temperature and / or its phase state. A phase state can be understood as a spatial region with uniform material properties. For example, a change in phase state should be understood as a transition from solid to liquid or from liquid to solid, or from liquid to gas or from gas to liquid. Chemical transformations (e.g., from monomer to dimer or from dimer to monomer) also constitute a change in phase state.

[0009] Preferably, the first actuator is characterized by a temperature of the first actuator and the first actuator includes a bimetallic component extending within the loop element, and / or wherein the second actuator is characterized by a temperature of the second actuator and the second actuator includes a bimetallic component extending within the support arm. For example, the bimetallic component can be formed, for example, of stainless steel and zinc. The coefficient of thermal expansion of stainless steel is 12 × 10⁻⁶. -6 / K, and the coefficient of thermal expansion of zinc is 30*10 -6 / K. These coefficients of thermal expansion are significantly different from each other, which allows for long-distance movement of loop elements and / or support arms using stainless steel and zinc, even with small temperature changes.

[0010] When the temperature of the first actuator is below its threshold temperature, the loop element is preferably in its stationary position, and the loop element is configured to move away from the optical body when the first actuator is heated to a temperature above its threshold temperature. The threshold temperature of the first actuator can be selected such that it is just above body temperature, for example, above 40°C. More specifically, the threshold temperature of the second actuator can be from 40°C to 50°C. As a result, when the loop element is cooled to body temperature by heat conduction, the loop element automatically moves backward toward its stationary position.

[0011] The first actuator preferably has a thickened portion of the first actuator, which is thermally bonded to the bimetallic conductor of the first actuator, and / or the second actuator preferably has a thickened portion of the second actuator, which is thermally bonded to the bimetallic conductor of the second actuator. Advantageously, the laser is simply focused on and irradiated by the thickened portion. The thickened portions of the first actuator and / or the second actuator are more preferably located in the region of the optic. This region is typically not located behind the iris of the eye, but in the center of the capsule, and is therefore easily accessible by electromagnetic radiation. Alternatively, the thickened portions of the first actuator and / or the second actuator are preferably located in the region surrounding the optic. This region can be located close to the optic. More preferably, the thickened portions of the first actuator and / or the second actuator are located in the region adjacent to the optic. These alternative arrangements allow the thickened portions to be positioned behind the iris of the eye, and thus outside the patient's field of vision. The characteristic changes or activation of the first actuator and / or the second actuator can be achieved by means of electromagnetic radiation. Preferably, this is achieved after prior drug-induced pupil dilation.

[0012] Preferably, the first actuator includes a reservoir for the first actuator and a conduit for the first actuator extending within a loop element, wherein the substance of the first actuator is disposed in the reservoir and the conduit, wherein the reservoir and the conduit are connected to each other by fluid conduction, and the characteristics of the first actuator are the temperature and / or phase state of the substance. Preferably, the second actuator includes a reservoir for the second actuator and a conduit for the second actuator extending within a support arm, wherein the substance of the second actuator is disposed in the reservoir and the conduit, wherein the reservoir and the conduit are connected to each other by fluid conduction, and the characteristics of the second actuator are the temperature and / or phase state of the substance. Changes in the temperature and / or phase state of the substance alter the pressure within the reservoir and the conduit. Pressure changes can reversibly alter the curvature of the loop element or the curvature of the support arm. The presence of a reservoir results in a more significant pressure increase compared to not having a reservoir. Furthermore, lasers are particularly easy to focus on the reservoir, and thus can irradiate large amounts of material. The pressure changes are especially large when the reservoir and conduits are completely filled with material.

[0013] The substance is preferably a gas and / or a liquid. Liquid and / or gaseous substances are particularly suitable when the characteristics of the first actuator and / or the second actuator are the temperature of the substance, because the flow of the substance from the memory into the conduit (or vice versa) can effectively change the pressure in the conduit.

[0014] The substance preferably has a photosynthetic system comprising a certain amount of monomers and / or a certain amount of dimers, wherein the two monomers are configured to undergo photochemical addition, especially photocycloaddition, especially [2+2] photocycloaddition, and thus form a dimer, and the dimer is configured to undergo photodissociation, and thus form two monomers. Such reactions are known to those skilled in the art (e.g., see Jonathan Clayden, Nick Geeves, and Stuart Warren, *Organic Chemistry*, Oxford University Press, 2006). For example, a photosynthetic system for this purpose may comprise coumarins, coumarin derivatives, cinnamon esters (especially methyl cinnamate), cinnamon ester derivatives or arbutin derivatives, and / or dimers of the above compounds. An example of photochemical addition and photodissociation is depicted for coumarins or coumarin derivatives in the reaction equation (1) below, wherein the dimer is depicted to the right of the reaction arrow and the monomer is depicted to the left of the reaction arrow:

[0015]

[0016] For example, R can be -H, -NR'2, -NH2, -NHCOR', -OH, or -OR', where when R = -H, the substance is coumarin. R' can be an aliphatic or aromatic group or an acrylate. Irradiation with wavelength λ2 causes the dimer to form; irradiation with wavelength λ1 causes the dimer to dissociate into monomers. The dimer has a higher density than the monomer. Therefore, irradiation with wavelength λ2 reduces the pressure in the conduit; irradiation with wavelength λ1 increases the pressure in the conduit.

[0017] Another example of photochemical addition and photodissociation is described for methyl cinnamate in reaction equation (2) below, where the dimer is depicted to the right of the reaction arrow and the monomer is depicted to the left of the reaction arrow:

[0018]

[0019] Irradiation with wavelength λ2 causes dimer formation; irradiation with wavelength λ1 causes the dimer to dissociate into monomers. The dimer has a higher density than the monomers. Therefore, irradiation with wavelength λ2 reduces the pressure in the catheter; irradiation with wavelength λ1 increases the pressure in the catheter.

[0020] Another example of photochemical addition and photodissociation for piraceae derivatives is described in reaction equation (3) below, where the dimer is depicted to the right of the reaction arrow and the monomer is depicted to the left of the reaction arrow:

[0021]

[0022] The dimer exists in two isomers. Irradiation with wavelength λ2 causes the dimer to form; irradiation with wavelength λ1 causes the dimer to dissociate into monomers. The dimer has a higher density than the monomers. Therefore, irradiation with wavelength λ2 reduces the pressure in the catheter; irradiation with wavelength λ1 increases the pressure in the catheter.

[0023] If wavelengths λ1 and / or λ2 are in the ultraviolet range, it is conceivable to irradiate the first actuator and / or the second actuator with short-duration light pulses of wavelengths λ1 / n and / or λ2 / n so that multiphoton absorption of n photons can occur.

[0024] The intraocular lens preferably includes a bandpass filter disposed around the material and configured to allow a first wavelength range and a second wavelength range to pass through the photosynthetic system, wherein irradiation of the photosynthetic system within the first wavelength range causes the dimer to dissociate and irradiation within the second wavelength range causes the dimer to form. In this way, unwanted phase transitions of the material due to sunlight entering the eye can be prevented. For example, the material can be mixed with the bandpass filter, or the bandpass filter can be disposed around the material. Particularly preferably, the first wavelength range has a wavelength λ1, and the second wavelength range has a wavelength λ2.

[0025] Preferably, the reservoir of the first actuator is located in the region of the optics and / or the reservoir of the second actuator is located in the region of the optics. This region is typically not located behind the iris of the eye, but in the center of the capsule, and therefore can be easily reached by electromagnetic radiation. Alternatively, preferably, the reservoir of the first actuator and / or the reservoir of the second actuator is located in the region surrounding the optics. This region can be located close to the optics. More preferably, the reservoir of the first actuator and / or the reservoir of the second actuator is located in the region adjacent to the optics. These alternative arrangements allow the reservoir to be positioned behind the iris of the eye and therefore outside the patient's field of vision. The characteristic change or activation of the first actuator and / or the second actuator can be achieved by means of electromagnetic radiation. Preferably, this is achieved after previous drug-induced pupillary dilation.

[0026] Preferably, these grooves are arranged side by side in the direction from the first longitudinal end of the loop element to the second longitudinal end of the loop element. Preferably, the first longitudinal end of the loop element is disposed on the optical body, while the second longitudinal end of the loop element is disposed away from the optical body, or the first longitudinal end of the loop element is disposed away from the optical body, while the second longitudinal end of the loop element is disposed on the optical body.

[0027] Preferably, depending on which groove the longitudinal end of the support arm is located in, either the first longitudinal end of the loop element or the second longitudinal end of the loop element, whichever is located furthest from the optical body, is located at a different distance from the optical body.

[0028] Preferably, the characteristic of the second actuator is its temperature, wherein the longitudinal end of the support arm is configured such that when the temperature of the second actuator is below its threshold temperature, it is positioned in one of the grooves in the region of the first longitudinal end of the loop element, and when the second actuator is heated to a temperature above its threshold temperature, it moves toward the second longitudinal end. It is conceivable that when the temperature is below the threshold temperature of the second actuator, the longitudinal end of the support arm is positioned in the groove closest to the first longitudinal end of the loop element. The threshold temperature of the second actuator can be selected such that it is above body temperature, for example, above 40°C. More specifically, the threshold temperature of the second actuator can be from 40°C to 50°C. By means of a threshold temperature higher than body temperature and the longitudinal end of the loop element positioned in the groove closest to the first longitudinal end of the loop element when the threshold temperature is below the threshold temperature, the following effect can be achieved: when the loop element is spaced apart from its first position, heating the actuator by electromagnetic radiation can bring the longitudinal end of the support arm into each groove.

[0029] Preferably, a locking tooth is provided between every two adjacent grooves. The locking tooth has a first tooth surface arranged facing the first longitudinal end of the loop element and a second tooth surface arranged facing the second longitudinal end of the loop element. The first and second tooth surfaces are shaped such that, when the loop element is in its first position, the longitudinal end of the support arm can slide towards the second longitudinal end of the loop element, while sliding towards the first longitudinal end of the loop element is prevented. In this way, it is possible that when the second actuator is cooled, the longitudinal end of the support arm does not move towards the first longitudinal end. However, simultaneously, when the second actuator is heated, movement of the longitudinal end of the support arm towards the second longitudinal end of the loop element is facilitated. To achieve this, for example, the first tooth surface can protrude more steeply from the surface of the loop element than the second tooth surface, as is the case, for example, in the case of a serrated profile.

[0030] Preferably, a locking tooth is provided between every two adjacent grooves.

[0031] Preferably, the loop element comprises a polymer in contact with the first actuator, and / or wherein the support arm comprises a polymer supporting the arm in contact with the second actuator. The polymer arrangement allows the loop element to easily change its loop curvature, and the support arm to easily change its support arm curvature. If a reservoir and conduit are provided, the polymer preferably surrounds, in particular, completely surrounds, the reservoir and conduit. If a bimetallic structure is provided, the polymer preferably encapsulates, in particular, completely encapsulates, the bimetallic structure. In this way, non-biocompatible metals can also be used in the bimetallic structure.

[0032] The intraocular lens preferably has two loop elements, a first actuator and a support arm for each loop element, and a second actuator for each support arm. As a result, the position of the optical body can be changed from two different directions.

[0033] The invention has been described in detail with reference to the accompanying schematic diagrams.

[0034] Figure 1 A first embodiment of the intraocular lens of the present invention is shown.

[0035] Figure 2 Details of a second embodiment of the intraocular lens of the present invention are shown.

[0036] Figure 3 Details of a third embodiment of the intraocular lens of the present invention are shown.

[0037] Figure 4 Details of the first embodiment are shown.

[0038] Figure 5 The absorption spectrum of the bandpass filter is shown.

[0039] from Figure 1 As can be seen, the intraocular lens 1 has an optical body 3, a loop element 4 mounted on the optical body 3, a first actuator 8, a support arm 5 mounted on the optical body 3, and a second actuator 9. The loop element 4 has a loop curvature and a plurality of grooves 21 on the side of the loop element 4 facing the optical body 3. The first actuator 8 is configured to reversibly change the loop curvature of the loop element 4 by changing the characteristics of the first actuator 8, so that the loop element 4 moves away from the optical body 3 from its rest position. The longitudinal end 22 of the support arm away from the optical body 3 is configured to be disposed in one of these grooves 21 when the loop element 4 is in its rest position, and the second actuator 9 is configured to reversibly change the support arm curvature of the support arm 5 by changing the characteristics of the second actuator 9, so that the groove 21 in which the longitudinal end 22 of the support arm is to be disposed can be adjusted by means of the characteristics of the second actuator 9.

[0040] Figure 1 As shown, the loop curvature and / or support arm curvature can be formed in a plane having a normal arranged parallel to the optical axis 27 of the optical body 3. More specifically, it is conceivable that the loop elements 4 are C-shaped. It is also conceivable that the intraocular lens 1 has two loop elements 4, a first actuator 8 for each loop element 4 and a support arm 5, and a second actuator 9 for each support arm 5.

[0041] also, Figure 1As shown, the grooves 21 can be arranged side by side with each other in the direction from the first longitudinal end 25 of the loop element 4 to the second longitudinal end 26 of the loop element 4. Figure 1 It can be seen that the first longitudinal end 25 of the loop element can be disposed away from the optical body 3, while the second longitudinal end 26 of the loop element can be disposed on the optical body 3. Alternatively, it is conceivable that the first longitudinal end 25 of the loop element is disposed on the optical body 3, while the second longitudinal end 26 of the loop element is disposed away from the optical body 3. Depending on which groove 21 the longitudinal end 22 of the support arm is disposed in, either the first longitudinal end 25 or the second longitudinal end 26 of the loop element disposed away from the optical body 3 can be disposed at different distances away from the optical body 3.

[0042] Figure 1 This illustrates how the position of the optic 3 can be altered when the intraocular lens 1 is introduced into the eye's capsule 2. The intraocular lens 1 and capsule 2 are shown at three different moments, with time progressing from left to right. At the first moment, the loop element 4 is in its rest position, and the longitudinal end 22 of the support arm is positioned in the original groove within the recess 21. At the first moment, the characteristics of the first actuator 8 are altered by irradiating it with electromagnetic radiation 7. This can be achieved, for example, by means of a laser. At the second moment, this is shown, causing the loop element 4 to move away from the optic 3 and toward the capsule 2 from its rest position. This increases the distance between the longitudinal end 22 of the support arm and the original groove. It is also shown that at the second moment, the characteristics of the second actuator 9 can be altered, for example, by irradiating it with electromagnetic radiation 7, for example, by means of a laser. This changes the curvature of the support arm. At the third moment, the loop element 4 is shown positioned in another rest position. Furthermore, the longitudinal end 22 of the support arm is now positioned closer to the optical body 3 than at the first moment, and is located in a groove in the groove 21 other than the original groove. As a result, the loop element 4 is positioned further away from the optical body 3 at the third moment than at the first moment. Alternatively, it is conceivable that the longitudinal end 22 of the support arm is positioned further away from the optical body 3 at the third moment than at the first moment, and is located in a groove in the groove 21 other than the original groove, resulting in the loop element 4 being positioned closer to the optical body 3 at the third moment than at the first moment. In this way, the position of the optical body 3 in the pouch 2 can be changed.

[0043] Figure 1 , Figure 3 and Figure 4As shown, in the first and third embodiments of the artificial lens 1, the characteristic of the first actuator 8 can be the temperature of the first actuator 8, and the first actuator 8 can include a bimetallic part 10 of the first actuator 8 extending within the loop element 4. Furthermore, the characteristic of the second actuator 9 can be the temperature of the second actuator 9, and the second actuator 9 can include a bimetallic part 11 of the second actuator 9 extending within the support arm 5. Figure 3 and Figure 4 As shown, the bimetallic 10 of the first actuator 8 may have a first metal 12 and a second metal 13, which are elongated and arranged side-by-side with respect to each other in a direction perpendicular to the longitudinal direction of the first metal 12 and the second metal 13, wherein the second metal 13 is positioned further outward than the first metal 12 relative to the optical element 3. It is conceivable that the coefficient of thermal expansion of the first metal 12 is higher than that of the second metal 13. This is the case, for example, when the first metal 12 is zinc and the second metal 13 is stainless steel. This higher coefficient of thermal expansion of the first metal 12 than the second metal 13 enables the loop element 4 to move outward when the first actuator 8 is heated. Similarly, it is conceivable that the bimetallic 11 of the second actuator 9 may have a first metal and a second metal, which are elongated and arranged side-by-side with respect to each other in a direction perpendicular to the longitudinal direction of the first metal and the second metal 12, wherein the coefficients of thermal expansion of the first metal and the second metal 12 are different. "Metal" is also understood to refer to an alloy.

[0044] from Figure 1 It can be seen that the bimetallic element 10 of the first actuator 8 can extend into the optical element 3. In addition, the bimetallic element 11 of the second actuator 9 can extend into the optical element 3.

[0045] It is conceivable that when the temperature of the first actuator 8 is below its threshold temperature, the loop element 4 is in its stationary position, and the loop element is configured to move away from the optical body 3 when the first actuator 8 is heated to a temperature above its threshold temperature. The threshold temperature of the first actuator 8 can be selected such that it is just above body temperature, for example, above 40°C. More specifically, the threshold temperature of the second actuator can be from 40°C to 50°C. For example, by selecting such a threshold temperature, it is possible to achieve, according to Figure 1 At the third moment, the loop element 4 moves back to its stationary position as the first actuator 8 is cooled by heat conduction.

[0046] Figure 1As shown, the first actuator 8 may have a thickened portion 14 of the first actuator 8 that is thermally connected to the bimetal 10 of the first actuator 8. More specifically, in a plane having a normal parallel to the optical axis 27 of the optical body 3, the thickened portion 14 of the first actuator 8 may be thicker than the rest of the bimetal 10 of the first actuator 8. Furthermore, the second actuator 9 may have a thickened portion 15 of the second actuator 9 that is thermally connected to the bimetal 11 of the second actuator 9. More specifically, in a plane having a normal parallel to the optical axis 27 of the optical body 3, the thickened portion 15 of the second actuator 9 may be thicker than the rest of the bimetal 11 of the second actuator 9. Furthermore, Figure 1 As shown, the thickened portion 14 of the first actuator 8 and / or the thickened portion 15 of the second actuator 9 can be disposed in the region of the optical body 3.

[0047] Figure 2 As shown, in a second embodiment of the intraocular lens 1, the first actuator 8 may have a reservoir 16 for the first actuator 8 and a conduit 17 for the second actuator 8 extending within the loop element 4. Substance 18 of the first actuator 8 may be disposed in the reservoir 16 and the conduit 17 of the first actuator 8. The reservoir 16 and the conduit 17 of the first actuator 8 may be fluidly connected to each other. The characteristics of the first actuator 8 may be the temperature and / or the phase state of the substance 18 of the first actuator 8. It is conceivable that the substance 18 of the first actuator 8 completely fills the reservoir 16 and the conduit 17 of the first actuator 8. Similarly, it is conceivable that the second actuator 9 may have a reservoir for the second actuator 9 and a conduit for the second actuator 9 extending within the support arm 5, wherein substance of the second actuator 9 is disposed in the reservoir and the conduit of the second actuator 9. The reservoir of the second actuator 9 and the conduit of the second actuator 9 can be connected to each other by fluid conduction. The characteristics of the second actuator 9 can be the temperature and / or phase state of the material of the second actuator 9. It is conceivable that the material of the second actuator 9 completely fills the reservoir of the second actuator 9 and the conduit of the second actuator 9. Phase state can be understood as a spatial region with uniform material properties. For example, a change in phase state should be understood as a transition from solid to liquid or from liquid to solid, or from liquid to gas or from gas to liquid. Chemical transformations (e.g., from monomer to dimer or from dimer to monomer) also constitute a change in phase state.

[0048] Figure 2It is shown that, in a plane having a normal parallel to the optical axis 27 of the optical body 3, the reservoir 16 of the first actuator 8 can be wider than the conduit 17 of the first actuator 8. Furthermore, it is conceivable that, in a plane having a normal parallel to the optical axis 27 of the optical body 3, the reservoir of the second actuator 9 can be wider than the conduit of the second actuator 9. Additionally, Figure 2 As shown, the reservoir 16 of the first actuator 8 can be disposed in the region of the optical body 3. Similarly, it is conceivable that the reservoir of the second actuator 9 can be disposed in the region of the optical body 3.

[0049] For example, the substance 18 of the first actuator 8 can be a gas and / or a liquid. For example, the substance of the second actuator 9 can be a gas and / or a liquid.

[0050] It is conceivable that substance 18 has a photosynthetic system comprising a certain amount of monomers and / or a certain amount of dimers, wherein the two monomers are configured to undergo photochemical addition, particularly photocycloaddition, particularly [2+2] photocycloaddition, and thus form a dimer, and the dimer is configured to undergo photodissociation, and thus form two monomers. For example, a photosynthetic system for this purpose may include coumarins, coumarin derivatives, cinnamates (especially methyl cinnamate), cinnamate derivatives or arsenic derivatives, and / or dimers of the above compounds.

[0051] To prevent unwanted dimer formation or unwanted dimer decomposition, the intraocular lens 1 may include a bandpass filter disposed around the material 18 and configured to allow a first wavelength range Λ1 and a second wavelength range Λ2 to pass through the photosynthetic system, wherein irradiation of the photosynthetic system within the first wavelength range Λ1 causes dimer dissociation and irradiation of the photosynthetic system within the second wavelength range Λ2 causes dimer formation. For example, the material may be mixed with the bandpass filter, or the bandpass filter may be disposed outside the conduit and / or reservoir.

[0052] Figure 5 An example of the absorption spectrum of a bandpass filter is shown. Wavelength 28 is plotted on the horizontal axis, and absorption 29 is plotted on the vertical axis. The bandpass filter has multiple different absorbers, each with a separate absorption band 32. All the individual absorption bands 32 accumulate to form the overall absorption 33 of the bandpass filter. The overall absorption 33 is smaller in the first wavelength range Λ1 and the second wavelength range Λ2 than in adjacent wavelength ranges. The absorption band 30 of the dimer is set in the first wavelength range Λ1, and the absorption band 31 of the monomer is set in the second wavelength range Λ2. Figure 5 As shown, the first wavelength range Λ1 and the second wavelength range Λ2 are separate from each other. Alternatively, it can be envisioned that the first wavelength range Λ1 and the second wavelength range Λ2 overlap.

[0053] Figure 1As shown, the characteristic of the second actuator 9 can be its temperature, wherein the longitudinal end 22 of the support arm is configured to: be disposed in a groove in the region of the first longitudinal end 25 of the loop element in the groove 21 when the temperature of the second actuator 9 is below its threshold temperature, and move toward the second longitudinal end 26 when the second actuator 9 is heated to a temperature above its threshold temperature. The threshold temperature of the second actuator 9 can be selected such that it is just above body temperature, for example, above 40°C. More specifically, the threshold temperature of the second actuator 9 can be from 40°C to 50°C. For example, such a selection of the threshold temperature can achieve the effect that, in the case of cooling by heat conduction, the longitudinal end 22 of the support arm automatically moves toward the first longitudinal end 22 of the loop element.

[0054] from Figure 1 It can also be seen that the locking teeth 6 can be disposed between every two adjacent grooves 21, and have a first tooth surface 23 arranged facing the second longitudinal end 26 of the loop element and a second tooth surface 24 arranged facing the first longitudinal end 25 of the loop element. The first tooth surface 23 and the second tooth surface 24 are shaped such that when the loop element 4 is in its rest position, the longitudinal end 22 of the support arm can slide toward the second longitudinal end 26 of the loop element, while sliding toward the first longitudinal end 25 of the loop element is prevented. As a result, when the second actuator 9 is heated, movement of the longitudinal end 22 of the support arm is facilitated. In contrast, when the second actuator 9 is cooled, movement of the longitudinal end of the support arm is prevented when the loop element 4 is in its rest position. For example, this behavior of the longitudinal end 22 of the support arm can be achieved by the first tooth surface 23 protruding more steeply from the surface of the loop element 4 than the second tooth surface 24.

[0055] Figures 1 to 4As shown, the loop element 4 may include a polymer 19 in contact with the first actuator 8. It is conceivable that the polymer 19 is made of the same material as the optical element 3. For example, the polymer 19 of the loop element 4 may be silicone and / or polyacrylate. For example, the glass transition temperature of the polymer 19 of the loop element 4 may be below body temperature, i.e., below 37°C. As a result, when the polymer 19 of the loop element 4 is disposed in the pouch 2, the polymer is soft and therefore deformable. Alternatively, it is conceivable that the glass transition temperature of the polymer 19 of the loop element 4 is above body temperature; more specifically, the glass transition temperature is from 37°C to 41°C. This allows the polymer 19 of the loop element 4 to be softened by heating the first actuator 8, as the polymer of the loop element 4 is heated to a temperature above the glass transition temperature due to heat conduction from the first actuator 8. The glass transition temperature is the temperature at which a polymer undergoes a phase transition from a solid state to a viscous state. The glass transition temperature may be determined at the temperature at which the viscous state of the polymer begins to form. According to Figure 1 and Figure 4 In a first embodiment of the intraocular lens 1, the polymer 19 of the loop element 4 contacts the actuator 8 on the side of the first actuator 8 away from the optics 3. The side of the first actuator 8 facing the optics 3 does not have the polymer 19 of the loop element 4. Alternatively, the locking tooth 6 may be mounted on the side of the first actuator 8 facing the optics 3. According to... Figure 2 In a second embodiment of the intraocular lens 1, the polymer 19 of the loop element 4 completely covers the conduit 17 of the first actuator 8 extending within the loop element 4. According to... Figure 3 In a third embodiment of the artificial lens 1, the polymer 19 of the loop element 4 completely covers the bimetal 10 of the first actuator 8 extending within the loop element 4.

[0056] from Figure 1 It can be seen that the support arm 5 may include a polymer 20 that forms contact with the second actuator 9. It is conceivable that the polymer 19 of the loop element 4 is made of the same material as the optical body 3. For example, the polymer 20 of the support arm 5 may be silicone and / or polyacrylate. For example, the glass transition temperature of the polymer 20 of the support arm 5 may be below body temperature, i.e., below 37°C. As a result, when the polymer 20 of the support arm 5 is disposed in the pouch 2, the polymer is soft and therefore deformable. Alternatively, it is conceivable that the glass transition temperature of the polymer 20 of the support arm 5 is above body temperature; more specifically, the glass transition temperature is from 37°C to 41°C. This allows the polymer 20 of the support arm to be softened by heating the second actuator 9, which heats the polymer 20 of the support arm to a temperature above the glass transition temperature due to heat conduction from the second actuator 9. Figure 1As shown, the polymer 20 of the support arm 5 may be disposed on the side of the second actuator 9 facing the optical body 3, and the distal side of the second actuator 9 may be free of the polymer 20 of the support arm 5. Alternatively, it is conceivable that the polymer 20 of the support arm 5 completely covers the second actuator 9 extending within the support arm 5.

[0057] List of reference numerals

[0058] 1. Intraocular lens

[0059] 2. Pouches

[0060] 3 Optical bodies

[0061] 4 loop components

[0062] 5 support arms

[0063] 6 locking teeth

[0064] 7 Electromagnetic radiation

[0065] 8 First actuator

[0066] 9 Second Actuator

[0067] 10 First Actuator 8 Bimetallic

[0068] 11 Bimetallic second actuator 9

[0069] 12 First Metal

[0070] 13 Second Metal

[0071] 14 Thickened part of the first actuator 8

[0072] 15 Thickened part of the second actuator 9

[0073] 16 First actuator 8 storage

[0074] 17. The conduit of the first actuator 8

[0075] 18 The substance of the first actuator 8

[0076] 19-loop element 4 polymer

[0077] 20 support arms 5 polymer

[0078] 21 Grooves

[0079] 22. Longitudinal end of support arm

[0080] 23 First tooth surface

[0081] 24 Second tooth surface

[0082] 25. First longitudinal end of loop element

[0083] 26. Second longitudinal end of loop element

[0084] 27 optical axes

[0085] 28 wavelengths

[0086] 29 Absorption

[0087] 30 absorption band of dimer

[0088] 31 Absorption bands of monomers

[0089] 32 Individual absorption bands

[0090] 33 Overall absorption

[0091] λ1 wavelength

[0092] λ2 wavelength

[0093] Λ1 First wavelength range

[0094] Λ2 Second wavelength range

Claims

1. An artificial lens comprising: an optical body (3); a loop element (4) mounted on the optical body (3) and having a loop curvature, and having a plurality of grooves (21) on the side of the loop element (4) facing the optical body (3); a first actuator (8) configured to reversibly change the loop curvature of the loop element (4) by means of changing the characteristics of the first actuator (8), such that the loop element (4) moves away from the optical body (3) from a rest position of the loop element (4); and a support arm (5) having been mounted on Mounted on the optical body (3), and the longitudinal end (22) of the support arm away from the optical body (3) is configured to be disposed in one of the grooves (21) when the loop element (4) is in the rest position of the loop element (4); and a second actuator (9) configured to reversibly change the curvature of the support arm (5) by means of changing the characteristics of the second actuator (9), so that the groove (21) to which the longitudinal end (22) of the support arm is to be disposed can be adjusted by means of the characteristics of the second actuator (9). in, The characteristic of the first actuator (8) is the temperature of the first actuator (8) and the first actuator (8) includes a bimetallic part of the first actuator (8) extending within the loop element (4), and wherein, The characteristic of the second actuator (9) is the temperature of the second actuator (9) and the second actuator (9) includes a bimetallic part of the second actuator (9) extending within the support arm (5). When the temperature of the first actuator (8) is lower than the threshold temperature of the first actuator (8), the loop element (4) is in the stationary position of the loop element (4), and the loop element is set to move away from the optical body (3) when the first actuator (8) is heated to a temperature higher than the threshold temperature of the first actuator (8).

2. The intraocular lens as described in claim 1, wherein, The first actuator (8) has a thickened portion, the thickened portion being combined with a bimetallic thermally conductive component, and / or wherein, The second actuator (9) has a thickened portion, which is combined with the bimetallic thermally conductive part of the second actuator (9).

3. The intraocular lens as described in claim 2, wherein, The thickened portion of the first actuator (8) and / or the thickened portion of the second actuator (9) are disposed in the region of the optical body (3) or in the region adjacent to the optical body (3).

4. The intraocular lens as described in any one of claims 1 to 3, wherein, The first actuator (8) includes a reservoir (16) of the first actuator (8) and a conduit (17) of the first actuator (8) extending within the loop element (4), wherein the substance (18) of the first actuator (8) is disposed in the reservoir (16) of the first actuator (8) and the conduit (17) of the first actuator (8), wherein the reservoir (16) of the first actuator (8) and the conduit (17) of the first actuator (8) are connected to each other in a fluid conduction manner, and the characteristics of the first actuator (8) are the temperature of the substance (18) of the first actuator (8) and / or the phase state of the substance (18) of the first actuator (8).

5. The intraocular lens according to any one of claims 1 to 3, wherein, The second actuator (9) includes a reservoir of the second actuator (9) and a conduit of the second actuator (9) extending within the support arm (5), wherein the substance of the second actuator (9) is disposed in the reservoir of the second actuator (9) and the conduit of the second actuator (9), wherein the reservoir of the second actuator (9) and the conduit of the second actuator (9) are connected to each other in a fluid conduction manner, and the characteristics of the second actuator (9) are the temperature of the substance of the second actuator (9) and / or the phase state of the substance of the second actuator (9).

6. The intraocular lens as claimed in claim 4, wherein, The substance (18) is a gas and / or a liquid.

7. The intraocular lens as described in claim 5, wherein, The substance (18) is a gas and / or a liquid.

8. The intraocular lens as claimed in claim 4, wherein, The substance (18) has a photosynthetic system comprising a certain amount of monomers and / or a certain amount of dimers, wherein two of the monomers are configured to enter into photochemical addition with each other and thus form the dimer, and the dimer is configured to enter into photodissociation and thus form two of the monomers.

9. The intraocular lens of claim 8, wherein, Two of the monomers are configured to enter the aura addition.

10. The intraocular lens of claim 8, wherein, Two of the monomers are set to enter the [2 + 2] aura enhancement.

11. The intraocular lens as claimed in claim 5, wherein, The substance (18) has a photosynthetic system comprising a certain amount of monomers and / or a certain amount of dimers, wherein two of the monomers are configured to enter into photochemical addition with each other and thus form the dimer, and the dimer is configured to enter into photodissociation and thus form two of the monomers.

12. The intraocular lens of claim 11, wherein, Two of the monomers are configured to enter the aura addition.

13. The intraocular lens of claim 11, wherein, Two of the monomers are set to enter the [2 + 2] aura enhancement.

14. The intraocular lens of claim 8, wherein, The artificial lens (1) includes a bandpass filter disposed around the material (18) and configured to allow a first wavelength range (Λ1) and a second wavelength range (Λ2) to pass through the photosynthetic system, wherein irradiation of the photosynthetic system within the first wavelength range (Λ1) causes the dimer to dissociate and irradiation of the photosynthetic system within the second wavelength range (Λ2) causes the dimer to form.

15. The intraocular lens of claim 4, wherein, The reservoir (16) of the first actuator (8) is located in the region of the optical body (3) or in the region adjacent to the optical body (3), and / or the reservoir of the second actuator (9) is located in the region of the optical body (3) or in the region adjacent to the optical body (3).

16. The intraocular lens of claim 5, wherein, The reservoir (16) of the first actuator (8) is located in the region of the optical body (3) or in the region adjacent to the optical body (3), and / or the reservoir of the second actuator (9) is located in the region of the optical body (3) or in the region adjacent to the optical body (3).

17. The intraocular lens according to any one of claims 1 to 3, wherein, These grooves (21) are arranged side by side in the direction from the first longitudinal end (25) of the loop element (4) to the second longitudinal end (26) of the loop element (4).

18. The intraocular lens of claim 17, wherein, The first longitudinal end (25) of the loop element is disposed on the optical body (3), while the second longitudinal end (26) of the loop element is disposed away from the optical body (3), or wherein, The first longitudinal end (25) of the loop element is disposed away from the optical body (3), while the second longitudinal end (26) of the loop element is disposed on the optical body (3).

19. The intraocular lens of claim 17, wherein, Depending on which of these grooves (21) the longitudinal end (22) of the support arm is located in, the first longitudinal end (25) of the loop element and the second longitudinal end (26) of the loop element are located at different distances from the optical body (3).

20. The intraocular lens of claim 18, wherein, Depending on which of these grooves (21) the longitudinal end (22) of the support arm is located in, the first longitudinal end (25) of the loop element and the second longitudinal end (26) of the loop element are located at different distances from the optical body (3).

21. The intraocular lens of claim 17, wherein, The longitudinal end (22) of the support arm is configured to: be disposed in one of the grooves (21) in the region of the first longitudinal end (25) of the loop element when the temperature of the second actuator (9) is lower than the threshold temperature of the second actuator (9), and move toward the second longitudinal end (26) when the second actuator (9) is heated to a temperature higher than the threshold temperature of the second actuator (9).

22. The intraocular lens of claim 18, wherein, The longitudinal end (22) of the support arm is configured to: be disposed in one of the grooves (21) in the region of the first longitudinal end (25) of the loop element when the temperature of the second actuator (9) is lower than the threshold temperature of the second actuator (9), and move toward the second longitudinal end (26) when the second actuator (9) is heated to a temperature higher than the threshold temperature of the second actuator (9).

23. The intraocular lens of claim 21, wherein, Locking teeth (6) are provided between every two adjacent grooves (21) and have a first tooth surface (23) arranged facing the second longitudinal end (26) of the loop element and a second tooth surface (24) arranged facing the first longitudinal end (25) of the loop element, wherein the first tooth surface (23) and the second tooth surface (24) are shaped such that when the loop element (4) is in its rest position, the longitudinal end (22) of the support arm can slide toward the second longitudinal end (26) of the loop element, while the sliding of the longitudinal end (22) of the support arm toward the first longitudinal end (25) of the loop element is prevented.

24. The intraocular lens of claim 23, wherein, The first tooth surface (23) protrudes more steeply from the surface of the loop element (4) than the second tooth surface (24).

25. The intraocular lens as described in any one of claims 1 to 3, wherein, A locking tooth (6) is provided between every two adjacent grooves (21).

26. The intraocular lens as described in any one of claims 1 to 3, wherein, The loop element (4) includes a polymer in contact with the first actuator (8), and / or the support arm (5) includes a polymer in contact with the second actuator (9).

27. The intraocular lens as described in any one of claims 1 to 3, wherein, The intraocular lens (1) has two loop elements (4), a first actuator (8) for each loop element (4) and a support arm (5), and a second actuator (9) for each support arm (5).

Images