Artificial eye lens with integrated drug depot and method for manufacturing an artificial eye lens

Abstract

Artificial eye lens (1) with an optical part (2) having a first optical side (4) and an opposite second optical side (5) viewed in the direction of a principal optical axis (A) of the artificial eye lens (1), and having a haptic (3), characterized in that a structure with at least one depression is formed in a frame (6) of the artificial eye lens (1) which surrounds the optical part (2) at least partially and is different from the haptic (3), wherein the structure (7, 8) is formed as a microperforation with a plurality of perforation zones (7a, 8a) and at least some perforation zones (7a, 8a) are filled at least partially with at least one drug to create a drug depot.

Description

Technical field

[0001] The invention relates to an artificial eye lens with an optical part comprising a first optical side, viewed along a principal optical axis of the lens, and a second optical side opposite it. The multifocal artificial eye lens also features a haptic element by means of which the lens can be positioned in the eye. The lens has a rim that at least partially surrounds the optical part and is distinct from the haptic element. A structure with at least one depression is formed in the haptic element and / or this rim. Furthermore, the invention also relates to a method for manufacturing such a lens using a laser. State of the art

[0002] Multifocal artificial lenses are known in a wide variety of ways from the state of the art. In particular, intraocular lenses are known that replace the natural lens in the eye and are implanted accordingly.

[0003] A contact lens is known from CN 202 472 154 U, which has an optically effective area. Micropores are formed in a radially outwardly adjacent, optically inactive area, in which a medication may be contained.

[0004] From CN 203 220 483 U, an intraocular lens is known which has an optical part and subsequently crescent-shaped connecting pieces. The connecting piece has recesses in which a drug can be contained.

[0005] Masked intraocular implants and lenses are known from US 2017 / 0143477 A1.

[0006] US Patent 2010 / 0082017 A1 discloses an intraocular lens in which slits are formed in both a haptic and an optical part to modify the mechanical and structural characteristics of the lens. These elongated slits are formed inside the intraocular lens, particularly using a laser.

[0007] Furthermore, US patent 2004 / 0032566 A1 discloses a method for marking an intraocular lens using a laser. The laser is used to micro-perforate the optical part of the lens.

[0008] It is also known that complications can occur during the implantation of artificial lenses, either during the operation itself, during the healing process after the operation, or even later. In such cases, further surgical intervention may be necessary to correct the complications. Description of the invention

[0009] One object of the invention is to create an artificial eye lens with improved functionality. Furthermore, it is an object of the invention to provide a method for manufacturing such a lens.

[0010] One aspect of the invention relates to an artificial eye lens comprising an optical part by which the optical imaging properties of the eye lens are characterized. This optical part has a first optical side and a second optical side opposite the first optical side when viewed along the principal optical axis of this eye lens. The artificial eye lens further comprises a haptic. The haptic holds the eye lens in position within the eye. In addition to the haptic, the artificial eye lens has a rim that surrounds the optical part at least partially and is distinct from the haptic. This rim is neither part of the optical part nor, in particular, is it part of any haptic components, if such a haptic is present. The artificial eye lens has a structure comprising at least one depression. The structure is a microperforation with a plurality of individual and separate

[0011] Perforation zones are formed. Microperforations are defined as perforations with a longitudinal extent in the micrometer and / or nanometer range. At least some of these perforation zones function as drug depots and are at least partially filled with at least one drug.

[0012] This design creates an artificial lens that inherently contains at least one medication. This enhances the lens's functionality. In addition to its primary function of improving visual acuity, this embodiment of the invention also inherently serves as a drug delivery system. Thus, such an artificial lens ensures that the medication is already present in the eye for drug treatment during surgery, particularly for the implantation of an intraocular lens, and / or during the healing process following such surgery, and / or for maintaining the patient's health even after the healing process is complete. The medication can then be dispensed individually by exiting through a perforation.This can be caused by interaction with one or more media within the eye, particularly in the capsular bag, without any external influence. Generally, this release of medication from a perforation zone can occur depending on the environmental conditions within the eye. In this context, a occlusion of a perforation zone, which is formed particularly after the perforation zone has been filled with at least one medication, can also be removed, for example, by dissolving. Depending on the thickness of the occlusion and / or the material, this removal in the implanted eye can also be precisely controlled in terms of timing and / or duration during the fabrication of the artificial lens.This also means that the timing and / or duration of medication release from a perforation zone in the implanted artificial lens can be individually adjusted. Additional surgical procedures, particularly after implantation of such a lens, to promote healing or maintain the healed state, are therefore no longer necessary or only required to a limited extent or in exceptional cases. The burden on patients from subsequent procedures can thus be significantly reduced.

[0013] In particular, such a structure, and thus also a perforation zone, is designed as a laser structure. This means that it is created with a laser. This allows the perforation zone to be created with extreme spatial and / or geometric accuracy. Undesirable dimensional tolerances and / or undesirable impairments of specific areas of the artificial eye lens, especially the optical component, are thereby prevented.

[0014] By creating microperforations in an area of ​​the artificial lens that differs from the optical part, the optical part itself is not affected. The optical imaging properties therefore remain unaffected.

[0015] With at least one such medication depot, it is possible to individually control the timing of the dispensing of at least one medication from the depot. This allows for the rapid and targeted dispensing of a specific, potentially very large, quantity of medication from the depot within the implanted lens, depending on the situation and the specific healing process. It is also possible for this dispensing of medication from the depot to occur continuously and over an extended period after the lens implantation.

[0016] In an advantageous embodiment, a first drug may be placed in at least one perforation zone, which then constitutes a drug depot, and a different second drug may be placed in at least one different second perforation zone, which in turn also constitutes its own drug depot. It may also be provided that at least two different drugs are placed in a common drug depot. Likewise, it is possible that more than two different drugs are placed in one perforation zone as a drug depot, or that at least three drugs are each housed in separate, distinct perforation zones.It is also possible that only one specific medication is placed in one perforation zone, while at least two different medications are placed in at least one other, separate perforation zone. Depending on which medication regimen is preferred for the individual patient and / or the duration of such treatment, these medication depots can be individually configured with medication even before the surgical procedure to implant the lens into the eye. This allows for consideration of various pre-existing conditions of the eye and / or the patient, such as the severity of diabetes and / or high blood pressure, etc.This also makes it possible to design such an artificial eye lens in a very patient-specific way, and depending on the patient's health and constitution, the design of these drug depots can then be very individual and tailored to the patient's needs.

[0017] Preferably, the perforation zones, which are at least partially filled with at least one drug, are designed as blind holes. This allows for a highly individualized and precise volume control, particularly using a laser, so that the amount of drug introduced into such a perforation zone can be very accurately controlled. Furthermore, this design prevents the unwanted leakage of the drug in an unintended direction. The release or escape of the drug from the perforation zone can then only occur in the direction in which the blind hole has its opening.

[0018] Preferably, the blind holes are funnel-shaped in cross-section, so that the cross-sectional area of ​​a blind hole decreases with increasing depth. This results in lower capillarity at the upper edge of the blind hole than at the bottom. This is advantageous because it allows for varying rates of drug release from the blind hole depending on its opening angle.

[0019] It can be designed so that the microperforations, and thus the perforation zones, are oriented in the same direction, or at least that two different perforation zones are oriented differently along their longitudinal axes. This allows for the creation of a customized structure depending on which medications are to be used and / or where they are primarily intended to exert their effects. This also ensures that the structure itself is tailored to the specific individual requirements, particularly the patient. This means that the number, location, orientation, and / or position of the perforation zones can be individually configured.

[0020] This can also be done in such a way that the perforation zones are locally specified on the haptics and / or the edging, depending on which medications and / or which quantity of medications are required for this individual shaping of the eye lens.

[0021] The artificial lens is preferably multifocal, or at least bifocal. The artificial lens is preferably an intraocular lens.

[0022] Preferably, the optical part of the multifocal artificial eye lens has a diameter greater than 6 mm. This ensures that the optical part extends over a large and / or very wide-opening pupil of the eye. In particular, this diameter of the optical part is greater than 6.5 mm.

[0023] The structure of the perforation zones may include at least one ring encircling the principal optical axis. Additionally or instead, the structure may also include at least one line of perforation zones oriented perpendicular to the principal optical axis. In particular, the structure may have a star shape encircling the principal optical axis, formed by the arrangement of the perforation zones. This allows for consideration of individual needs regarding the required location of the perforation zones containing the medications and / or the potentially more localized advantage of a larger quantity of one medication and / or the more localized advantage of at least two different medications.

[0024] Preferably, the artificial eye lens has a further structure, which is designed as an artificial aperture diaphragm or marking in the optical part. This further structure, which is thus different from the first structure formed in the haptic and / or the rim, is formed in this optical part at a radial distance of greater than or equal to 3 mm from the principal optical axis. This further structure is designed, in particular, as a microperforation with further perforation zones in this optical part. It can be provided that this further structure is designed as a laser structure and is thus produced with a laser. These further perforation zones of the further structure can be filled with a dye.This design makes it easy for a surgeon to characterize the eye lens with regard to, for example, its optical parameters and / or its orientation within the eye, such as in the case of a toric multifocal artificial lens. These additional perforation zones can also be designed to have a diameter of just a few micrometers and be created using an ultrashort pulse laser. This design ensures that they do not impair the optical imaging properties of the optical component while still allowing for the inscription of visually readable information within the optical component, as described above. For example, the position of cylinder axes, refractive parameters, and a type designation can be generated as readable information within the optical component.The reading can then be performed reliably, for example with a slit lamp, even during patient follow-up. In particular, it is also possible to provide such labeling outside of the photopic and / or mesopic pupil diameter.

[0025] The perforation zones can, for example, be designed as ring-shaped cavity channels or as closed rings in the form of cavity channels, and feature an internal coloration in the form of an aperture diaphragm acting as an artificial pupil by introducing an absorbing, biocompatible dye. These absorbing cavity channels can be used or designed to suppress scattered light under extreme viewing conditions, possibly in diffractive structures. Additionally or instead, a fluorescent dye can be provided for labeling, for example, an infrared dye.

[0026] An aperture diaphragm can be created alternatively or additionally to a dye by means of a different degree of polymerization of the material of the artificial eye lens by the action of a laser beam, in particular by multiphoton polymerization.

[0027] In an advantageous embodiment, this microperforation of the further structure is designed such that the aperture diaphragm can be automatically adjusted in its opening width depending on the incident light. This creates variable light transmission within the artificial eye lens and thus also provides an artificial pupil. As already explained above, this can be achieved in particular by specific dyes that are then introduced into this microperforation.

[0028] Preferably, the microperforation is provided that it comprises a plurality of perforation zones which are arranged differently with respect to their spacing. In particular, a statistical distribution can be implemented between them. The plurality of perforation zones can additionally or instead also be arranged differently with respect to their relative positions, and here too, a statistical distribution of these positions can be implemented. Additionally or instead, it can also be provided that this plurality of perforation zones differs in their dimensions. In particular, the zone diameter and / or the zone depth of a perforation zone can be designed to differ accordingly.

[0029] In particular, at least one microperforation has at least one perforation zone that is an annular channel, which is therefore, in particular, a completely closed, circumferential annular channel. This is especially advantageous for the design of an artificial pupil with, in particular, a light-dependent, radially changing light transmission.

[0030] Preferably, the microperforation is provided to have at least one perforation zone which is at least partially filled with at least one wavelength-selective or intensity-dependent dye with respect to its absorption behavior.

[0031] It may also be provided that a dye composition varying in the radial direction to the main optical axis with respect to absorption behavior is introduced into at least one perforation zone of this further structure, in which the absorption behavior increases in the radial direction to the main optical axis with increasing intensity of the incident light.

[0032] In a further embodiment, the optical part of the eye lens may have an additional structure formed as microperforations at least circumferentially around the principal optical axis of the optical part. This additional structure is formed in the optical part in a first radius interval between 1.5 mm and 2.5 mm relative to the principal optical axis and / or in a second radius interval between 3.0 mm and 4.0 mm relative to the principal optical axis. It may be provided that these structural rings, formed at specific locations in the radial direction, can transmit individual information about the eye lens and, on the other hand, provide additional functionality to the eye lens, in particular the generation of an artificial pupil.

[0033] It may be provided that a diffractive element is formed on at least one side of the optical part. At least one side may also be spherical or aspherical. Likewise, at least one side may have a toric surface profile. Similarly, ring-shaped zones, which may be implemented as Fresnel zones, may be formed on at least one side of the optical part. Such ring-shaped zones may also be configured such that they comprise a main subzone and a subsequent phase subzone. In such a configuration, the phase subzone is not oriented parallel to the main optical axis, but rather inclined to it, and has its own refractive power that contributes to the overall refractive power of this ring-shaped zone.Such a phase subzone generates an optical path length difference between two main subzones that directly adjoin this phase subzone in the radial direction. The aforementioned configurations of at least one side of the optical part can also be formed individually or in any combination.

[0034] In order to introduce additional diffractive properties beyond the refractive power of the eye lens due to its refractive power and shape, it is advantageously also provided to form a regular and thus uniform arrangement of this microstructure and thus of the perforation zones and a regular diameter generation of these perforation zones.

[0035] It may also be anticipated that, following cataract surgery, a secondary cataract may occur with an implanted intraocular lens, caused by the proliferation of epithelial cells towards the posterior capsule membrane. To at least mitigate this, it is preferably intended that microstructures, including nanostructures, be designed as perforation zones to modify the roughness and wettability of the intraocular lens outside the optical portion, particularly as laser structures. This allows cell adhesion and proliferation to be influenced. Thus, guiding structures can be created that promote directed cell growth and can therefore at least significantly suppress the negative effects in this regard.In particular, nanostructures that can be fabricated through interference structuring alter the distribution of focal adhesion sites on the cell and influence, among other things, complex mechanisms such as cell proliferation. Furthermore, the application of densely arranged bores and semiperforation zones as blind holes outside the optical region enables adhesion of the posterior capsular bag membrane. An example of such a structure is a honeycomb structure in which the perforation zones, designed as microbores, are arranged and formed.

[0036] Furthermore, the invention also relates to a method for producing a multifocal artificial eye lens according to the aspects mentioned above, in which a structure is produced with a laser device and a pulsed laser beam with a pulse length between 100 fs and 20 ps, ​​a wavelength between 200 nm and 1,100 nm, a pulse repetition rate between 1 kHz and 10 MHz, a focus diameter of less than 5 µm and a power density of greater than 10 6 W / cm 2 The pulse is generated and acts on the material of the artificial eye lens. Preferably, the pulse length is 300 fs and the wavelength is preferably 1060 nm, 532 nm, or 355 nm. A disruptive process can preferably provide a wavelength of 256 nm, and more preferably 213 nm, particularly for ablative processing.

[0037] A further independent aspect of the invention relates to an artificial eye lens comprising an optical element by which the optical imaging properties of the artificial eye lens are characterized. This optical element has a first optical side and a second optical side opposite the first optical side when viewed in the direction of the principal optical axis of this artificial eye lens. The artificial eye lens has a structure designed as a microperforation, which is formed at least partially circumferentially around the principal optical axis of the optical element. The optical element has a diameter greater than 6 mm, in particular greater than or equal to 6.5 mm. The structure is designed as an artificial aperture diaphragm in the optical element at a radial distance of greater than or equal to 3 mm from the principal optical axis.

[0038] A further independent aspect of the invention relates to an artificial eye lens comprising an optical part by which the optical imaging properties of the artificial eye lens are characterized. This optical part has a first optical side and a second optical side opposite the first optical side when viewed along the principal optical axis of this artificial eye lens. The multifocal artificial eye lens further comprises a haptic. The haptic holds the eye lens in position within the eye. The multifocal artificial eye lens may also have, in addition to or instead of the haptic, a rim that surrounds the optical part at least partially and is distinct from the haptic. This rim is neither part of the optical part nor part of a haptic if such a haptic is present. The multifocal artificial eye lens has a structure comprising at least one depression.The structure consists of microperforations with numerous individual and separate perforation zones. These perforation zones are formed as blind holes. The perforation zones create a network structure, specifically a honeycomb pattern.

[0039] A further independent aspect of the invention relates to an artificial eye lens comprising an optical element by which the optical imaging properties of the artificial eye lens are characterized. This optical element has a first optical side and a second optical side opposite the first optical side when viewed in the direction of the principal optical axis of this artificial eye lens. The artificial eye lens has a structure designed as a microperforation, which is formed at least partially circumferentially around the principal optical axis of the optical element. The structure is formed within the optical element. Specifically, the structure is formed within the optical element in a first radius interval between 1.5 mm and 2.5 mm relative to the principal optical axis and / or in a second radius interval between 3.0 mm and 4.0 mm relative to the principal optical axis.

[0040] Embodiments of the first independent aspect of the invention are to be regarded as advantageous embodiments of the further independent aspects. The same applies to the manufacturing process.

[0041] Further features of the invention are evident from the claims, the figures, and the description of the figures. The features and combinations of features mentioned above in the description, as well as those subsequently mentioned in the description of the figures and / or shown in the figures alone, are not only usable in the combinations specified, but also in other combinations without departing from the scope of the invention. Thus, embodiments that are not explicitly shown and explained in the figures, but which can be derived and generated from the explained embodiments by separate combinations of features, are also to be considered as encompassed and disclosed by the invention. Embodiments and combinations of features that do not exhibit all the features of an originally formulated independent claim are also to be considered disclosed.Furthermore, embodiments and combinations of features, in particular those set out above, are to be considered disclosed which go beyond or deviate from the combinations of features set out in the cross-references of the claims.

[0042] The specific parameter values ​​and information on parameter ratios or parameter values ​​specified in the documents for defining exemplary embodiments of the eye lens are also to be considered as included within the scope of the invention, even in the case of deviations, for example due to measurement errors, system errors, DIN tolerances, etc., which also includes explanations relating to essentially corresponding values ​​and information. Brief description of the drawings

[0043] Exemplary embodiments of the invention are explained in more detail below with reference to schematic drawings. These show: Fig. 1 a top view of a first embodiment of an artificial eye lens according to the invention in schematic representation; Fig. 2 a top view of a second embodiment of an artificial eye lens according to the invention in schematic representation; Fig. 3 a top view of a third embodiment of an artificial eye lens according to the invention in schematic representation; and Fig. 4 a simplified schematic representation of a laser device for creating a structure on an eye lens according to Fig. 1 to 3. Preferred embodiments of the invention

[0044] In the figures, identical or functionally equivalent elements are provided with the same reference symbols.

[0045] In Fig. Figure 1 shows a first embodiment of a multifocal artificial eye lens 1, which is an intraocular lens. The artificial eye lens 1 has an optical part 2 and a haptic 3 adjoining it. The artificial eye lens 1 is foldable and can be inserted into the eye through a small incision. The optical part 2, which is essential for the optical imaging properties of the artificial eye lens 1, has a principal optical axis A, which is oriented perpendicular to the plane of the figure and, in particular, is perpendicular to a principal plane of the optical part 2. Furthermore, the optical part 2, viewed in the direction of this principal optical axis A, has a first optical surface or optical side 4, which can be a front, and opposite it, a second optical surface or optical side 5, which can be a back.In the implanted state of the eye lens 1, the front side faces the cornea, whereas the back side faces away from the cornea.

[0046] The artificial eye lens 1 can have a rim 6 in addition to, or instead of, the haptic 3. The rim 6 is not part of the optical part 2 and therefore does not contribute to the optical imaging properties of the artificial eye lens 1, nor to those of the optical part 2. The same applies to the haptic 3. Here, the rim 6 is designed as a completely circumferential ring. However, the rim 6 can also be designed only as a ring segment, for example, only in the area between a haptic 3 and the optical part 2, such as a bridge or connector between these components.

[0047] In Fig. Figure 2 shows a further embodiment of a multifocal artificial eye lens 1 designed as an intraocular lens in a top view. It differs from the embodiment in Fig. 1 through the different haptics 3. By means of the haptics 3, the eye lens 1 is also held in the eye, especially in the capsular bag.

[0048] In Fig. Figure 3 shows a further embodiment of an eye lens 1 in a top view. Here, the frame 6 is also preferably designed as a circumferential ring. The haptic element can be omitted here, and its function can be fulfilled by the frame 6. However, it is also possible that ring segments of this ring around the optical part 2 form a partially circumferential frame 6, and other ring segments form a haptic element.

[0049] The optical surfaces 4 and 5 are preferably unevenly curved, in particular convexly. In particular, a diffractive profile and / or a toric profile is formed on at least one optical surface 4, 5 on this convex, in particular spherical or aspherical, basic shape.

[0050] In principle, differently shaped and designed haptics 3 and / or edgings 6 may also be provided.

[0051] The multifocal artificial eye lens 1, as used in Fig. 1 and Fig. Figure 2, shown in different embodiments, features a structure 7 of the haptic element 3, if present, and / or a structure 8 of the edging 6, if present. It should be noted here that both the spatial positions and the geometric configurations of structures 7 and 8 are merely symbolic and intended to clarify these structures; they do not constitute a definitive specification. Structure 7 is designed as a microperforation with a plurality of perforation zones 7a. The perforation zones 7a are specifically designed as blind holes and microbores. They are created using a laser-etched structure and a laser device.

[0052] At least some of these perforation zones 7a are designed as drug depots and are thus partially filled with at least one drug. Additionally or instead, the structure 8 may also be a microperforation with a multitude of perforation zones 8a. Fig. For clarity, only one representation of perforation zones 8a is shown in Figure 1. These perforation zones 8a are also preferably designed as blind holes and produced using a laser device. Here too, at least some of the perforation zones 8a are designed as drug depots and are at least partially filled with at least one drug. The perforation zones 7a and / or 8a can be formed in one or more lines. They can be geometrically identical or different from each other. They can be arranged regularly or in a statistically distributed pattern.

[0053] Structure 8 may have at least one ring encircling the principal optical axis A. Additionally or instead, structure 8 may have a structural region oriented radially to the principal optical axis A. Other geometric configurations of perforation zones may also be present in structure 7 and / or structure 8.

[0054] In one embodiment, particularly regardless of the local and geometric design of a structure 7 and / or 8, the optical part 2 can have a diameter d that is greater than 6 mm, in particular greater than 6.5 mm.

[0055] The optical part 2, also generated as a laser structure, particularly by the laser device, can have a structure 9, which can be a further structure 9 configured as an artificial aperture diaphragm. In particular, this artificial aperture diaphragm is configured in the optical part 2 at a radial distance of greater than or equal to 3 mm from the principal optical axis A, provided that the optical part 2 has a diameter greater than 6 mm. This further structure 9 is also configured, in particular, as a microperforation. This further structure 9 is, in particular, filled with at least one dye. Preferably, this microperforation of the further structure 9 is configured such that the aperture diaphragm can be automatically changed in its opening width depending on the incident light. An artificial pupil is thereby created within the artificial lens 1 itself.

[0056] This microperforation of the further structure 9 has in particular a plurality of perforation zones 9a which are arranged differently with respect to their distance from each other, in particular are arranged statistically distributed from each other, and / or are arranged differently with respect to their position from each other, in particular are arranged statistically distributed from each other, and / or are formed differently with respect to their dimensions, in particular a perforation zone diameter and / or a perforation zone depth.

[0057] It can also be provided that this further structure 9 has at least one ring completely encircling the principal optical axis A, or in particular, two such rings completely encircling the principal optical axis, spaced apart from each other in the radial direction relative to the principal optical axis A. It can be provided that this further structure 9 has, in particular, a ring of microperforations and thus perforation zones, designed as microbores, in a first radius interval between 1.5 mm and 2.5 mm relative to the principal optical axis A and / or in a second radius interval between 3.0 mm and 4.0 mm relative to the principal optical axis. However, this configuration can also be formed by a further structure that differs from the further structure 9 in this respect.

[0058] The to Fig. The different embodiments explained in point 1 are also applicable to the design according to Fig. 2 and Fig. 3 possible. In Fig. 2 is the one in Fig. Figure 1, which was explained but not shown there for clarity, illustrates a further structure 10 with the perforation rings shown at the specific radius intervals. These rings 10a and 10b at the radius intervals between 1.5 mm and 2.5 mm and between 3.0 mm and 4.0 mm are also shown here only symbolically for clarity.

[0059] In Fig. Figure 3 shows a specific geometry of structure 8, which here represents a star shape. This star shape extends from an inner edge 6a of the frame 6 to an outer edge 6b of this frame 6. The perforation zones 8a are also shown symbolically. Such a star shape of structure 8 can also be found in the embodiments in Fig. 1 and Fig. 2 is provided. To clarify this star shape, the frame is shown radially enlarged in comparison to the optical part 2.

[0060] The design may include the following configurations: some of the perforation zones 7a and / or 8a may be open towards the optical side 4 of the optical part 2, or perforation zones 7a and 8a may be open only towards the optical side 5 of the optical part 2. It is also possible for some of the perforation zones 7a and / or 8a to be open towards the optical side 4 and some of the perforation zones 7a and 8a to be open towards the optical side 5. These alternatives are particularly suitable if these perforation zones 7a and 8a are designed as blind holes. This allows for individual customization of the perforation zones and their openings, thus enabling specific localized delivery of the medication(s).

[0061] In Fig.Figure 4 shows a schematic representation of a laser device 11 designed for producing a multifocal artificial lens 1. In particular, this laser device 11 enables the creation of a structure 7 and / or a structure 8 and / or a structure 9 and / or a structure 10. The laser device 11 comprises at least one laser 12, which is an ultrashort pulse laser. This laser device 11 includes a scanner 13, which is adjustable in three dimensions, by means of which the pulsed laser beam of the laser 12 can be adjusted. Furthermore, the laser device 11 includes a focusing optic 14, which is arranged downstream of the scanner 13 in the beam path. The laser device 11 also has a receptacle 15 on which the artificial lens 1 is mounted, so that the desired structuring can then be applied with the laser beam 16 focused by the focusing optic 14.The laser beam 16 with its laser pulses is in particular equipped with a pulse length between 100 fs and 20 ps, ​​in particular a wavelength between 200 nm and 1,100 nm, in particular a pulse repetition rate between 1 kHz and 10 MHz, in particular a focus diameter less than 5 µm and in particular a power density greater than 10. 8 W / cm 2 This generates a multiphoton absorption effect. The focusing optics 14 can have a numerical aperture greater than 0.1, preferably greater than 0.3, and particularly greater than 0.5. The laser device 11 also makes it possible to generate focus diameters of less than 5 µm, particularly less than 2 µm. A power density of the focused laser beam greater than 10 is achieved. 10 W / cm 2This is useful to achieve optical breakthrough (photodisruption) of the polymer material of the artificial eye lens, for example, if linear absorption of the polymer material does not support this effect. To achieve only a non-linear interaction in the polymer material of the artificial eye lens 1, a power density of less than 10 is also sufficient. 10 W / cm 2 The process is designed to prevent photodisruption, but to alter optical and / or mechanical, and consequently hygroscopic, material properties. To ensure high processing efficiency of the artificial eye lens, a repetition rate of the ultrashort laser pulses of laser beam 16 in the range of 1 kHz to 10 MHz is advantageous. Pulse energies in the sub-µJ range are used. Particularly at repetition rates greater than 1 MHz, a pulse energy of less than 1 µJ is also possible due to cumulative interaction effects.

[0062] In particular, structure 7 and / or structure 8, in addition to the described configurations, can also be designed, at least in certain areas, as drug depots, especially within micro-shells or nano-shells, and especially in the form of rings encircling the principal optical axis A, at least in certain areas. This allows for a modification of the roughness and wettability of the artificial lens 1 in these areas. This is advantageous because it can reduce the occurrence of posterior capsule opacification (PCO) or enable its targeted control.

[0063] In particular, individual perforation zones can be provided and formed in the edge area of ​​structure 8 to enable better adhesion to the capsular bag. This also improves the positional arrangement of the lens 1 within the capsular bag. The arrangement can, for example, be designed as a honeycomb structure, so that the corresponding perforation zones 8a are designed accordingly. These features can be implemented in addition to and / or as an option to the features already described above.

Claims

[1] Artificial eye lens (1) with an optical part (2) having a first optical side (4) and an opposite second optical side (5) when viewed in the direction of a principal optical axis (A) of the artificial eye lens (1), and having a haptic (3), characterized by , that in a setting (6) of the artificial eye lens (1) surrounding the optical part (2) at least partially and different from the haptic (3) a structure with at least one depression is formed, wherein the structure (7, 8) is formed as a microperforation with a plurality of perforation zones (7a, 8a) and at least some perforation zones (7a, 8a) are filled at least partially with at least one drug to create a drug depot. [2] Artificial eye lens (1) according to claim 1, characterized by , that the perforation zones (7a, 8a) which are at least partially filled with at least one drug are formed as blind holes. [3] Artificial eye lens (1) according to any one of the preceding claims, characterized by , that the optical part (2) has a diameter (d) greater than 6 mm, in particular greater than 6.5 mm. [4] Artificial eye lens (1) according to any one of the preceding claims, characterized by , that a further structure (9) is formed as an artificial aperture diaphragm in the optical part (2) at a radial distance of greater than or equal to 3 mm to the principal optical axis (A) as a microperforation in the optical part (2). [5] Artificial eye lens (1) according to claim 4, characterized by , that the microperforation is designed in such a way that the aperture diaphragm can be automatically changed in its opening width depending on the incident light. [6] Artificial eye lens (1) according to claim 4 or 5, characterized by, that the microperforation has a plurality of perforation zones (9a) which are arranged differently with respect to their distance from each other, in particular are arranged statistically distributed from each other, and / or are arranged differently with respect to their position from each other, in particular are arranged statistically distributed from each other, and / or are formed differently with respect to their dimensions, in particular a zone diameter and / or a zone depth. [7] Artificial eye lens (1) according to any one of claims 4 to 6, characterized by that the microperforation has at least one perforation zone (9a) which is a ring canal. [8] Artificial eye lens (1) according to any one of claims 4 to 7, characterized by , that the microperforation has at least one perforation zone (9a) which is at least partially filled with at least one wavelength-selective dye with respect to absorption behavior. [9] Artificial eye lens (1) according to claims 7 and 8, characterized by , that in at least one perforation zone (9a) a dye composition is introduced which varies in the radial direction to the principal optical axis (A) with respect to the absorption behavior, in which, with increasing intensity of the incident light, the absorption behavior increases in the radial direction to the principal optical axis (A) when viewed inwards. [10] Artificial eye lens (1) according to any one of the preceding claims, characterized by , that the optical part (2) has a further structure (10) which is formed as a microperforation and at least partially circumferentially around the principal optical axis (A) of the optical part (2), wherein the further structure (10) is formed in the optical part (2) in a first radius interval between 1.5 mm and 2.5 mm to the principal optical axis (A) and / or in a second radius interval between 3.0 mm and 4.0 mm to the principal optical axis (A). [11] Artificial eye lens (1) according to any one of the preceding claims, characterized by , that the structure (7, 8) and / or another structure (9, 10) is / are formed as a laser structure. [12] Method for producing an artificial eye lens (1) according to one of the preceding claims, in which at least one structure (7, 8, 9, 10) is produced with a laser device (11), and a pulsed laser beam with a pulse length between 100 fs and 20 ps, ​​a wavelength between 200 nm and 1100 nm, a pulse repetition rate between 1 kHz and 10 MHz, a focus diameter of less than 5 µm and a power density of greater than 10 8 W / cm 2 is generated and acts on the material of the eye lens (1).

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