System and Method

Abstract

The present invention generally relates to a system for two-photon or multi-photon irradiation of an intraocular lens, preferably an intraocular lens which is preferably arranged in a patient's eye, and to a method for locally adjusting the degree of polarization and / or refractive index of the intraocular lens, preferably an intraocular lens which is preferably arranged in a patient's eye. The method particularly relates to manufacturing optical properties by adjusting the degree of polarization in a non-destructive manner by a two- or multi-photon method.

Description

Field of the Invention

[0001] The present invention generally relates to systems for two - photon or multi - photon irradiation of an intraocular lens, which is preferably an ophthalmic lens and is preferably disposed within a patient's eye, and to methods for locally adjusting the polarization degree and / or refractive index of the intraocular lens, which is preferably an ophthalmic lens and is preferably disposed within a patient's eye. The method particularly relates to manufacturing an optical profile by adjusting the polarization degree in a non - destructive manner by a two - or multi - photon method. Background of the Invention

[0003] The application of light - induced material property changes is used in several technical fields, such as microfabrication, 3D printing, nanostructuring or two - photon lithography. Different ways can occur here, such as photopolymerization, light - induced material degradation or photochemical cross - linking. The result of these methods is a change in the properties of the irradiated material. This can be a change in mechanical properties, solubility, transparency, refractive index or other aspects.

[0004] In 3D printing, typically lithography, femtosecond lasers can be used to polymerize specific arrays. This can be accomplished through a photopolymerization reaction. To make the formulation curable, a photosensitizer can be added. This allows printing with micron resolution, which may not be achievable with ordinary 3D printing techniques. Multi - beam arrays can be used to increase the manufacturing speed.

[0005] Nanostructuring is also used in the biomedical field. In the field of eye care, structuring applications are used to modify ophthalmic polymers (such as contact lenses or intraocular lenses (IOLs)) and eye tissues (for example, see US 2018243082 A1). When dealing with intraocular lenses, generally, photosensitivity in the material is utilized, for example, by absorption of ultraviolet light. Two - or multi - photon processes can allow targeting voxels in the internal material without affecting the IOL surface. When irradiated, the photosensitizer can absorb light and transfer energy to the surrounding material. In WO2017221068 A1, the emitted light provides heat to a hydrogel material. This may lead to polymer degradation and refractive index changes. Another approach is to form non - vision - reducing microcrystals in the material by femtosecond laser irradiation. As shown in US 2010228345 A1, the higher molecular order of the microcrystals can lead to a local increase in density in the material, thus resulting in a local increase in refractive index.

[0006] US2009143858 describes a method for changing the refractive index of an optical polymer material, the method comprising irradiating a selected area of the optical polymer material in a destructive manner with a focused, visible or near-infrared laser having a pulse energy of 0.05 nJ to 1000 nJ such that a refractive optical structure is formed. The refractive optical structure is characterized by a change in refractive index relative to the unirradiated optical polymer material used, exhibiting little or no scattering loss, and showing no significant difference in the Raman spectrum.

[0007] US2016081852 describes a method for changing the refractive properties of an eye, the method comprising applying a photosensitizer to the internal tissue of the eye cornea, the photosensitizer promoting crosslinking of the internal tissue of the cornea, irradiating the cornea to activate a crosslinking agent in the internal tissue of the cornea, and altering the cornea to change the refractive properties of the eye.

[0008] US2008004610 describes a specific refractive index adjustable lens and refractive index measurement during a process by a refractometer. The described adjustment is in a destructive manner.

[0009] Cataract is an opacity of the eye lens that may impede the passage of light. Most cases of cataract are associated with the aging process. However, children may be born with cataract or develop it at a very young age. In addition, cataract may occur after eye injury, inflammation or some other eye diseases. According to the research of the World Health Organization, there are currently more than 50 million people suffering from cataract worldwide, which makes cataract the cause of about half of the blindness cases globally. Although cataract can be removed surgically, surgical services are not available in many countries and cataract remains the leading cause of blindness. With the extension of the average life span, the number of people suffering from cataract is increasing. Therefore, cataract is an important cause of poor vision in both developed and developing countries. The comprehensive prevention of cataract formation is not clear.

[0010] Treating cataract during surgery may successfully restore vision. The opaque lens is removed here and replaced with an intraocular lens.

[0011] The intraocular lens is implanted into the remaining capsular bag as each modern lens through a small incision and after the natural lens is removed, or into the sulcus if the capsular bag is lost.

[0012] A typical problem associated with IOL implantation is that, in most cases, the results obtained are far from optimal in terms of best vision. Before IOL implantation, the biometric data of the eye, including the corneal radius of curvature and the axial length of the eye, cannot be determined with the required precision. The positioning of the IOL during surgery, the unpredictable effects of wound healing, and the postoperative displacement of the IOL that occurs weeks and months after cataract surgery are currently difficult to predict. There are various methods and formulas for predicting IOL refractive power before cataract surgery, but no adequate solution has been found.

[0013] Clinical trials dealing with the results of cataract surgery have shown that more than 80% of patients are within 1 diopter (D) of the required refractive index. However, many have refractive errors and thus require some correction to provide optimized vision. It has been shown that refractive errors after cataract surgery are virtually inevitable, even if the magnitude of the refractive error has been reduced. Problems can also occur if the eye has certain conditions, for example, if the axial length of the eye is significantly longer or shorter than the average. Pediatric cases are generally prone to complications related to refractive power prediction. Intraocular lens power errors due to manufacturing tolerances can also contribute to the overall error, especially for high refractive power IOLs. It is noted that the applicable ISO 11979 standard allows a tolerance of ±0.33 D in the corneal plane for IOLs above 25.00 D and even ±0.66 D for IOLs above 30.00 D.

[0014] Refractive error is defined as an error in the eye's ability to focus light, and it is a common cause of decreased visual acuity. When looking at distant objects, a normal eye has no refractive error.

[0015] An eye with a refractive error when looking at distant objects is said to be ametropic.

[0016] Refractive errors can be divided into spherical and cylindrical. Spherical error occurs when the optical power of the eye is too large or too small to focus light on the retina. Cylindrical error occurs when the curvature is different on two meridians. People with refractive errors have blurred vision.

[0017] Myopia, also known as nearsightedness or short-sightedness, is associated with a refractive defect of the eye where, when the eye is in a relaxed state, collimated light produces an image focus in front of the retina. Myopic people can see nearby objects clearly, while distant objects appear blurred. In the case of myopia, the eyeball is too long, or the cornea is too steep, i.e., the optics are too strong for the length of the eyeball. As a result, the image is focused within the vitreous body inside the eye rather than on the retina.

[0018] Hyperopia, also known as farsightedness or long-sightedness, is related to a vision defect caused by an eye defect. An optical device that is too weak for a specific eye length may cause an inability to focus on nearby objects. In extreme cases, a person may be unable to focus on objects at any distance. As an object moves towards the eye, the eye must increase its refractive power to keep the image in focus on the retina. If the refractive power of the cornea and lens is insufficient, such as in hyperopia, the image will appear blurred.

[0019] Astigmatism is an optical defect in which vision may be blurred because the eye's optical system fails to focus a point object into a sharp focused image on the retina. Irregular or toric curvature of the cornea or lens may be the cause of astigmatism. The degree of curvature refraction of two different meridians is different. In other words, the eye has different foci in different planes. For example, the image may be clearly focused on the retina in the horizontal plane but not in front of the retina in the vertical plane. People may see the outline of a specific direction blurred but can clearly see the outline with a right-angle direction. Patients with astigmatism may have difficulty seeing details. In some cases, a vertical line (such as a wall) may appear tilted to the patient. Astigmatic optics can usually be corrected by glasses, rigid contact lenses, or contact lenses with compensating optics.

[0020] There are approximately six different forms of cataracts, and more than twenty causes that may lead to cataracts have been identified. Therefore, once a cataract is diagnosed, medical treatment is currently impossible. The only current treatment is to replace the natural lens and then implant an artificial IOL. Nowadays, the standard concern is the foldable IOL.

[0021] The IOL can thus be immersed in the fluid of the eye chamber. The diameter of the optically effective part of the IOL is usually between 5 millimeters and a maximum of 7 millimeters. Depending on the specific model, an elastic ring or a stent is connected to the edge of the IOL optical part. These rings are called haptics, which can place the lens in the center of the capsular bag and fix the IOL in place. The total diameter of the artificial lens is about 12 millimeters, and its thickness depends on its refractive power and usually varies between 0.7 millimeters and a maximum of 2 millimeters. The weight of the artificial lens is about 50 milligrams.

[0022] Polymers that can be used to manufacture foldable IOLs can be divided into two groups. The IOLs can be made from (1) acrylates or methacrylates or (2) silicone-based polymers. In addition, hydrophobic and hydrophilic materials can be used for IOLs. The hydrophilic materials can be softened by a water absorption rate of about 10 - 30%, while the hydrophobic materials can be designed to be soft without a water absorption rate. Many IOL variants and many IOLs with different optical properties (such as multifocal, toric, extended depth of focus) have been studied and sold. However, it is currently difficult to determine biometric data with the precision required for IOLs to provide the promised results.

[0023] Examples of silicone-containing polymers that can be used as optical materials are described in WO2018149857.

[0024] Examples of acrylate-containing or methacrylate-containing polymers that can be used as optical materials are described in WO2017032442, WO2017032443, WO2017032444, WO2018149850, WO2018149852, WO2018149853, WO2018149855, and WO2018149856.

[0025] For example, the [2+2] cycloaddition reaction between coumarins can be carried out with light. One coumarin is photo-chemically excited and can react with ground-state molecules within its range. According to the Jablonski diagram, the absorption of photons causes the organic molecule to enter the excited singlet state. This can be converted to the triplet state through intersystem crossing. Compared to the singlet state that can be attenuated by fluorescence reduction, the triplet state can only be attenuated by non-irradiation decay. Therefore, the lifetime of the triplet state in organic molecules such as coumarins is much longer than that of the singlet state. Therefore, for the intermolecular [2+2] cycloaddition reaction of coumarins, the triplet state and its quantity are the most relevant [T. Wolff et al., Phys. Chem. Chem. Phys., 2004, 6, 368 - 376], because its long lifetime allows multiple collisions with other molecules and a high specific mobility resulting in a higher probability of the cyclo-dimerization reaction.

[0026] Accurate prediction of refraction after surgery / surgical treatment is almost impossible, except for errors caused by biometric data measurement. This is mainly due to unpredictable effects that may occur during the healing process in the weeks or months after cataract surgery. These effects include, for example, effects on the anterior chamber depth of the intraocular lens (IOL), i.e., the notional distance between the corneal apex and the effective principal surface of the IOL. In addition, changes in the corneal shape may occur during the healing process. The exact values of these changes can depend on various factors, including the originality of the eye, the type of IOL, and the surgeon and the instruments used. The uncertainty of IOL specifications can also make it difficult to predict the correct refractive coefficient.

[0027] After wound healing, treatment can be applied individually, i.e., adjusting the optical properties of the IOL, or patients receiving IOL treatment may need prescription glasses to achieve ideal vision.

[0028] Alternatively, the patient may need suitable contact lenses to correct the ideal vision of the natural lens.

[0029] Due to the currently insurmountable drawbacks in predicting the refractive power of the IOL before surgery, the aim of the systems and methods according to the present disclosure is to provide a solution for non-invasively adjusting the optical properties of an implanted IOL by changing the degree of polarization of the organic molecules used to manufacture the IOL. In addition, the aim of the systems and methods according to the present disclosure is to provide a solution for preparing and / or modifying an intraocular lens (which may or may not be disposed within the eye of a patient), in particular for modifying the degree of polarization of the IOL, especially by using a two-photon (or generally multi-photon) process.

[0030] Multi-photon excitation is a non-linear phenomenon that requires high intensity to enable the simultaneous absorption of photons. In the case of two-photon excitation, the probability of excitation occurring is proportional to the square of the intensity of the excitation light. On the other hand, the excitation light collected by the microscope objective has an intensity that is inversely proportional to the square of the distance from the focal plane.

[0031] N. Yonezawa et al., Bull. Chem. Soc. Jpn., 1984, 57, 1608 - 1611 described that heat has been shown to cause a thermal ring-opening reaction, which has a negative impact on the yield of the photochemically formed ring dimer. Summary of the Invention

[0033] The present inventors have now found that the above objects can be achieved individually or in any combination by the systems and methods of the present application.

[0034] The present invention relates to a system for irradiating an intraocular lens, the system comprising:

[0035] One or more irradiation sources for irradiating the intraocular lens with a two-photon or multi-photon irradiation beam that is focused by an optical device and has a first wavelength and / or a second wavelength different from the first wavelength,

[0036] A scanner connected to the one or more irradiation sources and configured to scan the irradiation beam across the intraocular lens, and

[0037] An input unit connected to the one or more irradiation sources and the scanner, wherein the input unit is configured to input data for processing the intraocular lens by scanning the irradiation beam across the intraocular lens based on the input data, and

[0038] wherein the first wavelength is between 600 nm and 800 nm to locally reduce the polarization degree of the intraocular lens based on the processing of the intraocular lens, and wherein the second wavelength is between 400 nm and 590 nm to locally increase the polarization degree of the intraocular lens based on the processing of the intraocular lens.

[0039] The present invention further relates to a system for irradiating an intraocular lens preferably disposed in a patient's eye, the system comprising:

[0040] One or more irradiation sources for irradiating the intraocular lens with a two-photon or multi-photon irradiation beam that is focused by an optical device and has a wavelength between 600 nm and 800 nm,

[0041] A scanner connected to the one or more irradiation sources and configured to scan the irradiation beam across the intraocular lens, and

[0042] An input unit connected to the one or more irradiation sources and the scanner, wherein the input unit is configured to input data for processing the intraocular lens by scanning the irradiation beam across the intraocular lens based on the input data, and

[0043] wherein the wavelength locally reduces the polarization degree of the intraocular lens based on the processing of the intraocular lens.

[0044] The present invention further relates to a system for irradiating an intraocular lens preferably disposed in a patient's eye, the system comprising:

[0045] One or more irradiation sources for irradiating the intraocular lens with a two-photon or multi-photon irradiation beam that is focused by an optical device and has a wavelength between 400 nm and 590 nm,

[0046] A scanner, which is connected to the one or more irradiation sources and configured to scan the irradiation beam across the intraocular lens, and

[0047] An input unit, which is connected to the one or more irradiation sources and the scanner, wherein the input unit is configured to input data to process the intraocular lens by scanning the irradiation beam across the intraocular lens based on the input data, and

[0048] wherein the wavelength locally increases the degree of polarization of the intraocular lens based on the processing of the intraocular lens.

[0049] Figure 1 and 2 Show a schematic diagram of the system as described above.

[0050] Figure 1 A schematic diagram of a system for the irradiation of an intraocular lens, such as a contact lens or an intraocular lens disposed within a patient's eye. The irradiation beam (2) emitted by the irradiation source (1) is deflected by the scanner (4) and focused by the optical device (16) for the adjustment of the degree of polarization of the desired intraocular lens (3). The positioning system (20) determines the working position of the in-focus point within the intraocular lens (3). Together with the refractive power and the existing optical characteristics of the intraocular lens (3), the positioning information is part of the input data (8) related to the intraocular lens (3). The lens data (10) and the treatment plan data (12) are further described below. The temperature management unit (14) predicts and / or measures the temperature in the material of the intraocular lens (3) before and / or during irradiation.

[0051] Figure 2 A schematic diagram of a system for the irradiation of an intraocular lens disposed within a patient's eye.

[0052] Figure 2 A schematic diagram of a system for the irradiation of an intraocular lens disposed within a patient's eye. The irradiation beam (2) emitted by the irradiation source (1) is deflected by the scanner (4) and focused by the optical device (16) for the adjustment of the degree of polarization of the desired intraocular lens (3) within the patient's eye, and the optical device (16) is connected to an eye interface system (18) that holds the patient's eye in a fixed position. The positioning system (20) determines the working position of the in-focus point within the intraocular lens (3). Together with the refractive power of the intraocular lens (3) and the existing optical characteristics, the positioning information is part of the input data (8) related to the intraocular lens (3). The lens data (10) and the treatment plan data (12) are further described below. The temperature management unit (14) predicts and / or measures the temperature in the material of the intraocular lens (3) before and / or during irradiation.

[0053] The present invention further relates to a method for adjusting the degree of polarization of an intraocular lens comprising a body formed from a polymeric optical material based on a two- or multi-photon absorption process, the method comprising the steps of:

[0054] providing said lens; and

[0055] adjusting the degree of polarization of said lens by irradiating said lens using a system according to the present invention as described above or preferably as described below, thereby altering the polymeric optical material relative to the unirradiated polymeric optical material of the intraocular lens, having a significant difference in the UV / Vis spectrum.

[0056] The present invention further relates to a method for locally adjusting the degree of polarization of an intraocular lens comprising a polymeric optical material disposed within a patient's eye, the method comprising:

[0057] exposing the intraocular lens to an irradiation beam having a wavelength between 600 nm and 800 nm to locally reduce the degree of polarization of the intraocular lens, or

[0058] exposing the intraocular lens to an irradiation beam having a wavelength between 400 nm and 590 nm to locally increase the degree of polarization of the intraocular lens.

[0059] The present invention still further relates to a method for correcting the vision of a patient by modifying the refractive index of an intraocular lens of the patient's eye, comprising

[0060] confirming and measuring the degree of vision correction of the patient;

[0061] determining the position and type of the refractive structure to be written to the intraocular lens to correct the vision of the patient; and

[0062] subsequently exposing the intraocular lens to two-photon or multi-photon irradiation having a wavelength between 600 nm and 800 nm to locally reduce the degree of polarization of the intraocular lens or exposing the intraocular lens, or

[0063] subsequently exposing the intraocular lens to two-photon or multi-photon irradiation having a wavelength between 400 nm and 590 nm to locally increase the degree of polarization of the intraocular lens.

[0064] The present invention further relates to a kit of components comprising a system as described above or preferably as described below and at least one intraocular lens adapted to said system. Detailed Description of the Invention

[0066] It should be noted that throughout this disclosure, any reference to an entity / component / part of a system being connected to another entity / component / part (and potentially further entities / components / parts) may require an entity / component / part to be directly and / or indirectly connected to another entity / component / part.

[0067] The disclosed lens or intraocular lens is defined as a contact lens or an intraocular lens. The intraocular lens according to the present invention is an implantable lens for replacing the natural lenses of the eye when they are damaged.

[0068] There is no restriction on the type of lens and it may include a contact lens or an intraocular lens. Most preferably, such an intraocular lens is an intraocular lens (IOL), which may be, for example, a posterior chamber intraocular lens or an anterior chamber intraocular lens.

[0069] There is no restriction on the type of intraocular lens. For example, it can be an aphakic intraocular lens or a phakic intraocular lens. The former type replaces the natural lens of the eye, usually replacing a removed cataract lens. The latter type is used to supplement the existing lens and serves as a permanent corrective lens, which is implanted in the anterior chamber or posterior chamber to correct the refractive error of the eye. The intraocular lens to be processed according to the present invention may, for example, include one or more optical components and one or more haptic components, where one or more optical components serve as the lens and one or more haptic components are attached to one or more optical components and fix one or more optical components in the eye. The intraocular lens to be processed according to the present invention can be a one-piece design or a multi-piece design, depending on whether the one or more optical components and the one or more haptic components are formed from a single piece of material (one-piece design) or are made separately and then combined (multi-piece design).

[0070] The intraocular lens, preferably an IOL, may comprise a polymeric optical material, wherein the optical properties of the lens can be non-invasively changed by the system. The system can be used to change the degree of polarization and thus the refractive index, especially based on a multi-photon process.

[0071] Preferably, the intraocular lens (contact lens or IOL) comprises a polymeric optical material as further preferably described below, wherein the optical properties of the IOL can be non-invasively changed by the system.

[0072] Particularly preferably, the intraocular lens (contact lens or IOL) consists of a polymeric optical material as further preferably described below. Typically, the optical properties of the lens are a diameter of 5 mm - 7 mm and a thickness typically between 0.2 mm and 2.0 mm.

[0073] In the present application, the input data is all types of data used to create a treatment plan, which is defined as converting an ophthalmic need into a control command for the writing process, as further described in detail below. During the writing process, an optical pattern is written by irradiation in the intraocular lens.

[0074] The term "control command" refers to a command that directly controls the writing process as previously defined or preferably as described below. The control command can control, for example, the movement of a scanner.

[0075] The term "scanner" used in this specification is not part of the input unit according to the present invention. The "scanner" as described herein is a component of the system according to the present invention that controls the movement of the irradiation beam.

[0076] An ophthalmic need refers to the desired optical characteristics that must be generated in the intraocular lens by the system and method according to the present invention.

[0077] The optical characteristics are the desired changes defined by the surgeon based on the examination results of the patient before or after implanting the intraocular lens; for example, but not limited to, spherical refractive power changes, toric characteristics, EDOF characteristics, or bifocal, trifocal, or multifocal characteristics. Alternatively, the optical characteristics are the optical characteristic adjustments of a contact lens.

[0078] An optical pattern is the necessary change in the degree of polarization that causes a change in the refractive index of each voxel of the intraocular lens.

[0079] The previously defined input data is intended to include common input data, individual input data, or in-process input data.

[0080] Common input data is intended to include general data that is used by default due to system reasons. Examples of such common input data are described below.

[0081] Individual input data is all data specifically related to the ophthalmic need. Examples of such individual input data are described below.

[0082] In-process input data is data created and used during the writing process.

[0083] The term "positioning system" used in this specification determines the position of the laser focus in the eye.

[0084] The term "locating system" used in this specification as part of the positioning system determines the position of the intraocular lens relative to the system and the patient's eye.

[0085] The term "irradiation beam" exit defines the position where the irradiation beam exits the system optics according to the present invention.

[0086] The term "optical device" as used herein as part of a system according to the invention includes all optical equipment required to control the spatial distribution of the irradiation source (focal point) on the intraocular lens. Key parameters of the focal point include the lateral focal size (or beam waist) and the focal length (or Rayleigh range). The optical device includes all elements that determine the focal point along the beam path, such as beam expanders, aperture stops, shutters, and in particular focusing optics, such as microscope objectives or individual aspherical lenses.

[0087] Irradiation within the focal volume creates a refractive optical structure characterized by a change in the degree of polarization / refractive index relative to the body of the intraocular lens or alternatively the non-irradiated portion of the intraocular lens.

[0088] In other words, the change in the degree of polarization / refractive index can be used to form a patterned desired refractive structure in the intraocular lens, as described below or preferably as depicted.

[0089] Preferably, a refractive structure is provided that exhibits a change in refractive index and shows little or no scattering loss, such that ablation, removal, or damage of the intraocular lens material is not observed in the irradiated area. The previously described irradiated area can take the form of two-dimensional or three-dimensional, area or volume-filling refractive structures, which can provide spherical, aspherical, annular, or cylindrical correction. In fact, any optical structure can be formed to produce refractive power correction in two physical directions. Additionally, the optical structures can be vertically stacked or written in separate planes within the artificial lens, which will be further described below for use as a single lens element.

[0090] Multiphoton excitation occurs only near the focal point and is preferably achieved by using ultrashort laser pulses. The average power is limited by the sample damage threshold, which is part of the common input data defined previously and below.

[0091] The system as described previously or preferably below advantageously allows for postoperative and non-invasive adjustment of the optical performance / characteristics of the implanted IOL to correct visual impairments such as refractive errors. Additionally, when manufacturing an intraocular lens (such as a contact lens or, for example, before inserting an intraocular lens into a patient's eye), the system advantageously allows for gentle preparation of the intraocular lens, thereby particularly allowing for the formation of such refractive structures that can provide spherical, aspherical, annular, or cylindrical correction and / or maintain the flexibility of the lens once the lens preparation is complete. The degree of polarization of the artificial lens is modified based on a two-photon (or generally multiphoton) process, which allows for the adjustment of the optical performance / characteristics of the artificial lens or allows for the adjustment of the optical performance in different planes of the artificial lens. Additionally, the modification of the degree of polarization based on a two-photon or multiphoton process allows for improved maintenance of the flexibility of the lens when processed with wavelengths in the range of 400 nm to 590 nm. The intraocular lens is preferably an IOL.

[0092] Criteria for system parameter selection and optimization:

[0093] One ultimate goal of the present invention is to produce local refractive index modification of the IOL after implantation in accordance with a doctor's prescription to improve the patient's visual acuity. A key criterion for the refractive index modification procedure is the total treatment time required to achieve the desired result. It is generally believed that such a procedure should not take more than a few minutes to be considered feasible. Prior art systems capable of local refractive index modification do not include a method for obtaining the actual treatment time for IOL applications.

[0094] Discussion of system trade - offs and limitations:

[0095] In order to be able to adjust a practical high - performance system for an intraocular lens in general or an IOL in particular after implantation, it is recognized that its sub - components must be treated as a system and thus must be jointly optimized because there are many interdependencies and trade - offs between the sub - components. The sub - components include the irradiation source, optics, scanner, and treatment plan.

[0096] A key requirement for any system / parameter optimization is that, in the case of an intraocular lens treated as a contact lens, the lens material remains within safe limits, or in the case of an intraocular lens treated as an IOL, the lens material and the eye and its components (such as the retina) remain within safe limits. These requirements form the basis for the common input data described above. Specifically, two main damage mechanisms of irradiation from an irradiation source (preferably a pulsed laser source) can be distinguished: single - pulse damage (dielectric breakdown and avalanche breakdown), and thermal damage, where the temperature of the lens material and / or the eye is subsequently heated for repeated pulses to the same volume. For example: the average power of a pulsed irradiation source is related to heating and thus to potential damage to the lens material and / or the eye. Therefore, while keeping the average power of the irradiation source below the threshold at which the lens material and / or the eye overheats, the pulse energy and the pulse repetition rate are in an inverse relationship, and the product of the pulse energy and the number of pulses per second ( = the reciprocal of the repetition rate) equals the average power.

[0097] The average power is defined as the pulse energy multiplied by the number of pulses per second and is characterized in watts (W).

[0098] The irradiance is equal to the fluence rate (W / cm 2 )

[0099] The radiation exposure is equal to the fluence (J / cm 2 )

[0100] One overall goal is to minimize the processing time for IOL accommodation after implantation. In theory, increasingly high pulse energies with higher frequency pulses ( = higher repetition rates) could be applied, however, above an average power of typically 1 watt, overheating starts to create unsafe conditions for the IOL material and the retina. Therefore, in order to stay within the safe operating limits while completing the processing of the entire IOL volume within a few minutes, a preferred radiation exposure can be defined. Preferred radiation exposure ≤ 5 kJ / cm 2 , particularly preferably < 1 kJ / cm 2 and very particularly preferably < 0.3 kJ / cm 2 . The radiation exposure thus described also applies to the processes and methods further described below according to the invention.

[0101] For cases where the processing plan is too extensive and would exceed the laser safety limits related to overheating, the processing can be interrupted to cool down all the IOL material and tissue affected by the processing. After cooling, the positioning system can compare the processed voxels in the IOL with the optical pattern and then the processing can be continued.

[0102] The process of adjusting the optical properties / characteristics of the artificial lens will be carried out through the system and according to the requirements as described above according to the processing plan. According to the processing plan, characteristics such as toric, spherical, multifocal or EDOF (extended depth of focus) can be written into the lens. Algorithms can be used to write the characteristics such as toric, spherical, multifocal or EDOF (extended depth of focus) characteristics.

[0103] By combining the information of the desired optical characteristics with common and individual input data, the required optical pattern and the control commands for the irradiation source, optics and scanner of the system as described above or preferably described below can be calculated. Individual input data are for example lens data, such as the laser energy required for a specific refractive index change of each voxel of the artificial lens material, and further patient data, such as the exact position and orientation of the artificial lens in the patient's eye as part of the processing plan data.

[0104] The control commands can be updated and modified during the writing process by, for example, temperature data of the patient's eye obtained by IR temperature measurement, positioning data during the process of the irradiation beam, artificial lens or eye obtained by OCT (optical coherence tomography), and / or refractive data obtained from Scheimpflug images.

[0105] In a further embodiment of the input data, the input data includes lens data of the intraocular lens, preferably the intraocular lens, and / or treatment plan data related to a treatment plan for the treatment of the intraocular lens. For example, the lens data may include data related to the polarization degree and / or refractive index of the intraocular lens as a function of the position of the corresponding volume or portion of the intraocular lens, and one or more of the shape, diopter, cylinder, and sphere and / or its individual aberrations in the dimension. Thus, according to the current polarization degree (or refractive index) and the polarization degree (or refractive index) to be obtained by treatment, the polarization degree can be increased or decreased at a specific position or volume in one or more planes of the intraocular lens.

[0106] Additionally or alternatively, the lens data may include data related to one or more of the following: the dimensions of the intraocular lens (such as diameter and / or thickness), the shape, diopter, cylinder, and sphere and / or its individual aberrations in the dimension, and data related to the material that the intraocular lens, preferably the intraocular lens, comprises.

[0107] Preferably, the lens data includes data related to one or more of the following: the dimensions of the intraocular lens or IOL (such as diameter and / or thickness), or data related to one or more of the following: the polarization degree and / or refractive index of the intraocular lens as a function of the position of the corresponding volume or portion of the intraocular lens, the lens shape, diopter, cylinder, and sphere and / or its individual aberrations in the dimension, and data related to the material that the intraocular lens comprises as part of the input data set.

[0108] The material of the intraocular lens, preferably the material included in the intraocular lens, is described below.

[0109] In some examples, treatment plan calculations can generate control commands that produce one or more treatment plan data, which include: scanning strategy control command data for the scanning of the irradiation beam at the first and / or second wavelength across the intraocular lens (e.g., scanning mode and / or scanning order and / or scanning speed and / or scanning duration of the scanning mode and / or scanning duration of the scanning order and / or pulse duration of the pulse of the irradiation beam at the first and / or second wavelength (e.g., nanosecond or picosecond or femtosecond pulse) and / or irradiation beam characteristics of the irradiation beam at the first and / or second wavelength and / or irradiation (photon) density and / or irradiation intensity and / or irradiation power and / or irradiation wavelength), input data during the process, such as temperature data of the current and / or predicted temperature of the intraocular lens during the exposure, refractive index / depolarization data of the refractive index / depolarization of the intraocular lens obtained based on the exposure, the refractive index / depolarization to be obtained being particularly related to mapping the refractive index / depolarization to be obtained to specific positions / coordinates of the intraocular lens, rupture dimension data of the rupture dimension, and individual input data, such as eye data related to the dimensions and / or shape of the patient's eye, positioning data related to the position and / or orientation of the intraocular lens relative to the eye, and registration data related to the patient identity and / or patient-specific eye.

[0110] Preferably, the scanning strategy control command data of the scanning strategy are the scanning mode and / or scanning speed and / or pulse duration of the pulse and / or irradiation intensity as further described below.

[0111] Then, the parameters of the irradiation beam can be adjusted according to the lens data and / or treatment plan data defined herein, so as to precisely (locally) change the depolarization / refractive index of the intraocular lens when needed.

[0112] Preferably, the parameters of the irradiation beam are adjusted according to the lens data and / or treatment plan data described as before or preferably described herein.

[0113] Those skilled in the art are well aware that when the depth of field (Rayleigh range) of the irradiation beam matches the required thickness of the optical structure of the intraocular lens to be written, the optimal irradiation focusing conditions are achieved.

[0114] Those skilled in the art are well aware that when the depth of field (Rayleigh range) of the irradiation beam matches the local thickness of the intraocular lens, the optimal irradiation focusing conditions will be achieved.

[0115] In a further embodiment, the lens data includes data related to the irradiation absorption properties of the intraocular lens (e.g., absorption and / or light attenuation coefficients, which may depend on the wavelength of light), and wherein the system is configured to adjust the first wavelength and / or the second wavelength for the intraocular lens to locally change the degree of polarization based on a multiphoton absorption process. For example, based on the material of the intraocular lens, a specific wavelength or wavelength range can be input to precisely locally change the degree of polarization of the intraocular lens.

[0116] As part of the system according to the invention as described above and further below, the input unit is configured to input the input data as described above to process the intraocular lens, which can be on a sample holder to process a contact lens, or the intraocular lens can be in a patient's eye for non-invasive adjustment of the intraocular lens.

[0117] Accordingly, the invention further relates to the system as described above or below, wherein the input data includes the lens data of the intraocular lens and / or processing plan data related to the processing plan for the processing of the intraocular lens.

[0118] Accordingly, the invention further relates to the system as described above or below, wherein the lens data includes data related to the irradiation absorption properties of the intraocular lens, and wherein the system is configured to adjust the first wavelength and / or the second wavelength for the intraocular lens to locally change the degree of polarization based on a multiphoton absorption process.

[0119] One or more irradiation sources as part of the system according to the invention may include one or more pulsed lasers, which can be used to generate nanosecond pulses, preferably picosecond pulses and more preferably femtosecond pulses. Preferably, one irradiation source is used. Particularly preferably, the one or more irradiation sources include one or more pulsed lasers for generating femtosecond pulses. Particularly preferably, one pulsed laser is used to generate femtosecond pulses, which is used for irradiation of the system according to the invention or for the processes and methods according to the invention.

[0120] In one embodiment of the invention, the one or more irradiation sources include a laser that is tunable to emit laser beams having first and second wavelengths, respectively. This can be particularly advantageous because, as desired, a single laser can be used to (locally) increase or decrease the degree of polarization / refractive index of the intraocular lens.

[0121] Different types of pulsed lasers are suitable for the illumination source within the system according to the present invention. Both MHz lasers and kHz lasers are suitable and have their specific advantages. For example, while MHz laser systems operate at relatively low pulse energies, for instance, the focused laser spot can be maintained in the μm range (<1 μm to a few μm), and thus can be used for precise local refractive index modification in all three dimensions, e.g., to generate diffraction structures. A preferred MHz illumination source is an 80 MHz laser with a pulse energy range of 0.1 to 10 nJ.

[0122] On the other hand, kHz lasers operate at relatively high pulse energies typically in the range of 0.1 to 10 μJ, and thus require a larger spot size, e.g., 10 to 100 μm, to avoid damaging the lens material. However, the larger laser spot size means a large depth of field (= long Rayleigh range), which can be equal to or even exceed the thickness of the intraocular lens material. For such a long Rayleigh range, it may not be possible to modify the refractive index in the IOL layer by layer, but only uniformly along the lines around the focus. A preferred kHz illumination source is a laser with a repetition rate of 100 to 500 kHz.

[0123] The average power of the illumination source as described above or preferably as previously described is preferably between 300 and 600 mW, particularly preferably between 400 and 500 mW.

[0124] In a further embodiment of the present invention, the same laser source as the illumination source is used by doubling the frequency of the pumping laser or using an optical power amplifier or using another laser source to generate illumination beams with wavelengths respectively exceeding a given range of the first and second wavelengths.

[0125] The illumination source, which is part of the system according to the present invention, preferably comprises a tunable laser that can provide a variable wavelength in the range of approximately 680 - 1080 nm, such as a Ti:sapphire laser (e.g., Chameleon Ultra II, Coherent, Santa Clara, CA, USA). The system may also comprise an optical parametric oscillator (e.g., frequency-doubled Chameleon Compact OPO-Vis, Coherent, Santa Clara, CA, USA).

[0126] The irradiation source, which is part of the system according to the invention, particularly preferably comprises a femtosecond pump laser with an optical parametric amplifier. The pump laser emits irradiation with an average power of >10 W at 1030 nm with <350 fs pulses at a repetition rate of 0.1 to 700 kHz. The irradiation of the pump laser is guided to the optical parametric amplifier, where the pump laser output is frequency-doubled and optically mixed, thereby generating a final tunable output with a wavelength range of 600 nm to 800 nm. The preferred repetition rate is between 50 and 600 kHz. Particularly preferably, the repetition rate is between 100 and 500 kHz.

[0127] The irradiation source, which is part of the system according to the invention, particularly preferably comprises a femtosecond pump laser with an average power of >10 W at 1030 nm in combination with an optical parametric amplifier, which emits <350 fs irradiation pulses at a repetition rate of 1 to 700 kHz. The irradiation of the pump laser is guided to an optical parametric amplifier with one or more second harmonic stages, thereby generating a final optical output with a wavelength range of 400 nm to 590 nm. The preferred repetition rate is between 50 and 600 kHz. Particularly preferably, the repetition rate is between 100 and 500 kHz.

[0128] The types of lasers described above or preferably described previously produce a collimated beam with a diameter of a few millimeters, which is then guided to the optical device and the scanner. The beam quality (measured in terms of M2) is ideally between 1.0 and 1.5, and more ideally between 1.0 and 1.3.

[0129] Multiphoton excitation only occurs near the focus and preferably occurs by using the ultrashort laser pulses described above. The average power is limited by the sample damage threshold, which is part of the common input data defined previously.

[0130] The ideal parameters of the two-photon induced cyclodimerization reaction are related to the relationship between the pulse duration and repetition rate of the system and the characteristic time constants of the intraocular lens material capable of cyclodimerization, as further described or preferably described below. Briefly, they include the molecular S1 state lifetime (about a few ns), the lifetime of the long-lived triplet state (many ns to >μs), and the characteristic thermal diffusion time (about 1 μs).

[0131] Considering the lifetime of the long-lived triplet state, longer pulse intervals are advantageous. The lifetime of the triplet state in the photoactive group (many ns to >μs) is much longer than the repetition rate (12.5 ns) in an 80 MHz system. Therefore, it is advantageous to use the kHz lasers described above or preferably described previously, because most triplet states are cleared before the next pulse is initiated. This effect results in a significant increase in the efficiency of the cyclodimerization reaction of the intraocular lens material, as further preferably described below.

[0132] The temperature rise within the focal point caused by linear absorption indicated by the characteristic thermal diffusion time will relax within one microsecond, about 79 times slower than the separation of a typical ~80 MHz pulse. Thus, the temperature rise is high. This is not the case for kHz pulses. Here, the thermal diffusion time is 9 times faster than the separation of a typical 100 kHz pulse. Thus, with a constant laser energy density illumination, the local temperature rise caused by laser heating is more prominent at higher repetition frequencies.

[0133] The first wavelength of the illumination beam within the system according to the invention is between 600 nm and 800 nm, preferably between 650 nm and 750 nm, more preferably between 670 nm and 720 nm, and even more preferably between 680 nm and 710 nm, in order to (locally) reduce the degree of polarization of the IOL (and thus the refractive index).

[0134] The second wavelength of the illumination beam within the system according to the invention is between 400 nm and 590 nm, preferably between 500 nm and 580 nm, more preferably between 530 nm and 570 nm, in order to (locally) increase the degree of polarization of the IOL (and thus the refractive index).

[0135] Thereby, the degree of polarization can be locally changed particularly precisely.

[0136] Based on (locally) changing the degree of polarization of the intraocular lens, the refractive index of the lens can be (locally) changed. More details of this correlation are described below.

[0137] Typical laser parameters are a wavelength of 680 nm, a pulse duration of 180 fs, and an average power of 500 mW, as described in one of the examples mentioned below.

[0138] The optical device within the system according to the invention:

[0139] The main function of the optical device is to focus the illumination beam emitted from the illumination source and controlled by the scanner onto the intraocular lens. As mentioned above, the key considerations are the spot size and the depth of focus to minimize the processing time while remaining within the limits given by the laser safety requirements and material damage as part of the common input data as mentioned above. The most important characteristics of the optical device are given by its numerical aperture (NA), effective focal length (EFL), and the diameter of the illumination beam at the entrance aperture of the focusing optical device. In addition, all optical elements within the system according to the invention should be selected for diffraction-limited or near-diffraction-limited characteristics so as not to significantly degrade the beam quality.

[0140] Different ophthalmic needs will require different spot sizes, as the spot size determines the achievable spatial resolution. Ideally, the spot size is between 1 and 100 μm, more ideally between 50 and 100 μm, to minimize the processing time while keeping the likelihood of material damage low.

[0141] The scanner within the system according to the invention:

[0142] The scanner used in the system according to the invention can include a Galvano-scanner, a piezoelectric scanner, a rotary scanner, or an acousto-optic modulator, or it can be digital, such as a spatial light modulator, a digital micromirror device, or a stereolithography apparatus. Preferably, the scanner as part of the system according to the described invention is selected from a Galvano-scanner, a piezoelectric scanner, a rotary scanner, an acousto-optic modulator, a spatial light modulator, a digital micromirror device, or a stereolithography apparatus. The preferred Galvano-scanner is a single pivot-point scanner.

[0143] Preferably, the scanner is configured to operate at a scanning speed greater than 50 mm / s. This can allow for a short treatment time to be maintained. As a general rule, the processing time should not exceed a few minutes per treatment session and is preferably less than 10 minutes, preferably less than 5 minutes, and particularly preferably less than 3 minutes.

[0144] The treatment area can be defined as the volume and size of the intraocular lens. Generally, the diameter of the optics of the lens is 5 mm to 7 mm and the thickness is typically between 0.2 mm and 2.0 mm.

[0145] The optimal irradiation exposure is <1 kJ / cm 2 , more ideally <0.3 kJ / cm 2 , to keep the overall irradiation exposure low and the processing time short while addressing the entire volume of the intraocular lens.

[0146] Particularly preferably, a random scan pattern or interlaced scan lines are used to spread the irradiation energy of the irradiation beam.

[0147] Scanning can be performed in three modes. In a bottom-up scan, the laser can travel from one point to another at each point with a specific dwell time ("bottom-up, point-to-point"). Alternatively, in a bottom-up scan, the laser may dwell on overlapping points ("bottom-up, point coverage"). Alternatively, the laser can travel at a fixed speed without dwelling on any point ("fly-over, constant speed"). Figure 3 A schematic diagram (1500) of such a scanning strategy as described above is shown.

[0148] In one embodiment of the scanning mode, the IOL is scanned by irradiating through the pupil using the previously described or preferably the previously described light source. The IOL contained in the capsular bag during scanning is pre-inserted through a corneal incision using a conventional surgical procedure. In such an embodiment, the entire volume of the IOL is scanned and the scanning is performed in a bottom-up manner (i.e., first scanning the portion of the IOL away from the cornea), thus creating optical properties to avoid unnecessary refractive index changes in the optical path.

[0149] As previously mentioned, a key consideration when selecting a scanning procedure is to minimize local heating of the intraocular lens and / or the patient's eye, and thus various variables are used in the scanning procedure. Considering anatomical features (such as rupture and pupil size) and optical features (such as numerical aperture and laser pulse characteristics), a laser program with a specific scanning speed and sequence is created. In such an instance, the relationship between the lens coordinates and the eye coordinate system is automatically considered. Figure 4 A schematic diagram (1600) of the variables used in the scanning procedure as described above when irradiating the lens in the patient's eye is shown.

[0150] The parameters of the scanning procedure and / or treatment plan are preferably the first and second wavelengths, scanning speed and sequence, the positioning of the lens relative to the eye (e.g., in Cartesian coordinates), scanning strategy, refractive index changes to be obtained (optical pattern), numerical aperture of the objective lens, rupture, pupil, and / or the optical diameter of the lens (about 6 mm in some examples), pulse duration of the laser beam (shape, intensity, and x-y positioning), laser safety when operating the laser, and centricity relative to the positioning of the lens and the eye.

[0151] In one embodiment of the system according to the present invention, the photons generated in the laser are preferably guided by a mirror (e.g., optical device 1) to a beam expander, such as preparing a beam for a subsequent scanner and focusing optics. After passing through the beam expander, the photons are directed to a scanner (e.g., a Galvano-scanner or a piezoelectric scanner or a rotary scanner or an acousto-optic modulator, or digitally using a spatial light modulator or a digital micromirror device or a stereolithography apparatus).

[0152] After passing through the scanner, the laser beam passes through another optical device, such as a divider mirror. In such an embodiment, the divider mirror divides the beam into a main imaging beam for intraocular lens irradiation and a beam for monitoring beam characteristics and for positioning feedback. After the divider mirror, the beam is focused onto the intraocular lens by an imaging group or focusing optics. In one embodiment, the imaging group includes a microscope objective to obtain a high numerical aperture (for μm-level spatial resolution) or a low NA optical device to allow a higher pulse energy at the μJ level.

[0153] In yet another embodiment of the system described previously or preferably described previously, the system further includes a microscope objective lens that is connected to the scanner for focusing the irradiation beam onto the intraocular lens through the microscope objective lens, wherein the microscope objective lens has a numerical aperture between 0.1 and 0.8, preferably between 0.2 and 0.5, and more preferably between 0.2 and 0.4. Providing a microscope objective lens with such a numerical aperture can allow for high irradiation beam quality, particularly with respect to the focusing and resolution characteristics of the beam used to treat the intraocular lens.

[0154] The microscope objective lens includes a typical lens configuration to allow, for example, correction of chromatic aberration. The microscope objective lens is preferably connected to an eye interface system, typically an aspiration system that holds the patient's eye in a fixed position as further described below.

[0155] In another embodiment of the objective lens used in the system according to the invention as described previously, the objective lens is an Olympus LUCPLFLN objective lens for focusing the irradiation beam onto the intraocular lens.

[0156] Accordingly, the present invention also relates to a system as described previously, the system further comprising a microscope objective lens connected to the scanner for focusing the irradiation beam onto the intraocular lens through the microscope objective lens, wherein the microscope objective lens has a numerical aperture between 0.1 and 0.8, preferably between 0.2 and 0.5, and more preferably between 0.2 and 0.4.

[0157] An alternative focusing optical device / imaging group is configured with a single aspherical lens, the effective focal length of which is preferably within 50 to 150 mm and the numerical aperture of which is preferably from 0.025 to 0.1.

[0158] Accordingly, the present invention further relates to a system as described previously that further includes a focusing optical device / imaging group configured with a single aspherical lens, the effective focal length of which is preferably within 50 to 150 mm and the numerical aperture of which is preferably from 0.025 to 0.1.

[0159] The system described previously or preferably described previously further includes a positioning system in yet another embodiment for determining the position of the focus of the irradiation beam within the eye of the patient, wherein the positioning system is connected to the scanner and wherein the scanning of the irradiation beam across the intraocular lens by the scanner is based on the position of the focus of the irradiation beam within the eye. The positioning system can include a seeking system, such as an optical coherence tomography system, a confocal microscope, or a Scheimpflug camera. The positioning system can be directly or indirectly connected to the scanner. In some examples of using a confocal microscope, the confocal microscope can be directly connected to the scanner.

[0160] The alignment system as described above is used to provide topographic data of the eye to the positioning system for determining the position of the laser focus based on the eye and the intraocular lens.

[0161] For a confocal microscope, a partially transparent mirror is used for video imaging.

[0162] The system as described above or preferably described previously is preferably further configured to determine the position and / or orientation of the intraocular lens relative to the eye and the exit of the irradiation beam, and wherein the scanning of the irradiation beam across the intraocular lens by the scanner is based on the position and / or orientation of the intraocular lens relative to the eye. This can be particularly advantageous because the position of the intraocular lens may not be concentric relative to the eye, and this misalignment can be taken into account when treating the intraocular lens with the irradiation beam.

[0163] Regarding the position of the IOL, at least two coordinate systems can be considered relevant: the coordinate system of the eye and the coordinate system of the intraocular lens within the eye, because the two may not be centered relative to each other.

[0164] Regarding the position of the intraocular lens, at least two coordinate systems can be considered relevant: the x, y, z coordinates of the eye and the x, y, z coordinates of the intraocular lens within the eye, because the two may not be centered relative to each other.

[0165] In one embodiment, the alignment system creates separate input data. These separate input data include, for example, data on the position and / or orientation of the intraocular lens within the eye and relative to the exit of the laser beam, and / or refractive power maps of the eye and / or the intraocular lens. These data are used for calculating the optical pattern or further processing.

[0166] Furthermore, the alignment system can create input data during the writing process. The input data in these processes include, for example, data on the position and / or orientation of the intraocular lens within the eye and relative to the exit of the laser beam, and / or refractive power maps of the eye and / or the intraocular lens. These data are used to modify the control commands for generating the optical pattern during the process.

[0167] Accordingly, the present invention also relates to a system as described above, which further includes a positioning system for determining the focus position of the irradiation beam within the eye of the patient, wherein the positioning system is connected to the scanner, and wherein the scanning of the irradiation beam across the intraocular lens by the scanner is based on the position of the focus of the irradiation beam within the eye.

[0168] Accordingly, the present invention further relates to a system as described above, wherein the system is configured to determine the position and / or orientation of the intraocular lens relative to the eye and the exit of the irradiation beam, and wherein the scanning of the intraocular lens by the scanner with the irradiation beam is based on the position and / or orientation of the intraocular lens relative to the eye.

[0169] The system as described above or preferably the previously described system further comprises a temperature management unit in a further embodiment, which is connected to (i) one or more irradiation sources and (ii) one or both of the scanners, wherein the temperature management unit is configured to determine the temperature of a part of the intraocular lens during the treatment of the intraocular lens by the scanning based on the irradiation beam performance of the irradiation beam and the intraocular lens performance of the intraocular lens, and wherein the system is configured to control (i) the one or more irradiation sources and (ii) one or both of the scanners based on the determination of the temperature. This allows ensuring that the eye and / or the intraocular lens are not adversely affected based on the treatment with the irradiation beam.

[0170] Furthermore, the temperature management unit is preferably configured to predict the temperature during the treatment of the intraocular lens, and wherein the input data includes the predicted temperature. This can allow taking preventive measures to ensure that the eye and / or the intraocular lens are not adversely affected based on the treatment with the irradiation beam.

[0171] Alternatively, the temperature management unit is an infrared camera that records the eye temperature and correlates the measurement data with general data carrying calibration data to calculate the true temperature in the eye.

[0172] In another embodiment, the temperature dependence of the refractive index is used for temperature control. In these examples, the system includes a diopter mapping device. Based on the deviation of the measured diopter map and the progress of writing the predicted diopter map, the temperature in the lens can be calculated during the process.

[0173] In another embodiment, the temperature dependence of the emission spectrum is used for temperature control. In these examples, the system includes an ultraviolet-visible spectrometer. Based on the deviation of the measured emission peak wavelength and / or peak width, the temperature in the focus can be calculated during the process.

[0174] Accordingly, the present invention also relates to a system as described above, which includes a temperature management unit connected to (i) one or more illumination sources and (ii) one or both of the scanners, wherein the temperature management unit is configured to determine the temperature of a portion of the intraocular lens during the processing of the intraocular lens by the scanning based on the illumination beam characteristics of the illumination beam and the intraocular lens characteristics of the intraocular lens, and wherein the system is configured to control one or both of (i) one or more illumination sources and (ii) the scanners based on the determination of the temperature.

[0175] Accordingly, the present invention further relates to a system as described above, wherein the temperature management unit is configured to predict the temperature during the processing of the intraocular lens, and wherein the input data includes the predicted temperature.

[0176] In another embodiment, the system as described above or preferably previously described further includes an eye interface system configured to hold the eye of the patient in a fixed position. The eye interface system may include a suction system for fixing the position of the patient's eye during the processing.

[0177] The patient can be "docked" to the system in a supine or upright position.

[0178] Accordingly, the present invention also relates to a system as described above, which includes an eye interface system configured to hold the eye of the patient in a fixed position.

[0179] In another embodiment, the system described previously or preferably previously described further includes a wireless or wired receiver and / or transceiver for one or more of the following: (i) sending control commands to one or more illumination sources, (ii) sending control commands to the scanner, and (iii) inputting control command data required to create an optical pattern into the scanner.

[0180] Accordingly, one or more illumination sources and / or scanners can be remotely controlled. Additionally or alternatively, data related to one or both of the lens data and the processing plan data can be stored external to the system and can be provided to the system when needed. In some examples, a wired receiver or transceiver may preferably be provided to at least control one or more illumination sources and / or to control the scanner in order to reduce (or avoid) any delay in sending control signals to one or more illumination sources and / or the scanner.

[0181] In another example, the receiver / transceiver sends the processing plan data and the lens data to a central computing unit, which calculates the optical pattern and sends it back to the receiver as input data, and the receiver provides it to the system.

[0182] In a further embodiment, the system described previously or preferably described previously further comprises means for locally measuring the diopter of the intraocular lens during said processing of the intraocular lens. Adjustment of one or more of the irradiation source, scanner, and input data can be made here during the processing.

[0183] In a further embodiment, the system described previously or preferably described previously further comprises a refractometer for locally measuring the refractive index of the intraocular lens during said processing of the intraocular lens. Adjustment of one or more of the irradiation source, scanner, and input data can be made here during the processing.

[0184] Other components of the system for providing photons are optionally a lid for all the devices built therein, a power unit for providing sufficient energy to the system and all subsystems, and subsystems such as a suction system and / or a refrigerator.

[0185] In addition to the above components, a controller, firmware, and a graphical user interface (GUI) as well as processing algorithms can also be provided. To connect to the system, a connection can be established via Bluetooth, Wi-Fi, or other ports such as RS-232.

[0186] Figure 5 A further schematic view of a system (100) for irradiating an intraocular lens disposed within the eye of a patient (136) is shown. The system (100) generally relates to a laser system that includes at least one femtosecond laser source (102, 104) capable of generating at least one, preferably two different wavelengths. The system (100) further includes focus or Z-shifter optics (106), a scanner (110) (Galvano-scanner, piezoelectric scanner, rotary scanner, acousto-optic modulator, spatial light modulator, digital micromirror device, or stereolithography apparatus), and optics (108) for delivering laser pulses to a predetermined area. The system (100) is capable of achieving the same level of energy delivery to a target area of a polymeric material that includes photoactive units forming an intraocular lens disposed within the eye of a patient (136). The system also includes an eye interface (112) for fixing the eye of the patient (136). In Figure 5 also Figure 5In this case, the laser system is connected to a computer controller (116) incorporating the corresponding device firmware (118) and a front-end graphical user interface (GUI) (120). An algorithm (122) is used to calculate the energy level delivered to a target area of a polymeric material that contains the photo-chemically active units for forming the intraocular lens in the treatment planning system. System parameters and process treatment plans (134) are monitored via the GUI (120). Inputs and adjustments from the patient (136), such as lens data (130) and refractive shaping plans (132), can be entered via the GUI (120). The laser source, subsystems, and body fixture (124) can be integrated into a single module that is connected to a power supply (126) sealed with a lid (128).

[0187] Figure 6 and Figure 7 shows a schematic diagram of the components of a system according to the invention described herein.

[0188] In Figure 6 the example, photons generated in the irradiation source (202) are directed by mirrors (optical system 1, such as a beam shaper (204), a focus shifter / Z-shifter (206)) to a scanner (208) (e.g., a Galvano-scanner or a piezo-scanner or a rotary scanner or an acousto-optic modulator or a digital spatial light modulator SLM). Connected to the scanner (208) are a microscope objective (optical system 2) and a patient interface (210).

[0189] As Figure 7 shown, the Z-shifter (302) includes a first lens (304), a second lens (306), and a third lens (308). The irradiation beam then travels to a scanner (310) that includes a plurality of mirrors (312), (314), and (316) that allow changing the position of the irradiation beam on the IOL in the x-y direction. After passing through the scanner (310), the irradiation beam passes through a beam splitter (318) for imaging before passing through an imaging group (320). The system also includes an illumination unit (322) and a patient interface (324).

[0190] The present application further describes a method for modulating the degree of polarization of an intraocular lens based on a two- or multi-photon absorption process in a body formed of a polymeric optical material (preferably at one or more specific locations of the lens), the method comprising the steps of: providing the lens; and modulating the degree of polarization of the lens by using the system described herein or preferably throughout the present disclosure, thereby altering the polymeric optical material relative to the unirradiated polymeric optical material of the intraocular lens, having a significant difference in the UV / Vis spectrum. The intraocular lens preferably comprises a contact lens or IOL of the polymeric optical material described herein or preferably as described below. The method for modulating the degree of polarization according to the present invention as described above or preferably as described below is carried out in a non-destructive manner on the intraocular lens material.

[0191] The ultraviolet-visible spectrum or ultraviolet-visible spectrophotometry (UV-Vis or UV / Vis) is known to those skilled in the art. It refers to the absorption spectrum or reflection spectrum of a portion of ultraviolet light and the complete adjacent visible spectral region. Suitable UV / Vis spectrometers are commercially available. The choice of the UV / Vis spectrometer is not critical for the comparison of the UV / Vis spectrum of the initial intraocular lens with the UV / Vis spectrum of the irradiated intraocular lens prepared according to the present invention. As long as both measurements are carried out under comparable conditions so that the results can be compared, this is known to those skilled in the art. A suitable spectrometer is the UV / Vis spectrometer Lambda 900 from Perkin Elmer.

[0192] In some examples, the intraocular lens can then be subsequently introduced into the eye of a patient. In some examples, the lens can comprise an intraocular lens such that the degree of polarization of the lens can be modulated when the lens is disposed within the eye of the patient.

[0193] In the foregoing method, the modulation of the degree of polarization of the intraocular lens comprises reducing the degree of polarization by irradiating the intraocular lens with an irradiation beam having a wavelength between 600 nm and 800 nm, thereby altering the polymeric optical material relative to the unirradiated polymeric optical material of the intraocular lens, having a significant difference in the UV / Vis spectrum, namely a peak absorption loss in the range of 300 nm - 400 nm.

[0194] Accordingly, the present invention further relates to the method as described above, wherein the modulation of the degree of polarization of the intraocular lens comprises reducing the degree of polarization by irradiating the intraocular lens with an irradiation beam having a wavelength between 600 nm and 800 nm, thereby altering the polymeric optical material relative to the unirradiated polymeric optical material of the intraocular lens, having a significant difference in the UV / Vis spectrum, namely a peak absorption loss in the range of 300 nm - 400 nm.

[0195] In the foregoing method, the adjustment of the degree of polarization of the intraocular lens includes increasing the degree of polarization by irradiating the intraocular lens with an irradiation beam having a wavelength between 400 nm and 590 nm, thereby changing the polymer optical material relative to the unirradiated polymer optical material of the intraocular lens, with a significant difference in the UV / Vis spectrum, namely an increase in the peak absorption in the range of 300 nm - 400 nm.

[0196] Accordingly, the present invention further relates to the method as described above, wherein the adjustment of the degree of polarization of the intraocular lens includes increasing the degree of polarization by irradiating the intraocular lens with an irradiation beam having a wavelength between 400 nm and 590 nm, thereby changing the polymer optical material relative to the unirradiated polymer optical material of the intraocular lens, with a significant difference in the UV / Vis spectrum, namely an increase in the peak absorption in the range of 300 nm - 400 nm.

[0197] Accordingly, the present invention further relates to a method for adjusting the degree of polarization of an intraocular lens based on a two - or multi - photon absorption process, which includes a body formed of a polymer optical material (preferably at one or more specific positions of the lens), the method comprising the steps of:

[0198] Providing the lens; and

[0199] Adjusting the degree of polarization of the lens by using a system comprising:

[0200] One or more irradiation sources for two - photon or multi - photon irradiating the intraocular lens with an irradiation beam having a first wavelength and / or a second wavelength different from the first wavelength, focused by an optical device,

[0201] A scanner connected to the one or more irradiation sources and configured to scan the irradiation beam across the intraocular lens, and

[0202] An input unit connected to the one or more irradiation sources and the scanner, wherein the input unit is configured to input data for processing the intraocular lens by scanning the irradiation beam across the intraocular lens based on the input data, and

[0203] Wherein the first wavelength is between 600 nm and 800 nm to locally reduce the degree of polarization of the intraocular lens based on the processing of the intraocular lens, thereby changing the polymer optical material relative to the unirradiated polymer optical material of the intraocular lens, with a significant difference in the UV / Vis spectrum, namely a loss of peak absorption in the range of 300 nm - 400 nm, and

[0204] Wherein the second wavelength is between 400 nm and 590 nm to locally increase the degree of polarization of the intraocular lens based on the treatment of the intraocular lens, thereby changing the polymer optical material relative to the unirradiated polymer optical material of the intraocular lens, having a significant difference in the UV / Vis spectrum, namely an increase in peak absorption in the range of 300 nm - 400 nm.

[0205] The specific wavelength for reducing and / or increasing the degree of polarization of an intraocular lens may depend on which specific material or composition can be used for the intraocular lens. Any one or more of the polymer optical materials described in the present disclosure can be used to fabricate and / or provide the lens.

[0206] Special polymers as described below are preferably used, which are suitable for manufacturing intraocular lenses, preferably IOLs. By virtue of their ability to change the degree of polarization and thereby the refractive index when a two - photon or multi - photon process is applied, their optical properties can be changed later (non - invasively).

[0207] The special polymers as described below are preferably processed with the system according to the present invention and / or preferably used in the method according to the present invention.

[0208] The two - photon or multi - photon process is generated by using the system described in detail previously.

[0209] The region of the applicable wavelength of the irradiation source, preferably in the range of 600 nm - 800 nm of the pulsed laser as described above, preferably 650 nm - 750 nm, particularly preferably 670 nm - 720 nm and very particularly preferably 680 - 710 nm, thereby reducing the degree of polarization of the intraocular lens and thereby reducing the refractive index.

[0210] The region of the applicable wavelength of the irradiation source, preferably in the range of 400 nm - 590 nm of the pulsed laser as described above, preferably 500 nm - 580 nm, and particularly preferably 530 nm - 570 nm, thereby increasing the degree of polarization of the intraocular lens and thereby increasing the refractive index.

[0211] Thus, the degree of polarization can be changed locally with particular precision.

[0212] Hereinafter, the optical material of the intraocular lens for the method according to the present invention, preferably the polymer optical material of a contact lens or IOL, is further and preferably described for the following wavelength regions: 600 nm - 800 nm, preferably 650 nm - 750 nm, particularly preferably 670 nm - 720 nm and very particularly preferably 680 - 710 nm to locally reduce the degree of polarization of the material.

[0213] To apply such an adjustment, the refractive index of the polymer optical material ranges from 1.45 to 1.60.

[0214] The polymeric optical material of an intraocular lens (contact lens or IOL) may optionally contain an ultraviolet light blocker or a blue light absorber.

[0215] The polymeric optical material of the intraocular lens for performing the adjustment according to the method of the present invention comprises a polymer matrix, which polymer matrix comprises covalently bound photoactive units, preferably in an amount of at least 2 wt% - 100 wt%, preferably 5 wt% - 90 wt%, most preferably 7 wt% - 80 wt%.

[0216] The photoactive units within the polymer matrix may be the same or different.

[0217] The polymer matrix of the polymeric optical material of the intraocular lens and / or IOL for the adjustment may be a matrix obtained from a homopolymer or a copolymer, preferably a copolymer.

[0218] The polymer matrix comprising photoactive units may be a matrix obtained from a silicone-containing polymer, an acrylic polymer, a methacrylic polymer or a mixture thereof.

[0219] A photoactive unit refers to a photochemically active unit that is photochemically active in the applicable wavelength region described above or preferably previously described under the effect of a two-photon or multi-photon process.

[0220] The photoactive unit preferably comprises non-aromatic double bonds, preferably carbon-carbon double bonds, which are capable of dimerizing by forming a cyclobutane ring through [2π + 2π] cycloaddition under the effect of a two-photon or multi-photon process.

[0221] Accordingly, the present invention further relates to a method for adjusting the degree of polarization of an intraocular lens comprising a body formed of a polymeric optical material (preferably at one or more specific locations of the lens), wherein the optical material of the intraocular lens comprises a polymer matrix, which polymer matrix comprises covalently bound photoactive units, which photoactive units comprise non-aromatic double bonds, preferably carbon-carbon double bonds, which are capable of dimerizing by forming a cyclobutane ring through [2π + 2π] cycloaddition under the effect of a two-photon or multi-photon process. In such an embodiment, the photoactive units within the polymeric optical material of the intraocular lens for the method according to the present invention may be the same or different, but are the only photoactive units in the polymeric optical material, and are all classified in that they comprise non-aromatic double bonds, preferably carbon-carbon double bonds, which are capable of dimerizing by forming a cyclobutane ring through [2π + 2π] cycloaddition under the effect of a two-photon or multi-photon process as described above or further preferably as described below.

[0222] Alternatively, the polymer matrix comprises the photoactive units as described before or hereinafter together with the photoactive units that have dimerized. Thus, the polymer matrix can still comprise photoactive units capable of dimerizing. The polymeric optical material (polymer matrix) can be partially dimerized.

[0223] In said embodiments of the optical material of an intraocular lens for use in the method according to the invention, preference is given to the polymeric optical material of a contact lens or IOL, such materials can be irradiated with light in the first or second region of the wavelength as described before to reduce or increase the polarization of the intraocular lens comprising said polymeric optical material and thereby reduce or increase the refractive index. With such a polymeric optical material, the polarization of the intraocular lens can be adjusted.

[0224] Accordingly, the present invention further relates to a method of adjusting the polarization (preferably at one or more specific locations of the lens) of an intraocular lens comprising a body formed from a polymeric optical material, wherein the optical material of the intraocular lens comprises a polymer matrix, the polymer matrix comprises covalently bound photoactive units, the photoactive units comprise non-aromatic double bonds, preferably carbon-carbon double bonds, which are capable of dimerizing by [2π+2π] cycloaddition to form a cyclobutane ring together with the photoactive units that have dimerized under the effect of a two-photon or multi-photon process. In such an embodiment, the photoactive units in the polymeric optical material of the intraocular lens for use in the method according to the invention can be the same or different, but are the only photoactive units in the polymeric optical material, and are all classified in that they comprise non-aromatic double bonds, preferably carbon-carbon double bonds, which are capable of dimerizing by [2π+2π] cycloaddition to form a cyclobutane ring under the effect of a two-photon or multi-photon process as described before or further preferably hereinafter or the photoactive units are their dimerized photoactive units.

[0225] The photoactive units in the polymeric optical material of the intraocular lens for use in the method according to the invention particularly preferably comprise non-aromatic carbon-carbon double bonds conjugated to at least one aromatic ring system, which are capable of dimerizing by [2π+2π] cycloaddition to form a cyclobutane ring under the effect of a two-photon or generally multi-photon process.

[0226] Preferably, the non-aromatic double bond and the aromatic ring system conjugated to the non-aromatic double bond form a fused ring system as part of the photoactive unit as described before, preferably a bicyclic or tricyclic ring system, particularly preferably a bicyclic ring system.

[0227] Examples of polycyclic ring systems conjugated with non-aromatic carbon double bonds as part of the photoactive unit within the polymeric optical material for an intraocular lens according to the method of the present invention are chromene-2-one, chromene-2-thione, thiochromene-2-one, thiochromene-2-thione, quinolin-2-one, quinolin-2-thione, benz[b]furan, benz[b]thiophene, benz[b]pyrrole, indene, 1,2-dihydronaphthalene, 6,7-dihydro-5H-benz[7]annulene, (Z)-5,6,7,8-tetrahydrobenz[8]annulene.

[0228] [2π+2π] cycloaddition can be visualized according to Scheme 1 below. Figure 8 The specific [2π+2π] cycloaddition reaction of poly(M-14) is shown; the representative material will be further described in Examples 1 and 2. Scheme 1 further visualizes ring cleavage. Figure 9 The cleavage of a specific poly(M-14)-dimer by ring cleavage is shown, which is further described in Examples 3 and 5.

[0229] Scheme 1:

[0230]

[0231] R p refers to a polymer / copolymer backbone covalently linked to the polycyclic ring system via a linker;

[0232] X'-X' are independently of each other CH=CH, CR'=CH, CH=CR' or CR'=CR';

[0233] Y' is O, S, NR', CH2, CHR', C(R')2;

[0234] In the case where Y' is O, S or NR', m is 1, and in the case where Y' is independently selected from CH2, CHR' and C(R')2 at each occurrence, m is 1, 2, 3 or 4;

[0235] Z' is C=O or C=S;

[0236] n is 0 or 1

[0237] R' is an organic substituent.

[0238] Examples of silicone-containing polymers that can be used as the optical material for an intraocular lens according to the method of the present invention are described in WO2018149857.

[0239] Examples of acrylate or methacrylate-containing polymers that can be used as the optical material of the intraocular lens for the method according to the invention are described in WO2017032442, WO2017032443, WO2017032444, WO2018149850, WO2018149852, WO2018149853, WO2018149855, WO2018149856.

[0240] All references are incorporated herein by reference.

[0241] In a preferred embodiment of the invention, the polymeric optical material comprises a polymer matrix that comprises covalently bound photoactive units for use in an intraocular lens for the method according to the invention, and the polymeric optical material contains polymerized monomers according to formula (1)

[0242]

[0243] where the symbols used are as follows:

[0244] u is 0 or 1,

[0245] Y is the same or different in each occurrence and is O, S, NR 0 or X 1 ,

[0246] X 1 is CH2, CHR 0 , C(R 0 )2, [CH2]2, [CHR 0 2, [C(R 0 )2]2, [CH2]3, [CHR 0 3, [C(R 0 )2]3, [CH2]4, [CHR 0 4 or [C(R 0 )2]4;

[0247] Z is the same or different in each occurrence and is O or S;

[0248] X1 is O, S or SO2;

[0249] a is 0 or 1;

[0250] Sp is an alkanediyl, alkenediyl or alkynediyl, which may be substituted by one or more R groups;

[0251] R 0 is a straight-chain or branched alkyl having 1-10 C atoms;

[0252] R 1 , R2 , R 3 and R 4 are each independently selected from H, F, Cl, Br, I, a straight-chain or branched alkyl having 1 - 20 C atoms, a partially or fully halogenated straight-chain or branched alkyl having 1 - 20 C atoms, and an aryl or heteroaryl having 5 - 40 ring atoms;

[0253] R 5 , R 6 , R 7 , R 8 and R 9 are each independently selected, in each occurrence, from F, a straight-chain or branched, non-halogenated, partially or fully halogenated alkyl having 1 - 20 C atoms, a non-halogenated, partially or fully halogenated cycloalkyl having 3 - 6 C atoms, a straight-chain or branched, non-halogenated, partially or fully halogenated alkoxy having 1 - 20 C atoms, and a straight-chain or branched, non-halogenated, partially or fully halogenated thioalkyl having 1 - 20 C atoms;

[0254] X 11 is selected from O, S, O - SO2, SO2 - O, C(=O), OC(=O), C(=O)O, S(C=O), and (C=O)S;

[0255] c is 0 or 1;

[0256] R 10 , R 11 , R 12 are each independently selected from H, F, a straight-chain or branched alkyl having 1 - 20 C atoms that may be partially or fully halogenated, and an aryl having 6 - 14 C atoms;

[0257] R is the same or different in each occurrence and is selected from F, OH, a straight-chain or branched alkyl having 1 - 10 C atoms, a straight-chain or branched, partially or fully halogenated alkyl having 1 - 10 C atoms, a straight-chain or branched alkoxy having 1 - 10 C atoms, and a straight-chain or branched, partially or fully halogenated alkoxy having 1 - 10 C atoms.

[0258] In a preferred embodiment of the present invention, the polymeric optical material comprises a polymer matrix containing covalently bound photoactive units of an intraocular lens to be used in the method according to the present invention, and the polymeric optical material contains a polymerized monomer according to formula (2)

[0259]

[0260] where the symbols used are as follows:

[0261] u is 0 or 1,

[0262] Y is the same or different at each occurrence and is O, S, NR 0 or X 1 ,

[0263] X 1 is CH2, CHR 0 , C(R 0 )2, [CH2]2, [CHR 0 2, [C(R 0 )2]2, [CH2]3, [CHR 0 3, [C(R 0 )2]3, [CH2]4, [CHR 0 4 or [C(R 0 )2]4;

[0264] Z is the same or different at each occurrence and is O or S;

[0265] X1 is O, S or SO2;

[0266] a is 0 or 1;

[0267] Sp is an alkanediyl, alkenediyl or alkynediyl, which may be substituted by one or more R groups;

[0268] R 0 is a straight-chain or branched alkyl having 1 - 10 C atoms;

[0269] R 1 , R 2 , R 3 and R 4 are independently selected from H, F, Cl, Br, I, a straight-chain or branched alkyl having 1 - 20 C atoms, a partially or fully halogenated straight-chain or branched alkyl having 1 - 20 C atoms, and an aryl or heteroaryl having 5 - 40 ring atoms;

[0270] R 5 , R 6 , R 7 , R 8 and R 9 are independently selected at each occurrence from F, a straight-chain or branched, non-halogenated, partially or fully halogenated alkyl having 1 - 20 C atoms, a non-halogenated, partially or fully halogenated cycloalkyl having 3 - 6 C atoms, a straight-chain or branched, non-halogenated, partially or fully halogenated alkoxy having 1 - 20 C atoms and a straight-chain or branched, non-halogenated, partially or fully halogenated thioalkyl having 1 - 20 C atoms, provided that

[0271] R 5 , R 6 , R7 , R 8 or R 9 One of them corresponds to formula (2-1), where * represents connection to the rest of formula (2).

[0272]

[0273] R 10 , R 11 , R 12 They are independently selected from H, F, straight-chain or branched alkyl groups having 1 - 20 C atoms which may be partially or fully halogenated, and aryl groups having 6 - 14 C atoms;

[0274] X 11 is selected from O, S, O - SO2, SO2 - O, C(=O), OC(=O), C(=O)O, S(C=O) and (C=O)S;

[0275] c is 0 or 1;

[0276] R is the same or different each time it appears, and is selected from F, OH, straight-chain or branched alkyl groups having 1 - 10 C atoms, straight-chain or branched alkyl groups having 1 - 10 C atoms which are partially or fully halogenated, straight-chain or branched alkoxy groups having 1 - 10 C atoms, and straight-chain or branched alkoxy groups having 1 - 10 C atoms which are partially or fully halogenated.

[0277] Halogenation means preferably fluorination, chlorination or bromination, particularly preferably fluorination.

[0278] Straight-chain or branched alkyl groups having 1 - 10 C atoms mean alkyl groups having 1, 2, 3, 4, 5, 6, 7, 8, 9 or 10 C atoms, such as methyl, ethyl, isopropyl, n-propyl, isobutyl, n-butyl, tert-butyl, n-pentyl, 1-, 2- or 3-methylbutyl, 1,1-, 1,2- or 2,2-dimethylpropyl, 1-ethylpropyl, n-hexyl, n-heptyl, n-octyl, ethylhexyl, n-nonyl or n-decyl. Straight-chain or branched alkyl groups having 1 - 20 C atoms include all examples of straight-chain or branched alkyl groups having 1 - 10 C atoms, including any alkyl groups having 11, 12, 13, 14, 15, 16, 17, 18, 19 and 20 C atoms, such as n-undecyl, n-dodecyl, n-tridecyl, n-tetradecyl, n-pentadecyl, n-hexadecyl, n-heptadecyl, n-octadecyl, n-nonadecyl and n-eicosyl.

[0279] The term partially halogenated alkyl means that at least one H atom of the alkyl group is replaced by F, Cl, Br or I. Preferably, the alkyl group is partially fluorinated, meaning that at least one H atom of the alkyl group is replaced by F.

[0280] The term fully halogenated alkyl means that all H atoms of the alkyl are replaced by F, Cl, Br and / or I. Preferably, the alkyl is fully fluorinated, meaning that all H atoms of the alkyl are replaced by F. A preferred fully fluorinated alkyl is trifluoromethyl.

[0281] The term halogenated or preferably fluorinated also corresponds to other groups, such as halogenated cycloalkyl, halogenated alkoxy or halogenated thioalkyl.

[0282] Cycloalkyl having 3 - 6 C atoms includes cyclopropyl, cyclobutyl, cyclopentyl and cyclohexyl, which may be partially or fully halogenated or fluorinated as described above.

[0283] Straight-chain or branched alkoxy having 1 - 20 C atoms means O-alkyl having 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19 or 20 C atoms, such as methoxy, ethoxy, isopropoxy, n-propoxy, isobutoxy, n-butoxy, tert-butoxy, n-pentyloxy, 1-, 2- or 3-methylbutoxy, 1,1-, 1,2- or 2,2-dimethylpropoxy, 1-ethylpropoxy, n-hexyloxy, n-heptyloxy, n-octyloxy, ethylhexyloxy, n-nonyloxy, n-decyloxy, n-undecyloxy, n-dodecyloxy, n-tridecyloxy, n-tetradecyloxy, n-pentadecyloxy, n-hexadecyloxy, n-heptadecyloxy, n-octadecyloxy, n-nonadecyloxy and n-icosyloxy, which may be partially or fully halogenated or preferably may be partially or fully fluorinated. A preferred fully fluorinated alkoxy is trifluoromethoxy.

[0284] A straight-chain or branched thioalkyl having 1 to 20 C atoms means an S-alkyl having 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19 or 20 C atoms, such as thiomethyl, 1-thioethyl, 1-thio-isopropyl, 1-thio-n-propyl, 1-thio-isobutyl, 1-thio-n-butyl, 1-thio-tert-butyl, 1-thio-n-pentyl, 1-thio-1-, -2- or -3-methylbutyl, 1-thio-1,1-, -1,2- or -2,2-dimethylpropyl, 1-thio-1-ethylpropyl, 1-thio-n-hexyl, 1-thio-n-heptyl, 1-thio-n-octyl, 1-thio-ethylhexyl, 1-thio-n-nonyl, 1-thio-n-decyl, 1-thio-n-undecyl, 1-thio-n-dodecyl, 1-thio-n-tridecyl, 1-thio-n-tetradecyl, 1-thio-n-pentadecyl, 1-thio-n-hexadecyl, 1-thio-n-heptadecyl, 1-thio-n-octadecyl, 1-thio-n-nonadecyl and 1-thio-n-eicosyl, which may be partially or completely halogenated or preferably may be partially or completely fluorinated. A preferred fully fluorinated thioether group is trifluoromethylthioether.

[0285] Preferred alkyl and alkoxy groups have 1, 2, 3, 4, 5, 6, 7, 8, 9 or 10 C atoms.

[0286] An aryl in the context of the present invention contains 6 to 40 ring atoms, and a heteroaryl in the context of the present invention contains 5 to 40 ring atoms, which contains at least one heteroatom. The heteroatom is preferably selected from N, O and / or S. An aryl or heteroaryl here means a simple aromatic ring, i.e., phenyl, or a simple heteroaromatic ring, such as pyridyl, pyrimidinyl, thiophenyl, etc., or a fused (anellated) aryl or heteroaryl, such as naphthyl, anthracenyl, phenanthryl, quinolinyl or isoquinolinyl.

[0287] The aryl or heteroaryl is preferably derived from benzene, naphthalene, anthracene, phenanthrene, pyrene, benzanthracene, , perylene, fluoranthene, tetracene, pentacene, benzopyrene, biphenyl, biphenylene, terphenyl, benzo[a]pyrene, fluorene, spirobifluorene, dihydrophenanthrene, dihydropyrene, tetrahydropyrene, cis- or trans-indeno[1,2-b]fluorene, cis- or trans-indeno[2,3-b]carbazole, cis- or trans-indolo[2,3-b]carbazole, triphenylene, isotriphenylene, spirotriphenylene, spiroisotriphenylene, furan, benzofuran, isobenzofuran, dibenzofuran, thiophene, benzothiophene, isobenzothiophene, dibenzothiophene, pyrrole, indole, isoindole, carbazole, pyridine, quinoline, isoquinoline, acridine, phenanthridine, benzo[5,6]quinoline, benzo[6,7]quinoline, benzo[7,8]quinoline, phenothiazine, phenoxazine, pyrazole, indazole, imidazole, benzimidazole, naphthimidazole, phenanthrimidazole, pyridinimidazole, pyrazinimidazole, quinoxalinimidazole, oxazole, benzoxazole, naphthoxazole, anthroxazole, phenanthroxazole, isoxazole, 1,2-thiazole, 1,3-thiazole, benzothiazole, pyridazine, hexaazatriphenylene, benzopyridazine, pyrimidine, benzopyrimidine, quinoxaline, 1,5-diazaphenanthrene, 2,7-diazapyrene, 2,3-diazapyrene, 1,6-diazapyrene, 1,8-diazapyrene, 4,5-diazapyrene, 4,5,9,10-tetraazaperylene, pyrazine, phenazine, phenoxazine, phenothiazine, fluoranthene ring, naphthyridine, azacarbazole, benzocarbazole, phenanthroline, 1,2,3-triazole, 1,2,4-triazole, benzotriazole, 1,2,3-oxadiazole, 1,2,4-oxadiazole, 1,2,5-oxadiazole, 1,3,4-oxadiazole, 1,2,3-thiadiazole, 1,2,4-thiadiazole, 1,2,5-thiadiazole, 1,3,4-thiadiazole, 1,3,5-triazine, 1,2,4-triazine, 1,2,3-triazine, tetrazole, 1,2,4,5-tetrazine, 1,2,3,4-tetrazine, 1,2,3,5-tetrazine, purine, pteridine, indolizine and benzothiadiazole.

[0288] An aryl group having 6 - 14 C atoms, preferably an aryl group, is selected from phenyl, naphthyl or anthryl, and particularly preferably phenyl.

[0289] In a particularly preferred embodiment of the present invention, the polymeric optical material comprises a polymer matrix containing covalently bonded photoactive units of an intraocular lens to be used in the method according to the present invention, and the polymeric optical material contains a polymerized monomer according to formula (3).

[0290]

[0291] where X1, a, R 5 -R 9 and R 10 -R 12 have the meanings as described above.

[0292] In a particularly preferred embodiment of the present invention, the polymeric optical material comprises a polymer matrix containing covalently bound photoactive units of an intraocular lens to be used in the method according to the present invention, and the polymeric optical material contains polymerized monomers according to formula (4),

[0293]

[0294] wherein

[0295] u is 0, Y is X 1 , X 11 is selected from O-SO2, SO2-O, OC(=O), C(=O)O, S(C=O) and (C=O)S, c is 1,

[0296] and X 1 , X1, a, Sp, R 0 , R 1 , R 2 , R 3 , R 4 , R 5 , R 6 , R 7 , R 8 , R 9 , R 10 , R 11 , R 12 , and R has the meanings as described above.

[0297] In a particularly preferred embodiment of the present invention, the polymeric optical material comprises a polymer matrix containing covalently bound photoactive units of an intraocular lens to be used in the method according to the present invention, and the polymeric optical material contains polymerized monomers according to formula (5),

[0298]

[0299] wherein

[0300] u is 0, Y is X 1 , X 11 is selected from, O-SO2, SO2-O, OC(=O), C(=O)O, S(C=O) and (C=O)S, c is 1,

[0301] and X 1 , X1, a, Sp, R 0 , R 1 , R 2 , R 3 , R 4 , R 5 , R 6 , R 7 , R 8 , R9 , R 10 , R 11 , R 12 , and R has the meaning as described above.

[0302] For a compound according to formula (1) or (3), R 5 , R 6 , R 7 , R 8 and R 9 are preferably independently of one another selected from H, F, Cl, Br, I, a straight-chain or branched alkyl having 1 - 20 C atoms, a straight-chain or branched alkoxy having 1 - 20 C atoms, a partially or fully halogenated straight-chain or branched alkyl having 1 - 20 C atoms, a partially or fully halogenated straight-chain or branched alkoxy having 1 - 20 C atoms, and an aryl or heteroaryl having 5 - 40 ring atoms, where at least one of the groups selected from R 5 -R 9 is a straight-chain or branched alkyl or alkoxy having 1 - 20 C atoms, which may be partially or fully halogenated.

[0303] For a compound according to formula (2), (4) or (5), R 5 , R 6 , R 7 , R 8 and R 9 are preferably independently of one another selected from H, F, Cl, Br, I, a straight-chain or branched alkyl having 1 - 20 C atoms, a straight-chain or branched alkoxy having 1 - 20 C atoms, a partially or fully halogenated straight-chain or branched alkyl having 1 - 20 C atoms, a partially or fully halogenated straight-chain or branched alkoxy having 1 - 20 C atoms, and an aryl or heteroaryl having 5 - 40 ring atoms.

[0304] In the compounds of formula (1), (2), (3), (4) or (5), Sp is preferably unsubstituted.

[0305] In the compounds of formula (1), (2), (3), (4) or (5), R 11 and R 12 are preferably H.

[0306] In the compounds of formula (1), (2), (3), (4) or (5), R 10 is preferably H or methyl.

[0307] In the compounds of formula (1) or (2), R 5 is preferably H.

[0308] In the compounds of formula (1) or (2), R 6Preferably H.

[0309] In the compound of formula (1) or (2), R 8 Preferably H.

[0310] In the compound of formula (1) or (2), R 9 Is preferably a straight-chain or branched alkyl or alkoxy group having 1-6 C atoms, which may be partially or fully fluorinated, and X1, a, R 5 -R 8 And R 10 -R 12 Have the meanings as described above or preferably as described previously.

[0311] In the compound of formula (1) or (2), R 7 Is preferably a straight-chain or branched alkyl group having 2 to 8 C atoms, which may be partially or fully fluorinated, and X1, a, R 5 -R 6 , R 9 And R 10 -R 12 Have the meanings as described above or preferably as described previously.

[0312] In the compound of formula (2), (4) or (5), R 1 , R 2 , R 3 And R 4 Preferably H.

[0313] In the compound of formula (2) or (4), R 5 , R 6 , R 7 , R 8 And R 9 Are preferably independently of each other selected from H, F, straight-chain or branched alkyl groups having 1-20 C atoms, straight-chain or branched alkoxy groups having 1-20 C atoms, partially or fully halogenated straight-chain or branched alkyl groups having 1-20 C atoms, and partially or fully halogenated straight-chain or branched alkoxy groups having 1-20 C atoms.

[0314] In the compound of formula (4), R 5 , R 6 , R 7 , R 8 And R 9 Are all preferably H, or one or two of R 5 , R 6 , R 7 , R 8 And R 9 Are F or alkyl groups having 1-8 C atoms, which may be partially or fully fluorinated, and the other substituents are H.

[0315] In the compound of formula (5), R 5 , R 6 , R 7 , R 8 and R 9 are all preferably H, except that one substituent is of formula (2-1) as described above or preferably as previously described.

[0316] In a further embodiment of the present invention, the polymeric optical material comprising the polymeric matrix of the intraocular lens to be used in the method according to the present invention contains monomers selected from the polymeric compounds (M-1) to (M-68) and (A-01) to (A-16):

[0317]

[0318]

[0319]

[0320]

[0321]

[0322]

[0323]

[0324]

[0325]

[0326]

[0327]

[0328] In a further embodiment of the present invention, the polymeric optical material comprising the polymeric matrix contains polymeric monomers selected from compounds (M-12), (M-14), (M-15), (M-18), (M-53), (M-55), (M-67), (A-01) to (A-16).

[0329] In a further highly preferred embodiment of the present invention, the polymeric matrix of the polymeric optical material to be used in the method according to the present invention is a copolymer matrix, which comprises polymeric monomers containing the light-active units as described or preferably as previously described, or polymeric compounds of formula (1) to (5) as described above or polymeric compounds (M-1) to (M-68) and (A-01) to (A-16) and other polymeric monomers known in the art.

[0330] Examples of monomers for copolymerizing with the monomers described above or preferably the monomers containing photoactive units described previously for constructing polymeric optical materials for intraocular lenses (such as contact lenses or IOLs) may be selected from styrene, ethoxyethyl methacrylate (EOEMA), methyl methacrylate (MMA), methyl acrylate, n-alkyl acrylates (n-alkyl containing 2-20 carbon atoms), n-alkyl methacrylates (n-alkyl containing 2-20 carbon atoms), iso-alkyl acrylates (iso-alkyl containing 3-20 carbon atoms), iso-alkyl methacrylates (iso-alkyl containing 3-20 carbon atoms), ethoxyethoxyethyl acrylate (EEEA), 2-hydroxyethyl methacrylate (HEMA), tetrahydrofurfuryl methacrylate (THFMA), glycidyl methacrylate (GMA), 16-hydroxyhexadecyl acrylate, 16-hydroxyhexadecyl methacrylate, 18-hydroxyoctadecyl acrylate, 18-hydroxyoctadecyl methacrylate, 2-phenoxyethyl acrylate (EGPEA), heptafluorobutyl acrylate, heptafluorobutyl methacrylate, hexafluorobutyl acrylate, hexafluorobutyl methacrylate, hexafluoroisopropyl acrylate, hexafluoroisopropyl methacrylate, octafluoropentyl acrylate, octafluoropentyl methacrylate, pentafluoropropyl acrylate, pentafluoropropyl methacrylate, tetrafluoropropyl methacrylate, trifluoroethyl acrylate, trifluoroethyl methacrylate, bisphenol A diacrylate-1EO / phenol (BPADA), 2-[3'-2'H-benzotriazol-2'-yl)-4'-hydroxyphenyl]ethyl methacrylate (BTPEM) or ethylene glycol dimethacrylate.

[0331] Preferred examples of monomers for copolymerizing with the monomers described above or preferably the monomers containing photoactive units described previously for constructing polymeric optical materials for intraocular lenses (such as contact lenses or IOLs) are selected from methyl methacrylate, 2-hydroxyethyl methacrylate, 2-phenoxyethyl acrylate, ethoxyethoxyethyl acrylate, 8-methylnonyl methacrylate, n-butyl methacrylate, 2-ethylhexyl methacrylate or mixtures thereof.

[0332] Suitable UV absorbers are 2-(3-(tert-butyl)-4-hydroxy-5-(5-methoxy-2-benzotriazolyl)phenoxy)ethyl methacrylate, 3-(3-(tert-butyl)-4-hydroxy-5-(5-methoxy-2-benzotriazolyl)phenoxy)propyl methacrylate, 3-(3-tert-butyl-5-(5-chlorobenzotriazol-2-yl)-4-hydroxyphenyl)propyl methacrylate, 3-(3-(tert-butyl)-4-hydroxy-5-(5-methoxy-2H-benz[d][1,2,3]triazol-2-yl)phenoxy)propyl methacrylate, 2-(2-hydroxy-5-vinylphenyl)-2H-benzotriazole, allyl 2-hydroxybenzophenone, 2-allyl-6-(2H-benzotriazol-2-yl)-p-cresol, 4-methacryloyl-2-hydroxybenzophenone, 2-(2'-hydroxy-3'-methylallyl-5'-methylphenyl)benzotriazole, 2-hydroxy-4-methacryloyloxylbenzophenone, 4-acryloylethoxy-2-hydroxybenzophenone, 2-[3-(2H-benzotriazol-2-yl)-4-hydroxyphenyl]ethyl methyl acrylate, 2-(2'-hydroxy-5'-methacryloylamidophenyl)-5-methoxybenzotriazole, 2-(2'-hydroxy-5'-methacryloylamidophenyl)-5-chlorobenzotriazole, 2-(2'-hydroxy-5'-methacryloyloxypropylphenyl)benzotriazole, 2-(2'-hydroxy-5'-methacryloylpropyl-3'-tert-butyl-phenyl)-5-methoxy-2H-benzotriazole, 2-(3-(tert-butyl)-4-hydroxy-5-(5-methoxy-2H-benz[d][1,2,3]triazol-2-yl)phenoxy)ethyl methacrylate, 2-[3'-tert-butyl-2'-hydroxy-5'-(3”-methacryloyloxypropyl)phenyl]-5-chlorobenzotriazole, 2-{2'-hydroxy-3'-tert-butyl-5'-[3'-methacryloyloxypropoxy]phenyl}-5-methoxy-2H-benzotriazole, 2-[3'tert-butyl-5'-(3”-dimethylvinylsilylpropoxy)-2'-hydroxyphenyl]-5-methoxybenzotriazole, 2-(tert-butyl)-6-(5-chloro-2H-benz[d][1,2,3]triazol-2-yl)-4-vinylphenol, 2-(2H-1,2,3-benzotriazol-2-yl)-4-methyl-6-(2-methylprop-2-enyl)phenol, 2-(3-acetyl-2-aminophenoxy)ethyl methacrylate, 2-(4-benzoyl-3-hydroxyphenoxy)ethyl acrylate, or a combination of these compounds.

[0333] Preferred UV absorbers are selected from 2-[3'-(2'H-benzotriazol-2'-yl)-4'-hydroxyphenyl]ethyl methacrylate (BTPEM), 2-(3-(tert-butyl)-4-hydroxy-5-(5-methoxy-2-benzotriazolyl)phenoxy)ethyl methacrylate, 3-(3-(tert-butyl)-4-hydroxy-5-(5-methoxy-2-benzotriazolyl)phenoxy)propyl methacrylate, 3-(3-tert-butyl-5-(5-chlorobenzotriazol-2-yl)-4-hydroxyphenyl)propyl methacrylate, and they can be polymerized together with the monomers according to formula (1), (2), (3), (4) or (5).

[0334] Suitable crosslinking agents for the polymer optical materials for constructing intraocular lenses (contact lenses or IOLs) to be used in the copolymers containing the polymerized monomers of formula (1), (2), (3), (4) or (5) are selected from poly(ethylene glycol) diacrylate, poly(ethylene glycol) dimethacrylate, ethylene glycol dimethacrylate (EGDMA), ethylene glycol diacrylate, 1,3-propanediol diacrylate, 1,6-hexanediol diacrylate, 1,8-octanediol diacrylate, 1,11-undecanediol diacrylate, 1,12-dodecanediol diacrylate, 1,15-pentadecanediol diacrylate, 1,16-hexadecanediol diacrylate, 1,18-octadecanediol diacrylate, 1,3-propanediol dimethacrylate, 1,6-hexanediol dimethacrylate, 1,8-octanediol dimethacrylate, 1,11-undecanediol dimethacrylate, 1,12-dodecanediol dimethacrylate, 1,15-pentadecanediol dimethacrylate, 1,16-hexadecanediol dimethacrylate, 1,18-octadecanediol dimethacrylate.

[0335] If it is necessary to increase the refractive index, a wavelength in another region can be applied to intraocular lenses (contact lenses or IOLs) made of one or more polymers capable of changing the degree of polarization. 400 - 590 nm can be used, preferably 500 - 580 nm, and most preferably 530 - 570 nm.

[0336] Hereinafter, the optical materials for intraocular lenses to be used in the method according to the present invention, preferably the polymer optical materials of contact lenses or IOLs, are further and preferably described for the wavelength regions of 400 nm - 590 nm, preferably 500 nm - 580 nm, particularly preferably 530 nm - 570 nm to locally increase the degree of polarization of the materials.

[0337] To apply such adjustment, the refractive index range of the polymer optical material is 1.45 - 1.60.

[0338] The polymeric optical material (contact lens or IOL) for the adjustable intraocular lens may optionally contain an ultraviolet light blocker or a blue light absorber as described above.

[0339] The polymeric optical material for the adjustable intraocular lens for use in the method according to the invention comprises a polymer matrix, which polymer matrix comprises covalently bound dimerized photoactive units, preferably in an amount of at least 2 wt% - 100 wt%, preferably 5 wt% - 90 wt%, most preferably 7 wt% - 80 wt%.

[0340] The dimerized photoactive units within the polymer matrix may be the same or different.

[0341] The polymer matrix of the polymeric optical material for the adjustable intraocular lens and / or IOL may be a matrix derived from a homopolymer or a copolymer, preferably a copolymer.

[0342] The polymer matrix comprising the dimerized photoactive units may be a matrix derived from a silicone-containing polymer, an acrylic polymer, a methacrylic polymer or a mixture thereof.

[0343] Dimerized photoactive units refer to photo-chemically active units which are photo-chemically active in the wavelength region of 400 nm - 590 nm as described or preferably previously described under the effect of a two-photon or multi-photon process.

[0344] The polymer matrix of the polymeric optical material for the adjustable lens and / or IOL comprises dimerized photoactive units which are capable of separating under the effect of a two-photon or generally a multi-photon process.

[0345] Accordingly, the present invention further relates to a method for adjusting the polarization degree of an intraocular lens (preferably at one or more specific locations of the lens) comprising a body formed from a polymeric optical material, wherein the polymeric optical material of the intraocular lens comprises a polymer matrix which polymer matrix comprises covalently bound dimerized photoactive units as the only photoactive units capable of separating under the effect of a two-photon or generally a multi-photon process.

[0346] Preferably, the dimerized photoactive units comprise a cyclobutane ring which will split under the effect of a two-photon or generally a multi-photon process.

[0347] Alternatively, the dimerized photoactive units particularly preferably comprise a cyclobutane ring which is capable of splitting under the effect of a two-photon or generally a multi-photon process.

[0348] Accordingly, the present invention further relates to a method for adjusting the polarization degree of an intraocular lens comprising a body formed of a polymeric optical material (preferably at one or more specific locations of the lens), wherein the polymeric optical material of the intraocular lens comprises a polymer matrix, the polymer matrix comprises covalently bonded dimerized photoactive units, which comprise a cyclobutane ring as the only photoactive unit and are capable of splitting under the effect of a two-photon or generally multi-photon process.

[0349] The splitting of the dimerized photoactive unit comprising a cyclobutane ring is visualized in Scheme 1 as described above.

[0350] In a preferred embodiment of the present invention, the polymeric optical material of a polymer matrix containing dimerized photoactive units of an intraocular lens to be used in the method according to the present invention is derived from the polymerized monomers of formula (1), (2), (3), (4) or (5) as described above or preferably described previously.

[0351] In a further embodiment of the present invention, the polymeric optical material of a polymer matrix containing dimerized photoactive units of an intraocular lens to be used in the method according to the present invention is derived from the monomers selected from the polymerized compounds (M-1) to (M-68) and (A-01) to (A-16) as described above.

[0352] In a further highly preferred embodiment of the present invention, the polymer matrix of the polymeric optical material to be used in the method according to the present invention is the copolymer matrix described above or preferably described previously containing polymerized monomers containing dimerized photoactive units, or is derived from the polymerized compounds of formula (1) to (5) as described above, or is derived from the polymerized compounds (M-1) to (M-68) and (A-01) to (A-16) and other polymerized monomers known in the art.

[0353] Examples of monomers, UV absorbers and crosslinking agents are described above and are thus applicable to such polymeric optical materials containing dimerized photoactive units as described above or preferably described previously.

[0354] In the manufacture of an intraocular lens to be used in the method according to the present invention, the polymer matrix containing partially or fully dimerized photoactive units can be formed via single-photon absorption or two-photon or generally multi-photon absorption of photoactive units capable of dimerizing by forming a cyclobutane ring by [2π + 2π] cycloaddition as described above or preferably described previously.

[0355] If the method according to the present invention is applied to the eye, two-photon (or generally multi-photon) absorption can be used.

[0356] To produce an intraocular lens comprising a polymeric optical material containing a polymeric matrix for use in the method according to the invention, the polymeric matrix comprising partially or fully dimerized photoactive units, two-photon (or generally multi-photon) absorption or single-photon absorption by any irradiation means (such as a UV lamp with a special wavelength filter, a UV LED with one of the wavelengths given above or a laser with the wavelength given above) can be used.

[0357] To produce an intraocular lens comprising a polymeric optical material containing a polymeric matrix for use in the method according to the invention, the polymeric matrix comprising partially or fully dimerized photoactive units, single-photon absorption by any irradiation means (such as a UV lamp with a special wavelength filter, a UV LED with one of the wavelengths given above or a laser with the wavelength given above) is preferably used.

[0358] To manufacture an intraocular lens comprising a polymeric optical material containing a polymeric matrix for use in the method according to the invention, the polymeric matrix comprising partially or fully dimerized photoactive units, the same irradiation sources as those described previously for the system according to the invention can be used, by doubling the frequency of the pumping laser, or an optical power amplifier can be used, or another irradiation source can be used. Preferably, another irradiation source is used to manufacture the intraocular lens.

[0359] The invention further relates to a method for adjusting the polarization degree of an intraocular lens comprising a body formed of a polymeric optical material based on a two- or multi-photon absorption process, the method comprising the following steps:

[0360] Providing the intraocular lens; and

[0361] Adjusting the polarization degree of the lens by irradiating the lens using the system as described previously or preferably as described previously,

[0362] wherein the provided intraocular lens comprises a polymeric matrix, the polymeric matrix comprising covalently bound photoactive units, the photoactive units comprising non-aromatic double bonds capable of dimerizing by [2π + 2π] cycloaddition as described previously or preferably as described previously,

[0363] and

[0364] wherein the provided intraocular lens is irradiated with an irradiation beam of the first wavelength, the irradiation causing dimerization of the photoactive units, thereby reducing the polarization degree of the intraocular lens and thus modifying the provided intraocular lens, which consists in that the modified intraocular lens comprises a polymeric matrix, the polymeric matrix comprising partially or fully dimerized photoactive units derived from the [2π + 2π] cycloaddition, and

[0365] Optionally, irradiate the modified intraocular lens with an irradiation beam of the second wavelength to locally increase the degree of polarization of the modified intraocular lens by partially splitting the dimerized photoactive units.

[0366] The present invention further relates to a method for adjusting the degree of polarization of an intraocular lens comprising a body formed of a polymeric optical material based on a two - or multi - photon absorption process, the method comprising the steps of:

[0367] Providing the intraocular lens; and

[0368] Adjusting the degree of polarization of the lens by irradiating the lens using the system as described above or preferably as previously described,

[0369] wherein the provided intraocular lens comprises a polymeric matrix comprising covalently - bound dimerized photoactive units as the only photoactive units capable of being separated under the effect of a two - photon or generally multi - photon process as described above or preferably as previously described, and

[0370] wherein the provided intraocular lens is irradiated with an irradiation beam of the second wavelength, said irradiation causing the separation of the dimerized photoactive units, thereby increasing the degree of polarization of the intraocular lens and thus modifying the provided intraocular lens, which consists in that the modified intraocular lens comprises a polymeric matrix comprising photoactive units capable of re - dimerizing and

[0371] Optionally, irradiate the modified intraocular lens with an irradiation beam of the first wavelength to locally decrease the degree of polarization of the modified intraocular lens by partially dimerizing the photoactive units.

[0372] The present invention further relates to a method for adjusting the degree of polarization of an intraocular lens comprising a body formed of a polymeric optical material based on a two - or multi - photon absorption process, the method comprising the steps of:

[0373] Providing the intraocular lens; and

[0374] Adjusting the degree of polarization of the lens by irradiating the lens using the system as described above or preferably as previously described,

[0375] wherein the provided intraocular lens comprises a polymeric matrix comprising covalently - bound photoactive units, the photoactive units comprising non - aromatic double bonds capable of dimerizing by [2π + 2π] cycloaddition with the photoactive units that have been dimerized as described above or preferably as previously described under the effect of a two - photon or multi - photon process, and

[0376] The intraocular lens provided is irradiated with an irradiation beam of the first wavelength, and the irradiation causes dimerization of the photoactive unit, thereby reducing the degree of polarization of the intraocular lens and thus modifying the provided intraocular lens, which consists in that the modified intraocular lens comprises a polymer matrix, and the polymer matrix comprises more photoactive units derived from the dimerization of the [2π+2π] cycloaddition, or

[0377] The intraocular lens provided is irradiated with an irradiation beam of the second wavelength, and the irradiation causes separation of the dimerized photoactive unit, thereby increasing the degree of polarization of the intraocular lens and thus modifying the provided intraocular lens, which consists in that the modified intraocular lens comprises a polymer matrix, and the polymer matrix comprises more photoactive units capable of dimerizing by forming a cyclobutane ring through [2π+2π] cycloaddition.

[0378] The present invention further relates to a method for locally adjusting the degree of polarization of an intraocular lens disposed in a patient's eye and comprising the polymer optical material as described above or preferably as previously described, the method comprising:

[0379] Exposing the intraocular lens to an irradiation beam having a wavelength between 600 nm and 800 nm to locally reduce the degree of polarization of the intraocular lens or

[0380] Exposing the intraocular lens to an irradiation beam having a wavelength between 400 nm and 590 nm to locally increase the degree of polarization of the intraocular lens, preferably using the system and / or method as described above.

[0381] The present invention further relates to a method for locally adjusting the degree of polarization of an intraocular lens disposed in a patient's eye and comprising the polymer optical material as described above or preferably as previously described, the method comprising:

[0382] Exposing the intraocular lens to a first irradiation beam having a first wavelength between 600 nm and 800 nm to locally reduce the degree of polarization of the intraocular lens; and

[0383] Exposing the intraocular lens to a second irradiation beam having a second wavelength between 400 nm and 590 nm to locally increase the degree of polarization of the intraocular lens, thereby preferably using the system and / or method as described above.

[0384] The invention further relates to a method for locally adjusting the degree of polarization of an intraocular lens disposed within a patient's eye and comprising the polymer optical material as described above or preferably as previously described, wherein said exposure of the intraocular lens comprises scanning the irradiation beam across the intraocular lens based on input data, said input data being related to: lens data associated with the intraocular lens, in particular associated with the polymer optical material, and / or treatment plan data associated with a treatment plan for treating the intraocular lens based on exposing the intraocular lens to the irradiation beam.

[0385] The invention further relates to a method for locally adjusting the degree of polarization of an intraocular lens disposed within a patient's eye and comprising the polymer optical material as described above or preferably as previously described, wherein the lens data comprises data related to one or more of the following: the dimensions of the intraocular lens (e.g., diameter and / or thickness), the material as described above or preferably as previously described comprised by the intraocular lens, in particular the polymer optical material, the refractive index of the intraocular lens, and a mapping of the refractive index to the specific position / coordinates of the intraocular lens.

[0386] The invention further relates to a method for locally adjusting the degree of polarization of an intraocular lens disposed within a patient's eye and comprising the polymer optical material as described above or preferably as previously described, wherein the treatment plan data comprises one or more of the following:

[0387] Scanning strategy control command data for the scanning of the irradiation beam across the intraocular lens (e.g., scanning mode and / or scanning order and / or scanning speed and / or scanning duration of the scanning mode and / or scanning duration of the scanning order and / or pulse duration of the pulses of the irradiation beam of the first and / or second wavelength and / or irradiation beam characteristics of the irradiation beam and / or irradiation (photon) density and / or irradiation intensity and / or irradiation power and / or irradiation wavelength),

[0388] Temperature data of the current and / or predicted temperature of the intraocular lens during said exposure,

[0389] Refractive index data of the refractive index of the intraocular lens to be obtained based on said exposure, the refractive index to be obtained being in particular related to a mapping of the refractive index to the specific position / coordinates of the intraocular lens,

[0390] Rupture dimension data of rupture dimensions,

[0391] Eye data related to the dimensions and / or shape of the patient's eye,

[0392] Positioning data related to the position and / or orientation of the intraocular lens relative to the eye, and

[0393] Registration data related to the identity of the patient and / or the patient's specific eye.

[0394] The present invention further relates to a method for locally adjusting the degree of polarization of an intraocular lens disposed within a patient's eye and comprising a polymeric optical material as described above or preferably as previously described, wherein the exposure of the intraocular lens to the irradiation beam comprises exposing a first volume of the intraocular lens and then exposing a second volume of the intraocular lens, wherein the first volume is further from the cornea of the patient's eye than the second volume.

[0395] The present invention further relates to a method for locally adjusting the degree of polarization of an intraocular lens disposed within a patient's eye and comprising a polymeric optical material as described above or preferably as previously described, wherein the (first) wavelength is between 650 nm and 750 nm, preferably between 670 nm and 720 nm, and more preferably between 680 nm and 710 nm.

[0396] The present invention further relates to a method for locally adjusting the degree of polarization of an intraocular lens disposed within a patient's eye and comprising a polymeric optical material as described above or preferably as previously described, wherein the (second) wavelength is between 500 nm and 580 nm, preferably between 530 nm and 570 nm.

[0397] In the above item, an initial step of the method may be to provide the intraocular lens.

[0398] In an example, wherein the exposure of the intraocular lens to the irradiation beam comprises exposing a first volume and / or plane and / or position of the intraocular lens and then exposing a second volume and / or plane and / or position of the intraocular lens, wherein the first volume and / or plane and / or position is further from the cornea of the patient's eye than the second volume and / or plane and / or position, the volume and / or plane and / or position irradiated at a later time point in the irradiation sequence may be closer to the cornea than the volume and / or plane and / or position irradiated at an earlier time point. The volume herein may be associated with one or more planes of the intraocular lens.

[0399] The lens data and the treatment plan data are preferably as previously described and are part of a system preferably for use in the method as previously described for locally adjusting the degree of polarization of an intraocular lens disposed within a patient's eye and comprising a polymeric optical material as described above or preferably as previously described.

[0400] The present invention further relates to a method for correcting the vision of a patient by modifying the refractive index of an intraocular lens as described above or preferably as previously described and comprising a polymeric optical material within the patient's eye, comprising

[0401] confirming and measuring the degree of vision correction of the patient;

[0402] Determine the position and type of the refractive structure to be written into the intraocular lens to correct the vision of the patient; and

[0403] Subsequently, expose the intraocular lens to two-photon or multi-photon irradiation with a wavelength between 600 nm and 800 nm to locally reduce the degree of polarization of the intraocular lens, and / or

[0404] Subsequently, expose the intraocular lens to two-photon or multi-photon irradiation with a wavelength between 400 nm and 590 nm to locally increase the degree of polarization of the intraocular lens, preferably by using the system and / or method as described above to expose the intraocular lens to the irradiation.

[0405] As described above, the change in the degree of polarization results in a change in the refractive index, as will be described in more detail below.

[0406] The speed of light c0 in a vacuum is a fundamental constant and describes the speed of electromagnetic waves in a vacuum. According to the solution of Maxwell's equations, the speed of light in a vacuum can be related to the electric constant ε0 and the magnetic constant μ0. They are also fundamental constants.

[0407]

[0408] The speed of light when passing through a transparent medium c m is less than its speed in a vacuum. The electric constant needs to be replaced by the permittivity ε and the magnetic constant needs to be replaced by the permeability μ.

[0409]

[0410] The relative permittivity ε r (also known as the dielectric constant) is a dimensionless, material-related parameter that gives the permittivity relative to the electric constant. Therefore, the relative permittivity ε of a vacuum r = 1, which can also be seen by comparing the above two equations. The actual permittivity is obtained by multiplying the relative permittivity by ε0

[0411] ε = ε0ε r = (1 + χ e )ε0

[0412] where χ e is the electric susceptibility of the material, a value closely related to ε r and defined as

[0413] χ e = ε r - 1

[0414] The relative permittivity describes how the electric field strength is reduced if a material (also called a dielectric) is placed in an electric field. The relative permittivity depends on the ability of the material to polarize in response to the electric field, thereby reducing the total electric field within the material. The relative permittivity of most materials is between 1 and 100, but dielectrics with ε r up to 10,000 are also known. For example, the relative permittivities of polystyrene, cellulose, and water are 2.5, 4.5, and 81, respectively. The relative permittivity of air can be considered 1 (a good approximation). Usually, the relative permittivity is not constant because it varies with the frequency of the applied electric field, humidity, temperature, and other parameters. In a non-linear dielectric, the permittivity can depend on the electric field strength. Therefore, the outdated term "dielectric constant" for ε r is ambiguous and should no longer be used.

[0415] For magnetic field values μ0, μ r and the definition of μ is similar to the corresponding electric field values. The magnetic permeability is μ = μ0μ r

[0416] and the magnetic susceptibility is

[0417] χ m = μ r - 1

[0418] By definition, the relative magnetic permeability of vacuum μ r = 1. The relative permittivity varies with the magnetic field strength and is generally a function of frequency. The relative magnetic permeability of a substance can also be negative. Diamagnetic substances (μ r < 1), paramagnetic substances (μ r > 1) and ferromagnetic substances (μ r >> 1) are distinguished. Most organic substances such as polymers are diamagnetic and their relative magnetic permeability is very close to 1.

[0419] The refractive index n is a material constant that characterizes the refraction properties of the medium. As previously introduced, the refractive index is the ratio of the speed of light in vacuum to the speed of light in a given medium. Thus, the refractive index of vacuum is 1. The refractive index of water is 1.333. The refractive index of commercially available glassware ranges from 1.4 to 1.9. The refractive index of most organic polymers is between 1.4 and 1.6, and that of specially modified high refractive index polymers is greater than 1.7. The refractive index generally depends on the frequency of light, a phenomenon called dispersion. Since the refractive index of dry air (n air ≈ 1.0003) is only slightly different from 1, it can be measured relative to air to obtain a good approximation. In technical optics, the refractive index n 0 is used. It is defined as

[0420]

[0421] The following relationship can be obtained

[0422]

[0423] Since μ r ≈ 1 for the frequencies of organic polymers in the visible part of the electromagnetic spectrum, this equation can be further simplified to

[0424]

[0425] This shows that the refractive index of the polymer / copolymer changes when its relative permittivity ε r changes. To understand how the relative permittivity and thus the refractive index of the polymer / copolymer can be modified, one must look more closely at what happens when light waves interact with matter. If an electric field, in this case the electric component of the light wave , acts on the medium, it induces a dipole moment . The polarization is defined as the density of electric dipoles per unit volume.

[0426]

[0427] The norm of the vector is the areal density σ p of the polarization charge.

[0428]

[0429] The polarization vector and the external electric field vector point in the same direction. The electric flux lines of the electric field induced by the polarization charge travel from the positive to the negative surface charges of the dielectric. Thus, the electric flux lines inside the dielectric travel in a direction opposite to the electric flux lines of the external electric field . The polarization in the electric field is given by

[0430]

[0431] The electric susceptibility was defined earlier. Two types of polarization need to be distinguished: displacement polarization and orientation polarization. Displacement polarization is produced by the relative displacement of charges in neutral atoms or molecules with respect to each other. It is the relative tendency of the charge distribution, like the electron cloud of an atom or molecule, to be deformed from its normal shape by an external electric field, i.e., the electric field induces an electric dipole moment. Orientation polarization is produced by the alignment of permanent dipoles along the electric field lines. These dipoles already exist in the medium even before the application of the electric field. In the visible spectral range, only the orientation polarization of electrons should be considered. The frequency of visible light is relatively high, ranging from about 10 14 Hz to 10 15Hz. Therefore, the factors affecting the overall polarization caused by the displacement of atoms and the orientation of permanent dipoles are very small and can be neglected. Only electrons can "obey" the rapidly oscillating electric field. For displacement polarity, the equation

[0432]

[0433] provides the relationship between the number of particles per unit volume x and the polarization. The proportionality constant α in this equation is called the electric susceptibility. The susceptibility is a molecular parameter. Quantum particles are not rigidly connected to each other. They are bound to their equilibrium positions by forces that are, to a first approximation, elastic. Therefore, Newton's law F = -kx can be applied. The external electric field exerts a force Q·E on such a charge Q. This force deflects the charge by a distance x = F / k = QE / k.

[0434] Such a displacement produces an induced dipole moment

[0435]

[0436] By comparison, it can be easily seen that α must be proportional to ε r .

[0437] α ∝ (ε r - 1)ε0

[0438] This means that changing the degree of polarization of the molecules in a given medium results in a change in the refractive index of that medium.

[0439] It should be noted that variations of the embodiments described in the present invention are all included within the scope of protection of the present invention. Unless explicitly excluded, any feature disclosed in the present invention may be exchanged for an alternative feature for the same purpose or an equivalent or similar purpose. Therefore, any feature disclosed in the present invention, unless otherwise specified, should be regarded as an example of a general series or an equivalent or similar feature.

[0440] All features of the present invention can be combined with each other in any way, unless the specific features and / or steps are mutually exclusive. This is especially true for the preferred features of the present invention. Similarly, features that are not necessarily combined can be used alone (instead of in combination).

[0441] It should also be pointed out that many features of the present invention, especially those of the preferred embodiments, are themselves inventive and should not be regarded merely as some embodiments of the present invention. For these features, independent protection may be sought in addition to or as an alternative to any currently claimed invention.

[0442] The technical teachings disclosed in the present invention can be extracted and combined with other examples.

[0443] Without a doubt, those skilled in the art will think of many other effective alternatives. It should be understood that the present invention is not limited to the described embodiments and includes modifications that are obvious to those skilled in the art and fall within the scope of the appended claims. Examples

[0444] The present invention is described in detail by the following examples, but is not intended to limit the present invention.

[0445] The following examples are also included in the present disclosure and may be incorporated in whole or in part into the embodiments and general disclosure of the present invention.

[0446] In the single - photon experiment, the operation of the UV / Vis spectrum is carried out by placing a cuvette containing the dissolved sample on the sample holder and then irradiating the cuvette. The change in the UV / Vis spectrum over time is monitored by UV / Vis measurement, for example, by using a UV / Vis spectrometer Lambda 900 (manufactured by Perkin Elmer).

[0447] The operation of the refractive index in the single - photon experiment as described below is carried out by placing the sample on the sample holder and preferably irradiating the sample for 30 seconds. The resulting change in refractive index is monitored over time by refractive index measurement. The change in refractive index is measured using a multi - wavelength refractometer (ATR - L from Schmidt&Haensch).

[0448] The single - photon experiment shows the ability of the described polymeric optical material of the intraocular lens to be used in the method according to the present invention to locally change the initial polarization degree by irradiating with specific first and second wavelengths to initiate, for example, a [2π + 2π] cycloaddition or ring - cleavage as described above or below.

[0449] Alternatively, the intraocular lens can be processed based on a multi - photon (e.g., two - photon) process further described in Examples 14 to 19 below.

[0450] Examples:

[0451] Example 1: Preparation of poly(M - 14):

[0452] First, 1 g of M - 14 was dissolved in 10 mL of chloroform. Then the solution was degassed and 1.33 mg of AIBN was added. Then the mixture was stirred at 60 °C for 14 h. After that, the polymer was precipitated in 250 mL of methanol. Then the resulting polymer poly(M - 14) was dried.

[0453] Example 2:

[0454] In the second embodiment, a solution of 75.4 mg of poly(M-14) in 10 mL of THF was prepared. It was diluted 500-fold. The diluted solution was filled into a quartz glass cuvette (32 / GL14 / S / Q / 10, obtained from STARNA, having a path length of 10 mm). The UV / Vis spectrum was obtained by using a UV / Vis spectrometer Lambda 900 (obtained from Perkin Elmer). The sample was alternately irradiated at 340 nm and the UV / Vis spectrum was obtained. The results are plotted in Figure 12 which shows the absorption as a function of the wavelength for the single-photon process.

[0455] Figure 12 There are three isosbestic points in. This indicates a controlled conversion. The photochemical reaction shown for the conversion is a [2π+2π] cycloaddition, as shown in Figure 8 which produces a cross-linked polymer. The dimerization of the photoactive units is indicated by the decreasing signal at 332 nm. The signal intensity in the range of 260 nm - 275 nm increases.

[0456] The reaction mixture was dried and analyzed by NMR.

[0457] 1 1H NMR (500 MHz, CDCl3) δ 7.45, 7.17, 7.08–7.03, 7.01–6.96, 6.84, 6.75, 6.61, 6.52, 4.96, 4.72, 4.06, 3.95–3.87, 2.58, 2.54–2.47, 2.36, 1.76, 1.71–1.56, 1.49–1.44, 1.37–1.24, 1.14, 0.93–0.84.

[0458] The 1 singlets at 4.72 and 4.96 ppm in the 1H NMR spectrum are attributed to the cyclobutane ring formed via the photochemical [2π+2π] cycloaddition reaction. The two signals are attributed to the formation of a mixture of photodimers consisting of cis and trans in head-to-head and head-to-tail arrangements respectively. The NMR signals and conclusions are in agreement with the literature [Rao et al., Chem. Ber., 1973, 106(2), 388].

[0459] Example 3:

[0460] In the third embodiment, irradiated poly(M-14) as prepared in Example 2 was used. The UV / Vis spectrum was taken. Samples were taken alternately at 275 nm and irradiated with the UV / Vis spectrum. The results are plotted in Figure 13 which shows the absorption as a function of the wavelength for the single-photon process.

[0461] The experiments described show the ability of representative polymeric optical materials to split photoactive units into dimers.

[0462] The amount of cyclobutane moieties within the crosslinked poly(M-14) is reduced. The mechanism of the splitting is shown in Figure 9 . The return conversion is indicated by an enhanced signal at 332 nm.

[0463] The reaction mixture was dried and analyzed by NMR.

[0464] 1 1H NMR (500 MHz, CDCl3) δ 7.67, 7.40, 7.20–7.14, 6.86, 4.11–4.00, 2.69–2.62, 2.36, 1.87–1.78, 1.65, 1.53–1.41, 1.40–1.26, 1.14, 0.91.

[0465] As can be further seen, the singlets at 4.74 and 4.98 ppm, previously ascribed to the cyclobutane ring formed via photoinduced photochemical [2π+2π] cycloaddition reaction as demonstrated in the 1H NMR spectrum of Example 2, disappear, documenting the splitting, as 1 shown. Figure 9

[0466] Example 4:

[0467] In a fourth example, a polymeric optical material with a copolymer matrix is prepared.

[0468] A melt mixture of 2.00 g of M-14, 10.36 mg of 2-[3-(2H-benzotriazol-2-yl)-4-hydroxyphenyl]ethyl methacrylate, 220.00 mg of poly(ethylene glycol) diacrylate (average Mn 250), and 247.60 mg of n-butyl methacrylate was first degassed. Subsequently, 25.57 mg of 1,1'-(3,3,5-trimethylcyclohexylidene)bis[2-(1,1-dimethylethyl) peroxide was added. The mixture was filtered into a 1 mm thick sheet mold. Polymerization occurred thermally under conditions considered suitable by those skilled in the art. After polymerization, the process was completed and the polymer was demolded, yielding a 1 mm thick polymer sheet.

[0469] Example 5:

[0470] In a fifth example, sheets were punched from a cylindrical blank of the polymeric optical material prepared according to Example 4. A multi-wavelength refractometer with a heating stage was used to determine the refractive index. Prior to measurement, the blank was heated to 80 °C in the apparatus to relieve stress from the material. In this example, the refractive index was measured at 546 nm and 35 °C. The blank was held outside the refractometer at​Figure 10 Irradiate in the device at 340 nm. Transfer the sample back to the refractometer, heat to 80 °C, and measure the refractive index at 546 nm and 35 °C. Figure 14 Shows the change in refractive index as a function of the applied energy for the single - photon process.

[0471] As the applied energy is increased, the refractive index of the irradiated polymeric optical material decreases. This is caused by the cross - linking reaction shown in Figure 8 . As shown in Figure 8 The cycloaddition reaction produces photoactive units (cyclobutane rings) with lower polarizability, which results in a decrease in the refractive index.

[0472] The sample irradiated at 340 nm is further used in the procedure as described herein, but the irradiation wavelength is 275 nm.

[0473] Shown in Figure 15 The effect is caused by the cleavage or re - conversion of the cyclobutane moiety (see Figure 9 ). This results in a higher degree of polarization and an increase in the refractive index. Figure 15 Shows the change in refractive index as a function of the applied energy for the single - photon process.

[0474] Figure 10 Shows a system (400) related to the irradiation setup using an LED system for single - photon experiments as described above.

[0475] The system (400) includes an irradiation source (402), a beam collimator (404), and a sample holder (408) on which a sample (406) is mounted.

[0476] The irradiation source (402) is a Mounted LED M340L4 - 340 nm, 53 mW from Thorlabs in this Example 5.

[0477] Examples 6 - 10 are carried out similarly to Examples 1 - 5 above.

[0478] Example 6: Preparation of poly(M - 18).

[0479] Dissolve 1 g of M - 18 in 10 mL of chloroform. Degas the solution and add 1.33 mg of AIBN. Stir the mixture at 60 °C for 14 h. Precipitate the polymer in 250 mL of methanol. Dry the resulting polymer poly(M - 18).

[0480] Example 7:

[0481] In the seventh embodiment, a solution of 12.67 mg of poly(M-18) in 25 mL of THF was prepared. It was diluted 20-fold. The diluted solution was filled into a quartz glass cuvette. A UV / Vis spectrum was taken. The sample was alternately irradiated at 340 nm and UV / Vis spectra were obtained. The results are shown in Figure 16 . Figure 16 showing the absorption of the single-photon process as a function of wavelength.

[0482] Example 8:

[0483] In the eighth embodiment, an irradiated sample of poly(M-18) according to Example 7 was used. A UV / Vis spectrum was taken. The sample was further irradiated at 275 nm and UV / Vis spectra were alternately obtained. The results are shown in Figure 17 . Figure 17 showing the absorption of the single-photon process as a function of wavelength.

[0484] Example 9:

[0485] In the ninth embodiment, a second polymeric optical material having a copolymer matrix was prepared.

[0486] A molten mixture of 2.00 g of M-18, 9.08 mg of 2-[3-(2H-benzotriazol-2-yl)-4-hydroxyphenyl]ethyl methacrylate, 65.8 mg of ethylene glycol diacrylate, 211.7 mg of 2-hydroxyethyl methacrylate, and 173.92 mg of octadecyl 2-methylacrylate was degassed. Thereafter, 26.42 mg of 1,1'-(3,3,5-trimethylcyclohexylidene)bis[2-(1,1-dimethylethyl)peroxide was added. The mixture was filtered into a 1 mm thick sheet mold. Polymerization occurred thermally under conditions considered suitable by those skilled in the art. After polymerization, the process was ended and the polymer was demolded to produce a 1 mm thick polymer sheet.

[0487] Example 10:

[0488] In the tenth embodiment, a sheet was punched out from a cylindrical blank of the ophthalmic material prepared as in Example 9. A multi-wavelength refractometer with a heating stage was used to measure the refractive index. Before measurement, the sample was heated to 80 °C in the apparatus to release stress from the material. The refractive index was measured at 546 nm and 35 °C. The sample was alternately irradiated at 340 nm, the sample was returned to the refractometer, heated to 80 °C, and the refractive index was measured at 546 nm and 35 °C. The results are shown in Figure 18 . Thus, Figure 18 showing the refractive index change of the single-photon process as a function of the applied energy.

[0489] The samples irradiated at 340 nm were further used in the procedures described herein, but with an irradiation wavelength of 275 nm. The effects shown in Figure 19 were produced by the cleavage or return conversion of the cyclobutane moiety (see Figure 9 ). Figure 19 shows the refractive index change of the single-photon process as a function of the applied energy.

[0490] Examples 11 - 13:

[0491] Examples 11 - 13 below show the refractive index change after single-photon process irradiation of polymer optical materials having copolymer matrices containing polymerized monomer M-58, M-56, or M-15 in the amounts shown in the following table and based on the formulation described in Example 9:

[0492]

[0493] Examples of Irradiation with Two-Photon / Multiphoton Absorption:

[0494] Example 14:

[0495] The experimental apparatus for Example 14 is shown in Figure 11 .

[0496] For Figure 11 the two-photon experiment in, the system (410) incorporated a tunable laser (412) (Ti:sapphire laser (Chameleon Ultra II, from Coherent, Santa Clara, CA, USA)) as the irradiation source, which was configured to produce pulsed laser irradiation. The irradiation beam was expanded in a beam shaper (414).

[0497] Then the pulsed laser irradiation generated by the laser source (412) was transmitted to a microscope objective (416) (LUCPLFLN, from Olympus) to produce a focused laser irradiation output.

[0498] The region of the polymer optical material (sample 418) to have its refractive index changed was targeted via a voice coil-driven linear stage (422) (from ) for positioning the sample holder (420).

[0499] The polymer sample (418) here was a flat button 6.0 mm in diameter of the polymer optical material described below.

[0500] All of the polymer of the polymer sample was a copolymer containing at least a crosslinking agent. The main monomers for each button material used to fabricate the polymer optical material containing the copolymer matrix are summarized in the following table:

[0501]

[0502] During the irradiation process, the flat button of the polymer material as the polymer sample (418) as described above is placed in a fixed position within the sample holder (420). A coupling gel (Vidisic [Bausch & Lomb]) is applied to the button. The sample holder (420) is mounted horizontally, and a laser pulse is focused onto the material using a microscope objective with a high numerical aperture. Refractive index shaping is approximately generated near the surface. This mimics a "bottom-up" and "point-to-point" process.

[0503] The sample holder (420) is driven by the voice coil linear stage (422) as described above. This mimics the scanner movement.

[0504] Typical laser parameters are a wavelength of 680 nm, a pulse duration of 180 fs, and an average power of 500 mW. The varying parameters are the scan speed and the x-spacing between the lines of the layer. These three parameters are adjusted to produce a uniform solid refractive index shaping. The change in refractive index is measured using a multi-wavelength refractometer (ATR-L, from Schmidt & Haensch).

[0505] The results of the two-photon laser experiment are related to the refractive index of the refractive index map electromagnetic energy input dependence of the one-photon experiment.

[0506] Example 15:

[0507] In the fifteenth embodiment, a solution of 288 mg of poly(M-14) (Example 1) in 4 mL of acetonitrile is prepared. The solution is filled into a quartz glass cuvette (32 / GL14 / S / Q / 10, from STARNA, with a path length of 10 mm). The cuvette containing the poly(M-14) liquid solution is irradiated at a wavelength of 680 nm with 1 μJ pulses at a repetition rate of 100 kHz using a NA 0.1 microscope objective. The two-photon generated fluorescence of the solution is measured as a function of the irradiation time using the pulsed irradiation source described earlier. The fluorescence is measured in a 90-degree geometry using a fiber-coupled and diffraction grating-based spectrometer with a sensitivity of 350 to 1050 nm. The fluorescence spectra as the irradiation time increases are compiled in Figure 20 . The two-photon induced [2π + 2π] cyclo-dimerization reaction of the photoactive unit is indicated by the decreasing signal between 400 and 500 nm. The emission peak decreases due to the conversion to a non-fluorescent dimer in poly(M-14).

[0508] The reaction mixture was dried and analyzed by NMR in d-chloroform. Singlets at 4.74 and 4.98 ppm are attributed to the cyclobutane ring formed via the two-photon induced photochemical [2π+2π] cycloaddition reaction. The NMR spectrum is correlated with the NMR spectrum of Example 2. Both the single-photon and two-photon induced photochemical [2π+2π] cycloaddition reactions produced the same product.

[0509] Example 16:

[0510] In the sixteenth example, the irradiated poly(M-14) prepared according to Example 14 in a quartz glass cuvette (32 / GL14 / S / Q / 10, obtained from STARNA, with a path length of 10 mm) was used as an acetonitrile solution (4 mL). The solution was irradiated at a wavelength of 532 nm with 1 μJ pulses at a repetition rate of 100 kHz using a NA 0.1 microscope objective. The amount of the cyclobutane moiety in the substrate decreased over time during the laser irradiation, which was attributed to the two-photon induced photochemical [2π+2π] ring cleavage reaction.

[0511] The reaction mixture was dried and analyzed by NMR in d-chloroform. The singlets at 4.74 and 4.98 ppm in Experiment 14, which were previously attributed to the cyclobutane ring formed via the two-photon induced photochemical [2π+2π] cycloaddition reaction, disappeared. The results of the two-photon induced photochemical [2π+2π] ring cleavage are correlated with the single-photon induced photochemical [2π+2π] ring cleavage experiment of Example 3.

[0512] Example 17:

[0513] In the seventeenth example, a solution of 288 mg of poly(M-14) of Example 1 in 4 mL of acetonitrile was prepared. The solution was filled into a quartz glass cuvette (32 / GL14 / S / Q / 10, obtained from STARNA, with a path length of 10 mm). In this example, the two-photon generated fluorescence from the solution was measured as a function of the irradiation wavelength of the previously described pulsed irradiation source. The cuvette containing the liquid solution of poly(M-14) was irradiated with 1 μJ pulses at a repetition rate of 100 kHz using a NA 0.1 microscope objective. The fluorescence was measured in a 90-degree geometry using a fiber-coupled and diffraction grating-based spectrometer with a sensitivity of 350 to 1050 nm. The peak of the fluorescence spectrum at 420 - 430 nm was determined for each irradiation wavelength and then plotted as a function of the irradiation wavelength in Figure 21 As can be seen in Figure 21 the two-photon induced fluorescence has a high value at approximately 680 nm and decreases with increasing irradiation wavelength. The excitation is maximum when the wavelength is approximately twice the maximum wavelength of single-photon excitation (340 nm). Such observations are typical for two-photon absorption methods.

[0514] Embodiment 18:

[0515] In the eighteenth embodiment, a polymer optical material having a copolymer matrix is prepared. A molten mixture of 4.1 g M-14, 21 mg 2-[3-(2H-benzotriazole-2-yl)-4-hydroxyphenyl]ethyl methacrylate, 143.6 mg 1,18-octadecanediol diacrylate, and 506.7 mg 2-hydroxyethyl methacrylate is first degassed. Afterwards, 52 mg 1,1'-(3,3,5-trimethylcyclohexylene)bis[2-(1,1-dimethylethyl)peroxide is added. The mixture is filtered into a sheet mold with a thickness of 1 mm. Polymerization occurs thermally under conditions known in the art. After polymerization, the process is completed and the polymer is demolded to produce a polymer sheet with a thickness of 1 mm. A cylindrical blank of the optical material is punched out from the sheet.

[0516] Embodiment 19:

[0517] In the nineteenth example, a cylindrical blank of an optical material prepared according to Example 18 was used. The two-photon induced photochemical crosslinking reaction of the optical material was shown. Figure 11 The setup shown uses two different illumination sources as described above. One illumination source is Figure 22 The "kHz" in the figure is a femtosecond laser operating at 680 nm and emitting μJ pulses with a repetition rate of 100 kHz. The second irradiation source, Figure 22 The "MHz" mark in the figure is a femtosecond laser operating at a wavelength of 680 nm and emitting nJ pulses with a repetition rate of 80 MHz. The cylindrical blanks were treated with an average power of 400 mW. After the irradiation treatment, for each measurement, the optical path difference across the sample was measured using an optical phase-sensitive camera. The refractive index of the material in the irradiated area was derived from the optical path difference and the sample thickness. Figure 22 The refractive index changes (Δn) depicted in are obtained by comparing the irradiated and unirradiated areas.

[0518] Subsequent data points from low to high radiation exposure values (= applied energy) receive increasing exposure durations, thereby showing the cumulative effect of the radiation treatment. This cumulative effect allows the physician's requirements to be accurately translated into a corresponding treatment plan.

[0519] Figure 22 The difference in overall system efficiency between kHz and MHz illumination sources is also shown. With all system settings being the same, the kHz system exhibits significantly improved writing speeds, leading to shorter and more desirable processing times. The results indicate that the two-photon-induced photochemical [2π+2π] cyclodimerization reaction is more efficient for the kHz system, which is consistent with the conclusion drawn from the excited state lifetimes described above.

[0520] Example 20:

[0521] In this example, a cylindrical blank of the optical material prepared as per Example 18 was used. The two-photon induced photochemical cross-linking reaction of the optical material using different irradiation wavelengths was shown. The irradiation source used was a femtosecond laser that could be tuned between 666 and 722 nm and emitted μJ pulses at a repetition rate of 100 kHz. The setup shown in Figure 11 was adopted. For each measurement, a 1 mm x 6 mm area on the optical material was processed at an average power of 400 mW with the same total radiation exposure. The refractive index of the material in the irradiated area was deduced from the optical path difference and the sample thickness. Figure 23 The refractive index change (Δn) shown in Figure 23 was obtained by comparing the irradiated and non-irradiated areas.

[0522] Figure 24 Selected examples of the refractive index distribution written in the optical material during this experiment were shown. In this example, the irradiation source operated at 710 nm with 5 μJ pulses at a repetition rate of 100 kHz. Using an optical scanner, a 0.6 mm x 6 mm rectangular area on the optical material was irradiated with spatially overlapping optical pulses. The data was collected with a phase-sensitive camera system mounted on a microscope at a magnification of 10 times. The phase-sensitive camera recorded the optical phase difference with a lateral resolution of 30 μm. By considering the sample thickness, the recorded values were subsequently converted to refractive index changes. Figure 24 It was shown that the refractive index of the irradiated area decreased by approximately 0.011 compared to the surrounding non-irradiated material.

[0523] Index of the Drawings:

[0524] Figure 1 is a schematic diagram of a system for irradiating an intraocular lens, such as a contact lens or an intraocular lens not disposed within a patient's eye.

[0525] Figure 2 is a schematic diagram of a system for irradiating an intraocular lens disposed within a patient's eye.

[0526] Figure 3 A schematic diagram (1500) of the scanning strategy is shown.

[0527] Figure 4 A schematic diagram (1600) of the variables considered for the scanning procedure when irradiating the lens within a patient's eye is shown.

[0528] Figure 5Shows a further schematic diagram of a system for irradiating an intraocular lens disposed within a patient's eye.

[0529] Figure 6 Shows a schematic diagram of components of a system for irradiating an intraocular lens disposed within a patient's eye.

[0530] Figure 7 Shows a schematic diagram of components of a system for irradiating an intraocular lens disposed within a patient's eye.

[0531] Figure 8 Shows a specific [2π + 2π] cycloaddition reaction of poly(M-14).

[0532] Figure 9 Shows a specific cleavage of poly(M-14)-dimer by ring-opening.

[0533] Figure 10 Shows the irradiation setup for Example 5.

[0534] Figure 11 Shows the irradiation setup for Example 14, for example.

[0535] Figure 12 Shows the absorption as a function of wavelength for a single-photon process, as further described in the experimental section, such as in Example 2.

[0536] Figure 13 Shows the absorption as a function of wavelength for a single-photon process as described in Example 3.

[0537] Figure 14 Shows the change in refractive index as a function of the applied energy for a single-photon process as described in Example 5.

[0538] Figure 15 Shows the change in refractive index as a function of the applied energy for a single-photon process as described in Example 5.

[0539] Figure 16 Shows the absorption as a function of wavelength for a single-photon process, as further described in Example 7.

[0540] Figure 17 Shows the absorption as a function of wavelength for a single-photon process as described in Example 8 using the solution of Example 7.

[0541] Figure 18 Shows the change in refractive index as a function of the applied energy for a single-photon process for the bulk polymer of Example 9 containing polymerized M18 as described in Example 10.

[0542] Figure 19 Shows the change in refractive index as a function of the applied energy for the dimer that crosslinks the bulk polymer of Example 9 containing aggregated M18, described in Example 10, for a single-photon process.

[0543] Figure 20 Shows the fluorescence spectrum under increasing irradiation time according to Example 15.

[0544] Figure 21 Shows the peak of the fluorescence spectrum at 420 - 430 nm as a function of the irradiation wavelength, described in Example 17.

[0545] Figure 22 Shows the refractive index change (Δn) as a function of the radiation exposure according to Example 19.

[0546] Figure 23 Shows the refractive index change (Δn) as a function of the radiation exposure according to Example 20.

[0547] Figure 24 Shows a selected example of the refractive index profile written into the optical material during the experiment of Example 20.

Claims

1. A system for irradiating an intraocular lens, the system comprising: One or more irradiation sources (1) for two - photon or multi - photon irradiating the intraocular lens (3) with an irradiation beam (2), the irradiation beam (2) being focused by an optical device (16) and having a first wavelength and a second wavelength different from the first wavelength, A scanner (4) connected to the one or more irradiation sources (1) and configured to scan the irradiation beam (2) across the intraocular lens (3), and An input unit (6) connected to the one or more irradiation sources (1) and the scanner (4), wherein the input unit (6) is configured to input data to process the intraocular lens (3) by scanning the irradiation beam (2) across the intraocular lens (3) based on the input data (8), and Wherein the first wavelength is between 600 nm and 800 nm to locally reduce the polarization degree of the intraocular lens based on the processing of the intraocular lens, and Wherein the second wavelength is between 400 nm and 590 nm to locally increase the polarization degree of the intraocular lens (3) based on the processing of the intraocular lens, Wherein locally adjusting the polarization degree of the intraocular lens includes exposing a first volume of the intraocular lens to the irradiation beam and then exposing a second volume of the intraocular lens to the irradiation beam, wherein the first volume is further away from the cornea of the patient's eye than the second volume.

2. The system according to claim 1, wherein the intraocular lens (3) is a contact lens or an intraocular lens.

3. The system according to claim 1 or 2, wherein the intraocular lens (3) is disposed within the patient's eye.

4. The system according to any one of claims 1 - 2, wherein the input data (8) includes lens data (10) of the intraocular lens (3) and / or treatment plan data (12) related to a treatment plan for the treatment of the intraocular lens (3).

5. The system according to claim 4, wherein the lens data (10) includes data related to the irradiation absorption performance of the intraocular lens (3), and wherein the system is configured to adjust the first wavelength and / or the second wavelength for the intraocular lens to locally change the polarization degree based on a two - photon or multi - photon absorption process.

6. The system according to claim 2, further comprising a positioning system (20) for determining the position of the focus of the irradiation beam (2) within the patient's eye, Wherein the positioning system (20) is connected to the scanner (4), and wherein the scanning of the irradiation beam (2) across the intraocular lens (3) by the scanner is based on the position of the focus of the irradiation beam within the eye.

7. The system according to claim 2 or 6, wherein the system is configured to determine the position and / or orientation of the intraocular lens (3) relative to the eye and the exit of the irradiation beam, and The scanning of the irradiation beam (2) across the intraocular lens (3) by means of the scanner (4) is based on the position and / or orientation of the intraocular lens (3) relative to the eye.

8. The system according to any one of claims 1-2 and 6, further comprising a temperature management unit (14) connected to (i) one or more of the irradiation sources (1) and (ii) one or both of the scanners (4), wherein the temperature management unit (14) is configured to determine the temperature of a portion of the intraocular lens (3) during the processing of the intraocular lens (3) being scanned, based on the irradiation beam performance of the irradiation beam (2) and the intraocular lens performance of the intraocular lens (3), and wherein the system is configured to control (i) one or more of the irradiation sources (1) and (ii) one or both of the scanners (4) based on the determination of the temperature.

9. The system according to claim 8, wherein the temperature management unit (14) is configured to predict the temperature during the processing of the intraocular lens (3), and wherein the input data (8) comprises the predicted temperature.

10. The system according to claim 2 or 6, further comprising an eye interface system (18) configured to hold the patient's eye in a fixed position.

11. A method for adjusting the polarization degree of an intraocular lens comprising a body formed of a polymeric optical material based on a two- or multi-photon absorption process when the intraocular lens is located outside the patient's eye, the method comprising the steps of: providing the intraocular lens; and adjusting the polarization degree of the intraocular lens by irradiation of the intraocular lens using the system according to claim 1, thereby altering the polymeric optical material relative to the non-irradiated polymeric optical material of the intraocular lens, having a significant difference in the UV / Vis spectrum.

12. The method according to claim 11, wherein the adjustment of the polarization degree of the intraocular lens comprises reducing the polarization degree by irradiating the intraocular lens with an irradiation beam having a wavelength between 600 nm and 800 nm, thereby altering the polymeric optical material relative to the non-irradiated polymeric optical material of the intraocular lens, having a significant difference in the UV / Vis spectrum, namely a loss of peak absorption in the range of 300 nm - 400 nm.

13. The method according to claim 11, wherein the adjustment of the polarization degree of the intraocular lens comprises increasing the polarization degree by irradiating the intraocular lens with an irradiation beam having a wavelength between 400 nm and 590 nm, thereby altering the polymeric optical material relative to the non-irradiated polymeric optical material of the intraocular lens, having a significant difference in the UV / Vis spectrum, namely an increase in peak absorption in the range of 300 nm - 400 nm.

14. The method according to claim 11 or 12, wherein the polymeric optical material of the intraocular lens comprises a polymer matrix, the polymer matrix comprises covalently bound photoactive units, and the active units comprise non-aromatic double bonds capable of dimerizing by [2π+2π] cycloaddition to form a cyclobutane ring under the effect of a two-photon or multi-photon process.

15. The method according to any one of claims 11-13, wherein the optical material of the intraocular lens comprises a polymer matrix, the polymer matrix comprises covalently bound photoactive units, and the photoactive units comprise non-aromatic double bonds capable of dimerizing by [2π+2π] cycloaddition to form a cyclobutane ring under the effect of a two-photon or multi-photon process together with the already dimerized photoactive units.

16. The method according to claim 11 or 13, wherein the polymeric optical material of the intraocular lens comprises a polymer matrix, the polymer matrix comprises covalently bound dimerized photoactive units as the only photoactive units capable of separating under the effect of a two-photon or generally multi-photon process.

17. The method according to any one of claims 11-13, wherein the provided intraocular lens comprising a polymer matrix comprises covalently bound photoactive units, the photoactive units comprise non-aromatic double bonds capable of dimerizing by [2π+2π] cycloaddition to form a cyclobutane ring, and the intraocular lens is irradiated with an irradiation beam of the first wavelength to cause dimerization of the photoactive units, thereby reducing the degree of polarization of the intraocular lens and thus modifying the provided intraocular lens, which consists in that the modified intraocular lens comprises a polymer matrix, the polymer matrix comprises partially or fully dimerized photoactive units derived from the [2π+2π] cycloaddition, and optionally irradiating the modified intraocular lens with an irradiation beam of the second wavelength to locally increase the degree of polarization of the modified intraocular lens by partially cleaving the dimerized photoactive units.

18. The method according to claim 16, wherein the provided intraocular lens is irradiated with an irradiation beam of the second wavelength to cause separation of the dimerized photoactive units, thereby increasing the degree of polarization of the intraocular lens and thus modifying the provided intraocular lens, which consists in that the modified intraocular lens comprises a polymer matrix, the polymer matrix comprises photoactive units capable of dimerizing again, and optionally irradiating the modified intraocular lens with an irradiation beam of the first wavelength to locally reduce the degree of polarization of the modified intraocular lens by partially dimerizing the photoactive units.

19. The method according to claim 15, wherein the provided intraocular lens is irradiated with an irradiation beam of the first wavelength to cause dimerization of the photoactive unit, thereby reducing the degree of polarization of the intraocular lens and thereby modifying the provided intraocular lens, which consists in that the modified intraocular lens comprises a polymer matrix, the polymer matrix comprising more photoactive units derived from the [2π + 2π] cycloaddition dimerization, or wherein the provided intraocular lens is irradiated with an irradiation beam of the second wavelength to cause separation of the dimerized photoactive units, thereby increasing the degree of polarization of the intraocular lens and thereby modifying the provided intraocular lens, which consists in that the modified intraocular lens comprises a polymer matrix, the polymer matrix comprising more photoactive units capable of dimerizing by forming a cyclobutane ring by [2π + 2π] cycloaddition.

20. A kit of components comprising the system according to any one of claims 1 - 10 and at least one intraocular lens adapted to the system.

Images