System and method

Abstract

To provide a system for two-photon or multiphoton for irradiation of, generally, an artificial lens, preferably, an intraocular lens, preferably arranged in an eye of a patient, and a method for locally adjusting a polarization property and / or a refractive index of the artificial lens, preferably, the intraocular lens, preferably arranged in the eye of the patient.SOLUTION: A method particularly relates to production of an optical profile by adjusting a polarization property by a non-destructive method or through a two-photon or multiphoton process.SELECTED DRAWING: Figure 1

Description

Technical Field

[0001] The present invention generally relates to a system for two - photon or multi - photon irradiation of an artificial lens, preferably disposed within a patient's eye, preferably an intraocular lens, and a method for locally adjusting the polarization and / or refractive index of an artificial lens, preferably disposed within a patient's eye, preferably an intraocular lens. The method particularly relates to the fabrication of an optical profile by adjusting the polarization through a two - or multi - photon process in a non - destructive manner.

Background Art

[0002] Light - induced changes in material properties are applied in several technical fields such as microfabrication, 3D printing, nanostructures, or two - photon lithography. This can result in various processes such as photopolymerization, light - induced material degradation, or photochemical cross - linking. As a result of these processes, the properties of the irradiated material change. This can potentially change mechanical properties, solubility, transparency, refractive index, etc. In 3D printing (usually a photolithographic approach), a femtosecond laser can be used to polymerize a specific array. This can be done through a photopolymerization reaction. A photosensitizer can be added to make the formulation curable. This can enable printing at a resolution of μm, which may not be possible with general 3D printing techniques. A multi - beam array can be used to increase the manufacturing speed. Nanostructures are also used in the biomedical field. In the field of eye treatment, structured applications are used to modify ophthalmic polymers (such as contact lenses and intraocular lenses (IOLs)), and eye tissues (see, for example, US2018243082A1). When treating an IOL, usually, for example, a photosensitizer in the material is utilized by absorbing UV light. Two or more photon processes can target voxels of the internal material without affecting the surface of the IOL. When irradiated, the photosensitizer can absorb light and supply energy to the surrounding material. In WO2017221068A1, the emitted light is provided in the form of heat to the hydrogel material. This can cause the polymer to degrade and the refractive index to change. Another approach is the formation of non-visual acuity-reducing microcrystals within the material by femtosecond laser irradiation. The higher molecular order of the microcrystals can result in a local increase in density within the material, and consequently a local increase in refractive index, as shown in US2010228345A1.

[0003] US2009143858 describes a method of modifying the refractive index of an optical polymer material, including irradiating selected regions of the optical polymer material in a destructive manner using a focused visible or near-infrared laser having a pulse energy of 0.05 nJ to 1000 nJ, resulting in the formation of a refractive optical structure. The refractive optical structure is characterized by having little or no scattering loss and showing no significant difference in Raman spectrum compared to the non-irradiated optical polymer material used, while having a changed refractive index. US2016081852 describes a method of changing the refractive properties of the eye, which includes applying a photosensitizer to the internal tissue of the eye's cornea, irradiating the cornea so that the photosensitizer promotes cross-linking of the internal tissue of the cornea and activates a cross-linking agent of the internal tissue of the cornea, and modifying the cornea so that the refractive properties of the eye change. US2008004610 describes a specific refractive index adjustable lens and refractive index measurement during treatment by a refractometer. The adjustment described is a destructive method.

[0004] Cataract is the clouding of the eye's lens that can prevent the passage of light. Most cases of cataracts are associated with the aging process. However, a child can be born with cataracts or develop them at an early age. Additionally, cataracts can develop after an eye injury, inflammation, or some other eye diseases. According to the World Health Organization's survey, currently, more than 50 million people worldwide suffer from cataracts, and cataracts are the cause of about half of the world's blindness cases. Although cataracts can be surgically removed, in many countries, surgical services are not accessible, and cataracts remain a major cause of blindness. As the average life expectancy is predicted, the number of people suffering from cataracts is increasing. Therefore, cataracts are an important cause of poor vision in both developed and developing countries. A comprehensive prevention of cataract development is not yet known. When treating cataracts surgically, vision can be restored to normal. The cloudy lens is removed here and replaced with an artificial lens. The artificial lens, as the most up-to-date lens of all, is implanted into the remaining lens capsule after the removal of the natural lens through a small incision, or into the sulcus if there is no lens capsule.

[0005] A typical problem regarding the implantation of IOL is that, considering the optimal vision, the results obtained are not optimal in most cases. The biometric data of the eye before IOL implantation, among which the radius of curvature of the cornea and the length of the eyeball cannot be determined with the desired accuracy. It is currently difficult to predict the positioning of the IOL during surgery, the unpredictable effects due to wound healing, and the postoperative movement of the IOL that occurs within several weeks to months after cataract surgery. There are various approaches and formulas used to predict the IOL power before cataract surgery, but no appropriate solution has been discovered yet.

[0006] In clinical trials dealing with the results of cataract surgery, it has been shown that more than 80% of patients are within 1 diopter (D) of the desired refraction. Nevertheless, many have refractive anomalies and thus require some correction to provide optimized vision. Refractive anomalies after cataract surgery have been shown to be substantially unavoidable, although the magnitude of the refractive anomaly decreases. Problems can also occur in certain situations of the eye, such as when the axial length of the eye is significantly longer or shorter than average. Pediatric cases generally tend to have complications related to refractive power prediction. Power errors of intraocular lenses due to manufacturing tolerances can also contribute to the overall error, especially in the case of high-power IOLs. It should be noted here that according to the applicable ISO 11979 standard, a tolerance of ±0.33 D is allowed on the corneal surface for IOLs over 25.00 D and ±0.66 D for IOLs over 30.00 D.

[0007] Refractive anomaly is defined as an error in the ability of the eye to focus light and is a frequent cause of decreased vision. An eye without refractive anomaly when looking at distant objects is emmetropic. An eye with a refractive anomaly when looking at distant objects is said to be ametropic. Refractive anomalies can be classified into spherical and cylindrical. Spherical anomalies occur when the optical power of the eye is too high or too low to focus light on the retina. Cylindrical anomalies occur when the curvature of two meridians is different. People suffering from refractive anomalies have foggy vision.

[0008] Myopia, also called near-sightedness or short-sightedness, relates to a refractive defect of the eye in which parallel light produces an image in front of the retina when the eye is in a relaxed state. People with myopia can see nearby objects clearly, but distant objects appear blurred. In myopia, the eyeball is too long or the cornea is too steep, that is, the power of the optical part is too high for the length of the eyeball. As a result, the image converges in the vitreous humor inside the eye rather than on the retina. Hyperopia, also known as farsightedness or long-sightedness, relates to a vision defect caused by an imperfection in the eye. The power of the optical part being too low for a particular length of the eyeball can cause the inability to focus on nearby objects. In extreme cases, a person cannot focus on objects at any distance. As an object moves towards the eye, the eye needs to increase its optical power to keep the image in focus on the retina. When the power of the cornea and lens is insufficient, as in hyperopia, the image appears blurred. Astigmatism is an optical defect in which the eye's optical part cannot focus a point object into a sharp, focused image on the retina, resulting in blurred vision. Irregular or toric curvature of the cornea or lens can cause astigmatism. There is a difference in the degree of refractive curvature between two different meridians. In other words, the eye has different foci in different planes. For example, the image is clearly focused on the retina in the horizontal plane but cannot be focused in front of the retina in the vertical plane. The contours in a particular direction may appear blurred, while those in the perpendicular direction may appear clear. People with astigmatism may have difficulty seeing fine details. In some cases, vertical lines (e.g., walls) may appear tilted to the patient. The optical part of astigmatism can often be corrected by glasses, hard contact lenses, or contact lenses with corrective optics.

[0009] There are about six different forms of cataracts, and over 20 causes that can lead to cataracts have been identified. Once diagnosed with a cataract, drug treatment is currently not possible. The only current treatment is to replace the natural lens and then implant an artificial IOL. Today's standard treatment is the foldable IOL. Here, the IOL can be immersed in the aqueous humor of the eye. The optically effective portion of the IOL typically has a diameter between 5 mm and up to 7 mm. Depending on the particular model, elastic loops or brackets are attached to the ends of the optical portion of the IOL. These loops, called haptics, enable the lens to be positioned at the center of the capsular bag and hold the IOL in place. The overall diameter of the IOL is about 12 mm, and its thickness depends on the refractive power and typically varies between 0.7 mm and up to 2 mm. The weight of the IOL is on the order of 50 mg.

[0010] The polymers that can be used to manufacture foldable IOLs can be classified into two subgroups. The IOL can be made of (1) acrylic or methacrylic, or (2) silicone-based polymers. Additionally, hydrophobic and hydrophilic materials can be used for the IOL. Hydrophilic materials can become soft by utilizing water absorption of about 10 - 30%, while hydrophobic materials can be designed to become soft without water absorption. Many variations of IOLs, and many IOLs with various optical profiles (such as multifocal, toric, extended depth of focus, etc.) have been studied and are commercially available. However, currently, it is difficult to determine biometric data with the accuracy required for the IOL to provide promised results.

[0011] Examples of silicon-containing polymers that can be used as optical materials are described in WO2018149857. 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.

[0012] For example, the [2+2] cycloaddition reaction between coumarins can be carried out with light. One coumarin can be photochemically excited and react with the ground state molecules within its range. According to the Jablonski diagram, upon absorption of a photon, an organic molecule becomes an excited singlet state. This can be converted to a triplet state via intersystem crossing. In contrast to the singlet state whose population can be decreased by fluorescence, the triplet state can only decrease its population by non-radiative decay. Therefore, the lifetime of the triplet state in organic molecules such as coumarin is much longer than that of the singlet state. Therefore, in the intermolecular [2+2] cycloaddition reaction of coumarin, its long lifetime enables numerous collisions with other molecules and high specific mobility, enhancing the possibility of the cyclo-dimerization reaction. Thus, the triplet state and its population are the most suitable [T. Wolff et al, Phys. Chem. Chem. Phys., 2004, 6, 368-376].

[0013] Apart from errors due to the measurement of biometric data, it is almost impossible to accurately predict the refraction after an operation / surgery. This is mainly due to unpredictable effects that can occur during the healing process within a few weeks or months after cataract surgery. These effects include, for example, the effect of the pseudophakic anterior chamber depth, which is the conceptual distance between the apex of the cornea and the effective main surface of the IOL. Furthermore, changes in the corneal shape can occur during the healing process. The exact values of these changes can depend on various factors, including the uniqueness of the eye, the IOL type, as well as the surgeon and the instruments used. The uncertainty in the IOL specifications can also make it difficult to predict the correct refraction. After wound healing, treatment, i.e., adjustment of the optical profile of the IOL, can be applied individually, or prescription glasses may be required for patients treated with an IOL to obtain ideal vision. Alternatively, a patient may require contact lenses that match the ideal visual acuity correction of the native lens. In preoperative IOL refractive power prediction, due to currently insurmountable drawbacks, the aim of the systems and methods according to the present disclosure is to provide a solution for non-invasively adjusting the optical profile of an already implanted IOL by changing the polarization of the organic molecules from which the IOL is made. Further, the aim of the systems and methods according to the present disclosure is to provide a solution for creating and / or modifying an artificial lens (which may or may not be placed within a patient's eye), in particular by using a two-photon (or generally multi-photon) process, in particular for modifying the polarization of the artificial lens. Multiphoton excitation is a non-linear phenomenon that requires high intensity to enable simultaneous absorption of photons. In the case of two-photon excitation, excitation occurs with a probability proportional to the square of the intensity of the excitation light. On the other hand, the excitation light collected by the objective lens of a microscope has a light intensity inversely proportional to the square of the distance from the focal plane.

[0014] N.Yonezawa et al, Bull.Chem.Soc.Jpn., 1984, 57, 1608-1611 explains that heat has been shown to induce a thermal cyclo-reversion reaction that adversely affects the yield of the cyclic dimer formed from the photoreaction. SUMMARY OF THE INVENTION

[0015] The inventors have found that the above objectives can be achieved, either individually or in any combination, by the systems and processes of the present application. The present invention relates to a system for irradiating an artificial lens, the system comprising: one or more irradiation sources for two-photon or multi-photon, which irradiate the artificial lens with an irradiation beam focused by an optical unit and having a first wavelength and / or a second wavelength different from the first wavelength, a scanner connected to the one or more irradiation sources and configured to scan the irradiation beam across the artificial lens, and An input unit coupled to one or more irradiation sources and a scanner, the input unit being configured to input data for treating the artificial lens by scanning the irradiation beam across the artificial lens based on input data. The first wavelength is between 600 nm and 800 nm for locally reducing the polarization of the artificial lens based on the treatment of the artificial lens, and the second wavelength is between 400 nm and 590 nm for locally increasing the polarization of the artificial lens based on the treatment of the artificial lens.

[0016] The present invention further relates to a system for irradiating an artificial lens, preferably disposed in a patient's eye, the system comprising: One or more irradiation sources for two-photon or multi-photon that irradiate an irradiation beam having a wavelength between 600 nm and 800 nm, focused by an optical unit, onto the artificial lens. A scanner coupled to one or more irradiation sources and configured to scan the irradiation beam across the artificial lens, and An input unit coupled to one or more irradiation sources and the scanner, the input unit being configured to input data for treating the artificial lens by scanning the irradiation beam across the artificial lens based on input data. The wavelength is for locally reducing the polarization of the artificial lens based on the treatment of the artificial lens.

[0017] The present invention further relates to a system for irradiating an artificial lens, preferably disposed in a patient's eye, the system comprising: One or more irradiation sources for two-photon or multi-photon that irradiate an irradiation beam having a wavelength between 400 nm and 590 nm, focused by an optical unit, onto the artificial lens. A scanner coupled to one or more irradiation sources and configured to scan the irradiation beam across the artificial lens, and including one or more irradiation sources and an input unit connected to a scanner, the input unit being configured to input data for treating the artificial lens by scanning the irradiation beam across the artificial lens based on input data, The wavelength is for locally increasing the polarization of the artificial lens based on the treatment of the artificial lens.

[0018] Figures 1 and 2 show schematic diagrams of the aforementioned system. Figure 1 is a schematic diagram of a system for irradiating an artificial lens, such as a contact lens or an intraocular lens not placed in 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 unit (16) to perform the desired adjustment of the polarization of the artificial lens (3). The positioning system (20) determines the operating position of the focus within the artificial lens (3). Together with the power and the existing optical profile of the artificial lens (3), the position information is part of the input data (8) regarding the artificial lens (3). The lens data (10) and the treatment plan data (12) will be further described below. The temperature management unit (14) predicts and / or measures the temperature of the material of the artificial lens (3) before and / or during irradiation.

[0019] Figure 2 is a schematic diagram of a system for irradiating an intraocular lens placed in a patient's eye. Figure 2 is a schematic diagram of a system for irradiating an intraocular lens disposed within a patient's eye. An irradiation beam (2) emitted by an irradiation source (1) is deflected by a scanner (4) and focused by an optical section (16) to effect a desired polarization adjustment of an intraocular lens (3) within the patient's eye, and the optical section (16) is linked to an eye interface system (18) that holds the patient's eye in a fixed position. A positioning system (20) determines the operative position of a focus within the intraocular lens (3). Together with the power and existing optical profile of the intraocular lens (3), the position information is part of the input data (8) regarding the intraocular lens (3). The lens data (10) and treatment plan data (12) will be further described below. A temperature management unit (14) predicts and / or measures the temperature of the material of the intraocular lens (3) before and / or during irradiation.

[0020] The present invention further relates to a process for adjusting the polarization of an intraocular lens comprising a body formed of a polymeric optical material based on a two- or multi-photon absorption process, the process comprising the following steps: providing the lens; and adjusting the polarization of the lens through irradiation of the lens by using the system according to the present invention described above or, preferably, below, thereby changing the polymeric optical material with a significant difference in the UV / Vis spectrum with respect to the non-irradiated polymeric optical material of the intraocular lens.

[0021] The present invention further relates to a method for locally adjusting the polarization of an intraocular lens comprising a polymeric optical material disposed within a patient's eye, the method comprising: exposing the intraocular lens to an irradiation beam having a wavelength between 600 nm and 800 nm to locally decrease the polarization of the intraocular lens, or exposing the intraocular lens to an irradiation beam having a wavelength between 400 nm and 590 nm to locally increase the polarization of the intraocular lens.

[0022] The present invention also further relates to a method for correcting a patient's vision by modifying the refractive index of an intraocular lens within the eye of the patient, comprising: specifying and measuring the degree of correction of the patient's vision; determining the position and type of refractive structures to be written into the intraocular lens to correct the patient's vision; and 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 polarization of the intraocular lens, or exposing the intraocular lens, or 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 polarization of the intraocular lens.

[0023] The present invention further relates to a kit of parts comprising the system described above, or preferably below, and at least one artificial lens suitable for said system.

[0024] Detailed Description of the Invention Throughout this disclosure, any reference to a body / element / component of a system that is connected to another body / element / component (and potentially additional bodies / elements / components) should be noted to potentially involve one body / element / component that is directly and / or indirectly connected to the other body / element / component.

[0025] The lens or artificial lens within the said disclosure is defined as a contact lens or an intraocular lens. The intraocular lens according to the present invention is a transplantable lens used to replace the eye's natural lens when it is damaged. The type of lens is not limited and may include contact lenses or intraocular lenses. Most preferably, such an artificial lens is an intraocular lens (IOL), which can be, for example, a posterior chamber intraocular lens or an anterior chamber intraocular lens. There is no restriction whatsoever 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 eye's natural transparent lens and usually replaces the removed cataract lens. The latter type is used to supplement the existing lens, functions as a permanent corrective lens, and is implanted in the anterior chamber or posterior chamber to correct refractive abnormalities of the eye. The artificial lens treated by the present invention may include, for example, one or more optics and one or more haptic elements, where one or more optical elements function as a lens and one or more haptic elements are attached to one or more optical elements to hold one or more optical elements in a predetermined position in the eye. The artificial lens treated by the present invention can be of a one-piece design or a multi-piece design depending on whether one or more optical elements and one or more haptic elements are formed from a single material (one-piece design) or are made separately and later joined (multi-piece design).

[0026] The artificial lens, preferably an IOL, may include a polymeric optical material, whereby the optical properties of the lens can be non-invasively changed by a system. Using the system, specifically based on a multiphoton process, the polarization and thus the refractive index can be changed. Preferably, the artificial lens (contact lens or IOL) includes a polymeric optical material as will be further preferably described below, whereby the optical properties of the IOL can be non-invasively changed by a system. Particularly preferably, the artificial lens (contact lens or IOL) consists of a polymeric optical material as will be further preferably described below. Typically, the optical portion of the lens has a diameter of 5 mm to 7 mm and a thickness typically between 0.2 mm and 2.0 mm.

[0027] In this application, input data is defined as all types of data used to create a treatment plan that, as will be explained in more detail in the following description, is to be converted into control commands for the writing process for ophthalmic requirements. During the writing process, the optical pattern is written into the artificial lens by irradiation. The term "control command" refers to a command that directly controls the writing process, as defined previously or preferably as will be explained below. The control command can control, for example, the movement of the scanner. The term "scanner" as used in this description is not part of the input unit according to the present invention. The "scanner" described in this specification is an element of the system according to the present invention that controls the movement of the irradiation beam. Ophthalmic requirements refer to the desired optical profile that must be created within the artificial lens through the system and process according to the present invention.

[0028] The optical profile is the necessary change defined by the surgeon according to the patient's examination results before or after implanting the artificial lens, for example, spherical refractive power change, toric profile, EDOF profile, or 2-, 3-, or multifocal profile, etc., but is not limited thereto. Alternatively, the optical profile is the adjustment of the optical properties of the contact lens. The optical pattern is the necessary change in polarization that causes a change in refractive index in all voxels of the artificial lens.

[0029] The previously defined input data is intended to include common input data, individual input data, or in-process input data. Common input data is intended to include general data that is used by default for systematic reasons. Examples of such common input data will be explained below. Individual input data is all data that is only related to ophthalmic requirements. Examples of such individual input data will be explained below. In-process input data is data that is created and used during the writing process.

[0030] As used herein, the term "positioning system" determines the position of the laser focus within the eye. As part of the positioning system used herein, the term "rating system" determines the position of the artificial lens relative to the system and the patient's eye. The term "irradiation beam" exit defines the position where the irradiation beam leaves the optical part of the system according to the present invention. As used herein as part of the system according to the present invention, the term "optical part" includes all the optical devices necessary to control the spatial distribution of the irradiation source (focus) on the artificial lens. Important parameters of the focus include the lateral focus size (or beam waist) and the focal length (or Rayleigh length). The optical part includes all elements along the optical beam path that determine the focus, such as beam expanders, aperture stops, shutters, and focusing optical parts, particularly microscope objectives or single-element aspherical lenses. Irradiation within the focal volume results in a refractive optical structure characterized by a change in polarization / refractive index in most of the artificial lens or, alternatively, in the polarization / refractive index of the non-irradiated portion of the artificial lens. In other words, changes in polarization / refractive index can be used to form the desired refractive structure patterned within the artificial lens, as described below or preferably described.

[0031] Preferably, a refractive structure is provided that exhibits a change in refractive index and shows little or no scattering loss so that peeling, removal, or destruction of the intraocular lens material is not observed within the irradiation region. The aforementioned irradiation region can take the form of a refractive structure filled with a two- or three-dimensional region or volume that can provide spherical, aspherical, toroidal, or cylindrical correction. In fact, any optical structure can be formed to perform refractive power correction in both physical directions. Further, the optical structure can be vertically stacked or written in separate planes within the artificial lens, as further described below, to function as a single lens element. Multiphoton excitation occurs only near the focus, preferably by using ultrashort laser pulses. The average power is limited by the sample damage threshold, such a threshold being part of the co-input data defined above and below.

[0032] As described above or preferably as described below, the system advantageously enables postoperative and non-invasive adjustment of the optical properties / profile of the implanted IOL to remove visual impairments such as refractive anomalies. Further, when manufacturing an artificial lens (e.g., a contact lens or, for example, before inserting an intraocular lens into a patient's eye), the system advantageously enables the gentle creation of an artificial lens such that it can provide a refractive structure that provides spherical, aspherical, toroidal, or cylindrical correction and / or can maintain the flexibility of the lens even after the creation of the lens is complete. The polarization of the artificial lens is modified based on a two-photon (or generally multiphoton) process that enables adjustment of the optical properties / profile of the artificial lens or enables adjustment of the optical properties in different planes of the artificial lens. Furthermore, modification of the polarization based on a two-photon or multiphoton process can improve the maintenance of the flexibility of the lens when treated at wavelengths from 400 nm to 590 nm. The artificial lens is preferably an IOL.

[0033] Criteria for selection and optimization of system parameters: One ultimate objective of the present invention is to generate local refractive index modification of the implanted IOL as defined by the physician to improve the patient's vision. An important criterion for the refractive index modification procedure is the total treatment time required to obtain the desired result. It is generally recognized that such a procedure should not take more than a few minutes to be recognized as feasible. State-of-the-art systems capable of local refractive index modification do not include an approach for obtaining the actual treatment time of an IOL application.

[0034] Consideration of system trade-offs and limitations: In the case of an implantable artificial lens in general, or a particularly practical and high-performance system that can adjust an IOL, since there are many interdependencies and trade-offs among the subcomponents, it is recognized that those subcomponents need to be treated as a system and thus need to be optimized jointly. The subcomponents include an irradiation source, an optical unit, a scanner, and a treatment plan. An important requirement for optimizing any system / parameters is that when the treatment of the artificial lens is a contact lens, it is the lens material, and when the treatment of the artificial lens is an IOL, it is the lens material and the eye combined with its elements (e.g., the retina) that stay within the safety limits. Such requirements form the basis of the aforementioned common input data. In particular, two main damage mechanisms of the radiation from an irradiation source, preferably a pulsed laser source, can be identified: single-pulse damage (dielectric breakdown and avalanche breakdown) where the lens material and / or the temperature of the eye is subsequently heated due to pulses repeated for the same volume, and thermal damage. For example, the average power of the pulsed irradiation source is relevant to heating and thus to the potential damage to the lens material and / or the eye. Therefore, while the average power of the irradiation source is kept below the threshold of overheating of the lens material and / or the eye, the pulse energy and the pulse repetition rate are in inverse proportion to the product of the pulse energy, and the number of pulses per second (= the reciprocal of the repetition rate) is equal to the average power. The average power is defined as the pulse energy multiplied by the number of pulses per second and is expressed in watts (W). The exposure dose is equal to the beam density (W / cm 2 ). The radiant exposure is equal to the fluence (J / cm 2 ).

[0035] One overall objective is to minimize the treatment time for IOL adjustment after implantation. Theoretically, it is possible to apply increasingly high pulse energies at more frequent pulses (= higher repetition rates), but typically when the average power exceeds 1 watt, dangerous conditions begin to occur in the IOL material and the retina due to overheating. Therefore, in order to stay within the safe operating limits, a preferred radiation exposure can be defined while completing the treatment of the entire IOL volume in a few minutes. The preferred radiation exposure is ≦ 5 kJ / cm 2 , particularly preferably < 1 kJ / cm 2 , and very particularly preferably < 0.3 kJ / cm 2 . The described radiation exposure is further applied to the processes and methods according to the invention, as further explained below. If the treatment plan is too extensive and exceeds the laser safety limits regarding overheating, the treatment can be interrupted to allow for cooling of all the materials and tissues of the artificial lens affected by the treatment. After cooling, the assessment system can compare the voxels treated within the artificial lens with the optical pattern and continue the treatment.

[0036] The process of adjusting the optical properties / profile of the artificial lens through the system and according to the aforementioned requirements is carried out according to the aforementioned treatment plan. According to the treatment plan, for example, toric, spherical, multifocal, or EDOF (extended depth of focus) profiles can be written onto the lens. An algorithm can be utilized to write, for example, into profiles for toric, spherical, multifocal, or EDOF (extended depth of focus) profiles.

[0037] By combining the information on the desired optical profile with common and individual input data, the necessary optical pattern, and the control commands for the irradiation source, optical unit, and scanner of the system described above or preferably below can be calculated. Individual input data includes, for example, lens data such as the laser energy required for a specific refractive index change per voxel of the artificial lens material, and further patient data as the exact position and orientation of the artificial lens within the patient's eye, which is part of the treatment plan data. The control commands can be updated and modified during the writing process by, for example, in-process input data such as temperature data of the patient's eye by IR temperature measurement, irradiation beams, artificial lenses, or in-process positioning data of the eye obtained by, for example, OCT (optical coherence tomography), and / or refractive data obtained from the shine-proof image.

[0038] In a further aspect of the input data, the input data includes lens data of the artificial lens, preferably the intraocular lens, and / or treatment plan data regarding the treatment plan for the treatment of the artificial lens. For example, the lens data may include data regarding the polarization and / or refractive index, shape, diopter, cylinder and sphere of the artificial lens as a function of the position of each volume or part of the artificial lens, and / or one or more of its individual abnormalities in the dimensions. Thus, the polarization can increase or decrease at specific positions or volumes in one or more planes of the artificial lens depending on the current polarization (or refractive index) and the polarization (or refractive index) obtained through the treatment. Furthermore, or alternatively, the lens data may include data regarding one or more of the dimensions (e.g., diameter and / or thickness) of the artificial lens, lens shape, diopter, cylinder, sphere, and / or one or more of its individual abnormalities in the dimensions, and data regarding the material included in the artificial lens, preferably the intraocular lens. Preferably, the lens data includes data regarding one or more dimensions (e.g., diameter and / or thickness) of the artificial lens or IOL, or the polarization and / or refractive index of the artificial lens as a function of the position of each volume or part of the artificial lens, lens shape, diopter, cylinder, sphere, and / or one or more of its individual abnormalities in the dimensions, and data regarding the material included in the artificial lens, which is part of the individual input data set. The preferred materials included in the artificial lens, preferably the intraocular lens, are described below.

[0039] In some examples, the calculation of the treatment plan can generate control commands that result in one or more of the following treatment plan data: Scanning procedure control command data for the scanning of the irradiation beam of the first and / or second wavelength across the artificial lens (e.g., scanning pattern, and / or scanning sequence, and / or scanning speed, and / or scanning duration of the scanning pattern, and / or scanning duration of the scanning sequence, and / or pulse duration of the pulses of the irradiation beam of the first and / or second wavelength (e.g., nanosecond, or picosecond, or femtosecond pulse), and / or irradiation beam profile of the irradiation beam of the first and / or second wavelength, and / or radiation (photon) density, and / or radiation intensity, and / or radiation power, and / or radiation wavelength), in-process input data such as temperature data of the current and / or predicted temperature of the artificial lens during the exposure, refractive index / polarization refractive index / polarization data of the artificial lens obtained based on the exposure, refractive index / polarization obtained particularly with respect to the mapping of the refractive index / polarization obtained at specific locations / coordinates of the artificial lens, incision dimension data of the incision dimension, and eye data regarding the dimensions and / or shape of the patient's eye, positioning data regarding the position and / or orientation of the artificial lens with respect to the eye, and registration data regarding the identification of the patient and / or the specific eye of the patient, etc. individual input data.

[0040] Preferably, the scanning procedure control command data of the scanning procedure is the scanning pattern, and / or scanning speed, and / or pulse duration of the pulse, and / or radiation intensity, as further described below. Next, the parameters of the irradiation beam can be adjusted by the lens data and / or treatment plan data defined herein to accurately (locally) change the polarization / refractive index of the artificial lens as needed. Preferably, the parameters of the irradiation beam are adjusted by the lens data and / or treatment plan data as described above or preferably herein.

[0041] Those skilled in the art are well aware that, in this regard, when the depth of field (Rayleigh length) of the irradiation beam matches the desired thickness of the optical part structure written into the artificial lens, the optimal irradiation focus conditions are achieved. Those skilled in the art are well aware that, in this regard, when the depth of field (Rayleigh length) of the irradiation beam conforms to the local thickness of the artificial lens, the optimal irradiation focus conditions are achieved.

[0042] In a further aspect, the lens data includes data regarding the radiation absorption characteristics of the artificial lens (for example, absorption and / or light attenuation coefficients that may depend on the wavelength of light), and the system is configured to adjust the first wavelength and / or the second wavelength of the artificial lens in order to locally vary the polarization based on a multiphoton absorption process. For example, based on the material used for the artificial lens, a specific wavelength or wavelength range can be input to accurately locally vary the polarization of the artificial lens.

[0043] As part of the system according to the present invention described above and further described below, the input unit is configured to input these input data for treating an artificial lens that may be on a sample holder for the treatment of a contact lens or may be inside a patient's eye for the non-invasive adjustment of an intraocular lens. Accordingly, the present invention further relates to the system described above or below, wherein the input data includes the lens data of the artificial lens and / or treatment plan data regarding the treatment plan for the treatment of the artificial lens. Accordingly, the present invention further relates to the system described above or below, wherein the lens data includes data regarding the radiation absorption characteristics of the artificial lens, and the system is configured to adjust the first wavelength and / or the second wavelength so that the artificial lens locally varies its polarization based on a multiphoton absorption process.

[0044] One or more irradiation sources as part of the system according to the present invention may include one or more pulsed lasers that can be utilized to generate nanosecond pulses, preferably picosecond pulses, more preferably femtosecond pulses. Preferably, one irradiation source is used. Particularly preferably, one or more irradiation sources include one or more pulsed lasers that are used to generate femtosecond pulses. Particularly preferably, one pulsed laser is used to generate femtosecond pulses for use in irradiating the system according to the present invention, or the processes and methods according to the present invention.

[0045] In one aspect of the present invention, one or more irradiation sources include a laser that is adjustable to emit laser beams having first and second wavelengths, respectively. This can be particularly advantageous as a single laser can be used to (locally) increase or decrease the polarization / refractive index of the intraocular lens as needed. Various pulsed laser types are suitable for the irradiation source within the system according to the present invention. MHz lasers as well as kHz lasers are suitable and have specific advantages. For example, an MHz laser system operates with lower pulse energy, but the focused laser spot can be kept on the μm scale (<1 μm to several μm), so it can be used for accurate local index modification in all three dimensions, for example, to generate diffraction structures. A preferred MHz irradiation source is an 80 MHz laser with a pulse energy in the range of 0.1 to 10 nJ. On the other hand, kHz lasers typically operate with higher pulse energies in the range of 0.1 to 10 μJ, so a larger spot size, for example, 10 to 100 μm, is required to avoid damaging the lens material. However, a large laser spot size means that the depth of field is deep (= the Rayleigh length is long) and may be equal to or exceed the thickness of the artificial lens material. In such a case of a long Rayleigh length, it may not be possible to modify the refractive index layer by layer within the IOL and it may only be possible to modify it uniformly along a line around the focus. A preferred kHz irradiation source is a laser with a repetition rate of 100 to 500 kHz. The average power of the foregoing, or preferably the foregoing irradiation source, is preferably between 300 and 600 mW, particularly preferably between 400 and 500 mW.

[0046] In a further aspect of the invention, to generate an irradiation beam having a wavelength outside the ranges given for the first and second wavelengths respectively, the same laser source as the irradiation source is used by doubling the frequency of the supply laser, or an optical power amplifier is used, or another laser source is used.

[0047] The irradiation source as part of the system according to the invention preferably includes a wavelength-variable laser that can provide a variable wavelength in the range of about 680 - 1080 nm, such as a titanium sapphire laser (e.g., Chameleon Ultra II by Coherent, Santa Clara, CA, USA). The system may also include an optical parametric oscillator (e.g., frequency-doubled Chameleon Compact OPO-Vis by Coherent, Santa Clara, CA, USA).

[0048] The irradiation source as part of the system according to the invention particularly preferably includes a femtosecond excitation laser in addition to an optical parametric amplifier. The excitation laser emits an average power >10 watts at 1030 nm with a pulse <350 fs at a repetition rate of 0.1 - 700 kHz. The radiation of the excitation laser is directed towards the optical parametric amplifier, where the excitation laser output is frequency-doubled and optically mixed, resulting in a final adjustable output in the wavelength range of 600 nm - 800 nm. The preferred repetition rate is between 50 and 600 kHz. The particularly preferred repetition rate is between 100 and 500 kHz. The irradiation source, as part of the system according to the present invention, particularly preferably comprises, in combination with an optical parametric amplifier, a femtosecond excitation laser with an average power > 10 watts at 1030 nm, which emits irradiation pulses < 350 fs at a repetition rate of 1 to 700 kHz. The radiation of the pump laser is directed towards an optical parametric amplifier having one or more second harmonic stages, resulting in a final optical output in the wavelength range of 400 nm to 590 nm. The preferred repetition rate is between 50 and 600 kHz. The particularly preferred repetition rate is between 100 and 500 kHz.

[0049] The aforementioned, or preferably the aforementioned laser type, generates a collimated optical beam with a diameter of a few millimeters, which is then directed towards the optical unit and the scanner. The quality of the optical beam (measured in units of M 2 is ideally between 1.0 and 1.5, more ideally between 1.0 and 1.3.

[0050] Multiphoton excitation occurs only near the focus and is preferably generated by using the aforementioned ultrashort laser pulses. The average power is limited by the sample damage threshold, such a threshold being part of the previously defined common input data. The ideal parameters for two-photon induced cyclic dimerization reactions are linked to the pulse duration and repetition rate from the system, and further described or preferably as described below, in relation to the specific time constants of the artificial lens material that can be cyclically dimerized, which are briefly the lifetime of the S1 state of the molecule (~ several ns), the lifetime of the long-lived triplet state (from several ns to > μs), and the specific heat diffusion time (~ 1 μs). Considering the lifetime of the long-lived triplet state, it is advantageous that the pulse interval is longer. The lifetime of the triplet state in the photochemically active group (from many ns to > μs) is much longer than the repetition rate (12.5 ns) of an 80 MHz system. Therefore, since most of the triplet states are cleared before the next pulse is initiated, it is advantageous to use the aforementioned, or preferably the aforementioned kHz laser. This effect results in a significant increase in the efficiency of the cyclic dimerization reaction of the artificial lens material, as will be further preferably explained below. The temperature rise within the focus due to linear absorption, which is referenced by the characteristic thermal diffusion time, relaxes within microseconds, which is approximately 80 times slower than the interval of a typical ~80 MHz pulse. Therefore, the temperature rise is significant. This does not apply to kHz pulses. Here, the thermal diffusion time is 10 times faster than the interval of a typical 100 kHz pulse. Therefore, when irradiating with a constant laser fluence, the local temperature rise due to laser heating is more prominent at higher repetition rates.

[0051] The first wavelength of the irradiation beam within the system according to the present 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 and 710, in order to (locally) reduce the polarization (and thus the refractive index) of the IOL. The second wavelength of the irradiation beam within the system according to the present 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 polarization (and thus the refractive index) of the IOL. Thereby, the polarization can change particularly accurately locally.

[0052] Based on (locally) changing the polarization of the artificial lens, the refractive index of the lens can be (locally) changed. The details of this correlation will be explained below. As explained in one of the examples described below, typical laser parameters are a wavelength of 680 nm, a pulse duration of 180 fs, and an average power of 500 mW.

[0053] Optical part in the system according to the present invention: The main function of the optical part is to focus the irradiation beam emitted from the irradiation source and controlled by the scanner onto the artificial lens. As described above, the important consideration is to keep within the limits given by the laser safety requirements and material damage while minimizing the treatment time, which is the spot size and depth of focus. The most important characteristics of the optical part are given by its effective focal length (EFL), the diameter of the irradiation beam at the entrance aperture of the focusing optical part, and in addition, its numerical aperture (NA). Furthermore, all optical elements in the system according to the present invention should be selected for diffraction-limited or near-diffraction-limited characteristics in order not to substantially degrade the quality of the optical beam. Since the spatial resolution obtained by the spot size is determined, if the ophthalmic needs are different, the required spot size is also different. Ideally, in order to minimize the treatment time while keeping the possibility of material damage low, the spot size is between 1 and 100 μm, more ideally between 50 and 100 μm.

[0054] Scanner in the system according to the present invention: The scanner used in the system according to the present invention may include a galvanometer scanner, a piezo scanner, a rotary scanner, or an acousto-optic modulator, and it may also be digital such as a spatial light modulator, a digital micromirror device, or a stereolithography apparatus. Preferably, the scanner as part of the system of the present invention according to this description is selected from a galvanometer scanner, a piezo scanner, a rotary scanner, an acousto-optic modulator, a spatial light modulator, a digital micromirror device, or a stereolithography apparatus. A preferred galvanometer scanner is a single pivot point scanner. Preferably, the scanner is configured to operate at a scanning speed exceeding 50 mm / s. Thereby, the treatment time can be kept short. In principle, the treatment time should not exceed several minutes, preferably less than 10 minutes, preferably less than 5 minutes, and particularly preferably less than 3 minutes per treatment session. The treatment area can be defined as the volume and size of the artificial lens. Typically, the optical portion of the lens has a diameter of 5 mm to 7 mm and a thickness of typically 0.2 mm to 2.0 mm.

[0055] In order to keep the overall irradiation exposure low and shorten the treatment time while corresponding to the total volume of the artificial lens, the optimal radiation exposure is <1 kJ / cm 2 and more preferably <0.3 kJ / cm 2 is.

[0056] Particularly preferably, a random scan pattern or an interleaved scan line is used to spread the irradiation energy of the irradiation beam. Scanning can be performed in three modes. In a bottom-up scan, with a specific dwell time at each spot, the laser moves from spot to spot (bottom-up, spot-to-spot). Alternatively, in a bottom-up scan, the laser can stay at overlapping spots (bottom-up, spot overlay). Alternatively, the laser can move at a constant speed without staying at any spot (flyby, constant velocity). Figure 3 shows a schematic diagram (1500) of the aforementioned scanning procedure. In one aspect of the scan pattern, the IOL is scanned by the irradiation source as described above, or preferably as described above, by illuminating through the pupil. The IOL contained in the lens capsule during scanning is pre-inserted through the corneal incision using conventional surgical procedures. In this aspect, the entire volume of the IOL is scanned and the scan is performed in a bottom-up manner (i.e., the portion of the IOL further away from the cornea is scanned first), thus creating an optical profile and avoiding unnecessary changes in the refractive index in the optical path.

[0057] As described above, an important consideration when selecting a scanning program is to minimize the artificial lens and / or local heating of the patient's eye, and thus various variables are used in the scanning program. A laser program is created using a specific scanning speed and sequence, taking into account anatomical features such as incisions and pupil size, as well as optical features such as numerical aperture and laser pulse characteristics. In this embodiment, the relationship between the lens coordinates and the eye coordinates is automatically considered. FIG. 4 shows a schematic diagram (1600) of the variables used in the aforementioned scanning program considering irradiating the lens within the patient's eye.

[0058] The parameters of the scanning program and / or treatment plan preferably include the first and second wavelengths, scanning speed and sequence, the position of the lens relative to the eye (e.g., in Cartesian coordinates), the scanning procedure, the resulting refractive index change (optical pattern), the numerical aperture of the objective lens, the incision, the pupil and / or the optical diameter of the lens (about 6 mm in some embodiments), the pulse duration of the laser beam (shape, intensity, and x-y positioning), the safety of the laser when operating the laser, and the centering regarding the position of the lens and the eye.

[0059] In one aspect of the system according to the present invention, the photons generated by the laser are preferably directed through a mirror (e.g., as the optical unit 1) to, for example, a beam expander that creates a beam for a subsequent scanner and focusing optics. After passing through the beam expander, the photons are directed to a scanner (e.g., digitally using a galvanometer scanner, or a piezo scanner, or a rotating scanner, or an acousto-optic modulator, or a spatial light modulator, or a digital micromirror device or a stereolithography apparatus). After passing through the scanner, the laser beam travels through another optical component such as a dividing mirror. In this mode, the dividing mirror splits the beam into a main image beam for artificial lens irradiation and a beam for monitoring beam characteristics and positioning feedback. After the dividing mirror, the optical beam is focused on the artificial lens by an image group or focusing optics. In one aspect, the image group includes a microscope objective lens for obtaining a high numerical aperture (for μm-level spatial resolution) or a low NA optical component for enabling a higher pulse energy at the μJ level.

[0060] The aforementioned or preferably the aforementioned system, in a further aspect of the system, further includes a microscope objective lens coupled to the scanner for focusing the irradiation beam on the artificial lens by the microscope objective lens, and the microscope objective lens has a numerical aperture between 0.1 and 0.8, preferably between 0.2 and 0.5, more preferably between 0.2 and 0.4. Providing a microscope objective lens having such a numerical aperture can enable high irradiation beam quality with respect to the focusing and resolution characteristics of the beam, particularly for use in treating intraocular lenses. The microscope objective lens includes, for example, a typical lens configuration capable of correcting chromatic aberration. The microscope objective lens is preferably linked to an eye interface system, typically a suction system for keeping the patient's eye in a fixed position, as will be further described below. In a further aspect of the objective lens used within the system according to the present invention described above, the objective lens is an Olympus LUCPLFLN objective lens for focusing the irradiation beam on the artificial lens. Accordingly, the present invention further relates to the aforementioned system further including a microscope objective lens coupled to the scanner for focusing the irradiation beam on the artificial lens by the microscope objective lens, and the microscope objective lens has a numerical aperture between 0.1 and 0.8, preferably between 0.2 and 0.5, more preferably between 0.2 and 0.4.

[0061] The alternative focusing optical unit / image group is preferably composed of a single aspherical lens having an effective focal length within 50 to 150 mm and preferably an aperture number of 0.025 to 0.1. Accordingly, the present invention further relates to the aforementioned system further including a focusing optical unit / image group preferably composed of a single aspherical lens having an effective focal length within 50 to 150 mm and preferably an aperture number of 0.025 to 0.1.

[0062] The aforementioned system, or preferably the aforementioned system, in yet a further aspect, further includes a positioning system for determining the position of the focus of the irradiation beam within the eye of the patient, the positioning system being coupled to the scanner, and the scanning of the irradiation beam across the intraocular lens by the scanner being based on the position of the focus of the irradiation beam within the eye. The positioning system may include an evaluation system such as an optical coherence tomography system, a confocal microscope, or a Scheimpflug camera. The positioning system may be coupled to the scanner directly or indirectly. In some embodiments where a confocal microscope is used, the confocal microscope may be directly coupled to the scanner. The aforementioned evaluation system is used to provide local data of the eye to the positioning system to determine the position of the laser focus according to the eye and the intraocular lens. In the case of a confocal microscope, a partially transparent mirror is used to enable a video image.

[0063] The aforementioned, or preferably the aforementioned system, is preferably configured to further determine the position and / or orientation of the intraocular lens relative to the eye and the exit of the irradiation beam, and 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 since the position of the intraocular lens may not be centered relative to the eye, and misalignment can be taken into account when treating the intraocular lens with the irradiation beam.

[0064] Regarding the position of the IOL, it can be considered that at least two coordinate systems are involved: the coordinate system of the eye and the coordinate system of the lens within the eye, because the two cannot be centered with respect to each other. Regarding the position of the IOL, it can be considered that at least two coordinate systems are involved: the x, y, z coordinates of the eye and the x, y, z coordinates of the lens within the eye, because the two cannot be centered with respect to each other.

[0065] In one aspect, the evaluation system creates individual input data. These individual input data contain, for example, data regarding the lens position and / or orientation of the intraocular lens, and / or data regarding the laser beam exit, and / or the optical power mapping of the eye and / or the intraocular lens. These data are used for the calculation of the optical pattern or the continuation of the treatment. Furthermore, it is possible for the evaluation system to create input data during the writing process. These in-process input data contain, for example, data regarding the lens position and / or orientation of the intraocular lens, and / or data regarding the laser beam exit, and / or the optical power mapping of the eye and / or the intraocular lens. These data are used for the in-process modification of the control commands used for the generation of the optical pattern. Accordingly, the present invention further relates to the aforementioned system further comprising a positioning system for determining the position of the focus of the irradiation beam within the eye of the patient, the positioning system being connected to the scanner, and the scanning of the irradiation beam over the artificial lens by the scanner being based on the position of the focus of the irradiation beam within the eye. Accordingly, the present invention further relates to the aforementioned system, the system being configured to determine the position and / or orientation of the artificial lens and the exit position of the irradiation beam with respect to the eye, and the scanning of the irradiation beam over the artificial lens by the scanner being based on the position and / or orientation of the artificial lens with respect to the eye.

[0066] The foregoing system, or preferably the foregoing system, in yet a further aspect, further comprises (i) one or more irradiation sources, and (ii) a temperature management unit coupled to one or both of the scanners, the temperature management unit being configured to determine the temperature of a portion of the artificial lens during the treatment of the artificial lens by the scanning, based on the irradiation beam characteristics of the irradiation beam and the artificial lens characteristics of the artificial lens, the system being configured to control (i) one or more irradiation sources, and (ii) one or both of the scanners, based on the determination of the temperature. Thereby, it may be possible to ensure that the eye and / or the artificial lens are not adversely affected based on the treatment by the irradiation beam. Furthermore, the temperature management unit is preferably configured to predict the temperature during the treatment of the artificial lens, and the input data includes the predicted temperature. Thereby, it may be possible to take preventive measures to ensure that the eye and / or the artificial lens are not adversely affected based on the treatment by the irradiation beam. Alternatively, the temperature management unit is an infrared camera that records the temperature of the eye and correlates the measured data with common data including calibration data to calculate the true temperature of the eye. In another aspect, the temperature dependence of the refractive index is used for temperature control. In these embodiments, the system includes a refractive power mapping device. Based on the deviation of the measured refractive power map and the progress of the writing of the predicted refractive power map, the temperature within the lens can be calculated during the treatment.

[0067] In another aspect, the temperature dependence of the emission spectrum is used for temperature control. In these embodiments, the system includes a UV-Vis spectrometer. Based on the deviation of the measured emission peak wavelength and / or the peak width, the temperature within the focus can be calculated during the treatment. Accordingly, the present invention further relates to the foregoing system comprising (i) one or more irradiation sources, and (ii) a temperature management unit coupled to one or both of the scanners, The temperature management unit is configured to determine the temperature of a part of the artificial lens during the treatment of the artificial lens by the scanning, based on the irradiation beam characteristics of the irradiation beam and the artificial lens characteristics of the artificial lens. The system is configured to control (i) one or more irradiation sources and (ii) one or both of the scanners based on the determination of the temperature. Accordingly, the present invention further relates to the aforementioned system, wherein the temperature management unit is configured to predict the temperature of the artificial lens during the treatment of the artificial lens, and the input data includes the predicted temperature.

[0068] The aforementioned, or preferably the aforementioned system, in a further aspect, further includes an eye interface system configured to keep 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 treatment. The patient may be "docked" to the system in a lying or upright position. Accordingly, the present invention further relates to the aforementioned system including an eye interface system configured to keep the eye of the patient in a fixed position.

[0069] The aforementioned system, or preferably the aforementioned system, in a further aspect, includes a wireless or wired receiver and / or transceiver for one or more of (i) transmitting control commands to one or more irradiation sources, (ii) transmitting control commands to the scanner, and (iii) inputting control command data necessary for creating an optical pattern into the scanner. Thus, one or more light sources and / or scanners may be remotely controllable. Additionally or alternatively, data regarding either or both of the lens data and treatment plan data may be stored external to the system and provided to the system as needed and when needed. In some embodiments, it may be preferable to provide a wired receiver or transceiver to at least control one or more light sources and / or to reduce (or avoid) any latency when transmitting control signals to one or more light sources and / or scanners to control the scanner. In another embodiment, the receiver / transceiver transmits the treatment plan data and lens data to a central processing unit, which calculates the optical pattern and sends it back to the receiver as input data, and the receiver provides it to the system.

[0070] The aforementioned system also or preferably further includes, in a further aspect, a device for locally measuring the refractive power of the artificial lens during the treatment of the artificial lens. Thereby, adjustments to one or more light sources, scanners, and input data can be made during the treatment process. The aforementioned system also or preferably further includes, in a further aspect, a refractometer for locally measuring the refractive index of the artificial lens during the treatment of the artificial lens. Thereby, adjustments to one or more light sources, scanners, and input data can be made during the treatment process.

[0071] Further elements of the system that provide photons may optionally be a cover in which all devices are incorporated, a power unit that provides sufficient energy to the system and all subsystems, and subsystems such as a suction system and / or a cooling device. In addition to the above elements, a controller, firmware, a graphical user interface (GUI), and treatment algorithms may be provided. Connectivity can be established via other ports such as Bluetooth®, Wi-Fi, or RS-232 to connect to the system.

[0072] FIG. 5 shows a further schematic view of a system (100) for the irradiation of an intraocular lens disposed within the eye of a patient (136). The system (100) generally relates to a laser system including at least one femtosecond laser source (102, 104) capable of generating at least one, preferably two different wavelengths. The system (100) further includes a focus or Z-shifter optics (106), a scanner (110) (galvanometer scanner, piezo scanner, rotary scanner, acousto-optic modulator, spatial light modulator, digital micromirror device, or stereolithography apparatus), and an optics (108) for delivering laser pulses to a predetermined area. The system (100) may be capable of achieving the same level of energy as that delivered to a target area of a polymeric material including a photochemically active unit that forms an intraocular lens within the eye of the patient (136). The system further includes, in FIG. 5, an eye interface (112) for fixing the eye of the patient (136). In FIG. 5, the laser system is connected to a computer controller (116) incorporating corresponding device firmware (118) and a front-end graphical user interface (GUI) (120). An algorithm (122) is used to calculate the level of energy delivered to a target area of a polymeric material including a photochemically active unit that forms an intraocular lens in a treatment planning system. System parameters, and a process treatment plan (134) are monitored via the GUI (120). Inputs and adjustments from the patient (136), such as lens data (130), and refractive index formation plan (132) may be input via the GUI (120). The laser source, subsystems, and body fixation (124) may be integrated into a single module connected to power (126) sealed by a cover (128).

[0073] Figures 6 and 7 show schematic diagrams of elements of the system according to the invention described herein. In the embodiment of FIG. 6, the photons generated by the irradiation source (202) pass through a mirror (optical system 1, such as a beam shaper (204), a focus shifter / Z shifter (206)) and are guided to a scanner (208) (for example, a galvanometer scanner, or a piezo scanner, or a rotary scanner, or an acousto-optic modulator, or digital using a spatial light modulator SLM). Attached to the scanner (208) are a microscope objective lens (optical system 2) and a patient interface (210).

[0074] As shown in FIG. 7, the Z shifter (302) includes a first lens (304), a second lens (306), and a third lens (308). Next, the irradiation beam travels to a scanner (310) that includes a plurality of mirrors (312), (314), and (316), thereby being able to change the x-y position of the irradiation beam on the IOL. After passing through the scanner (310), the irradiation beam travels through an imaging split mirror (318) before passing through an image group (320). The system further includes an illumination unit (322) and a patient interface (324).

[0075] This application further describes a process for adjusting the polarization of an artificial lens (preferably at one or more specific locations of the lens) comprising a body formed of a polymeric optical material based on a two- or multi-photon absorption process, the process comprising the steps of: providing the lens; and adjusting the polarization of the lens by using a system described throughout or preferably described in this disclosure, whereby the polymeric optical material is changed with a significant difference in the UV / Vis spectrum with respect to the non-irradiated polymeric optical material of the artificial lens. The artificial lens is preferably a contact lens or an IOL comprising a polymeric optical material described below or preferably described. The process for adjusting polarization according to the present invention, as described above or preferably below, is performed in a non-destructive manner on the artificial lens material. Ultraviolet-visible spectroscopy, or ultraviolet-visible spectrophotometry (UV-Vis or UV / Vis) is known to those skilled in the art. This refers to absorption spectroscopy, or reflectance spectroscopy, of a portion of the ultraviolet spectrum and the entire adjacent visible spectral region. Suitable UV / Vis spectrometers are commercially available. The choice of UV / Vis spectrometer is not critical for the comparison of the UV / Vis spectrum of the original artificial lens and the UV / Vis spectrum of the irradiated artificial lens made according to the present invention, as long as both measurements are made under equivalent conditions known to those skilled in the art. A suitable spectrometer is the PerkinElmer UV / Vis spectrometer Lambda900.

[0076] Next, in some embodiments, the artificial lens may then be inserted into the patient's eye. In some embodiments, the lens may include an intraocular lens such that the polarization of the lens can be adjusted while the lens is positioned in the patient's eye. Within the foregoing process, the adjustment of the polarization property of the artificial lens reduces the polarization property by irradiating the artificial lens with an irradiation beam having a wavelength between 600 nm and 800 nm, and as a result, changes the polymer optical material with a significant difference in the UV / Vis spectrum, i.e., a loss of peak absorption in the range of 300 nm to 400 nm, with respect to the non-irradiated polymer optical material of the artificial lens. Accordingly, the present invention further relates to the foregoing process, wherein the adjustment of the polarization property of the artificial lens reduces the polarization property by irradiating the artificial lens with an irradiation beam having a wavelength between 600 nm and 800 nm, and as a result, changes the polymer optical material with a significant difference in the UV / Vis spectrum, i.e., a loss of peak absorption in the range of 300 nm to 400 nm, with respect to the non-irradiated polymer optical material of the artificial lens.

[0077] Within the foregoing process, the adjustment of the polarization property of the artificial lens increases the polarization property by irradiating the artificial lens with an irradiation beam having a wavelength between 400 nm and 590 nm, and as a result, changes the polymer optical material with a significant difference in the UV / Vis spectrum, i.e., an increase of peak absorption in the range of 300 nm to 400 nm, with respect to the non-irradiated polymer optical material of the artificial lens. Accordingly, the present invention further relates to the foregoing process, wherein the adjustment of the polarization property of the artificial lens increases the polarization property by irradiating the artificial lens with an irradiation beam having a wavelength between 400 nm and 590 nm, and as a result, changes the polymer optical material with a significant difference in the UV / Vis spectrum, i.e., an increase of peak absorption in the range of 300 nm to 400 nm, with respect to the non-irradiated polymer optical material of the artificial lens.

[0078] Accordingly, the present invention further relates to a process for adjusting (preferably at one or more specific positions of the lens) the polarization property of an artificial lens comprising a body formed of a polymer optical material based on a two- or multi-photon absorption process, the process comprising the following steps: providing the lens; and Adjusting the polarization of the lens by using a system including: One or more irradiation sources for two-photon or multi-photon that irradiate the artificial lens with an irradiation beam focused by an optical unit and having a first wavelength and / or a second wavelength different from the first wavelength, A scanner connected to one or more irradiation sources and configured to scan the irradiation beam across the artificial lens, and An input unit connected to one or more irradiation sources and the scanner, where the input unit is configured to input data for treating the artificial lens by scanning the irradiation beam across the artificial lens based on input data, The first wavelength is between 600 nm and 800 nm to locally reduce the polarization of the artificial lens based on the treatment of the artificial lens, resulting in a significant difference in the UV / Vis spectrum for the non-irradiated polymer optical material of the artificial lens, i.e., changing the polymer optical material with a loss of peak absorption in the range of 300 nm to 400 nm, The second wavelength is between 400 nm and 590 nm to locally increase the polarization of the artificial lens based on the treatment of the artificial lens, resulting in a significant difference in the UV / Vis spectrum for the non-irradiated polymer optical material of the artificial lens, i.e., changing the polymer optical material with an increase in peak absorption in the range of 300 nm to 400 nm.

[0079] The specific wavelengths used to decrease and / or increase the polarization of the artificial lens may depend on which specific material or composition can be used for the artificial lens. Any one or more of the polymer optical materials described throughout this disclosure may be used to create and / or provide the lens. The special polymers described below are preferably utilized and are suitable for the fabrication of IOLs that can (non-invasively) change optical properties later by utilizing the ability to change polarization and thus refractive index, preferably when a two-photon or multi-photon process is applied. The special polymer described below is preferably utilized for treatment with the system according to the invention and / or is preferably used during the process according to the invention.

[0080] Two-photon, or multi-photon processes are created by utilizing the system as previously described in detail. The applicable wavelength range of the irradiation source, preferably a pulsed laser, is, as described above, in the range of 600 nm to 800 nm, preferably 650 nm to 750 nm, particularly preferably 670 nm to 720 nm, and very particularly preferably 680 to 710 nm, reducing the polarization and thus reducing the refractive index of the artificial lens. The applicable wavelength range of the irradiation source, preferably a pulsed laser, is, as described above, in the range of 400 nm to 590 nm, preferably 500 nm to 580 nm, particularly preferably 530 nm to 570 nm, increasing the polarization and thus increasing the refractive index of the artificial lens. Thereby, the polarization can be changed particularly accurately locally.

[0081] Hereinafter, the optical material of the artificial lens used during the process according to the invention, preferably the polymer optical material of a contact lens or an IOL, will be further and preferably described with respect to the wavelength range of 600 nm to 800 nm, preferably 650 nm to 750 nm, particularly preferably 670 nm to 720 nm, and very particularly preferably 680 to 710 nm for locally reducing the polarization of the material. To apply this adjustment, the polymer optical material has a refractive index in the range of 1.45 to 1.60. The polymer optical material of the artificial lens (contact lens or IOL) can optionally contain an ultraviolet blocker or a blue light absorber.

[0082] The polymeric optical material of the artificial lens used in the process according to the invention for said adjustment comprises a polymer matrix containing covalently bonded photoactive units, preferably in an amount of at least 2% to 100% by weight, preferably 5% to 90% by weight, most preferably 7% to 80% by weight. The photoactive units within the polymer matrix may be the same or different. The polymer matrix of the polymeric optical material of the artificial lens and / or IOL for said adjustment may be a matrix from a homopolymer, or a copolymer, preferably a copolymer.

[0083] The polymer matrix containing photoactive units may be a matrix from a silicon-containing polymer, an acrylic polymer, a methacrylic polymer, or a mixture thereof.

[0084] Photoactive unit means a photochemically active unit that is photochemically active in the region of the wavelength applicable as described above, or preferably as described above, under the influence of a two-photon, or multi-photon process. The photoactive unit preferably contains a non-aromatic double bond, preferably a carbon-carbon double bond, which can dimerize by forming a cyclobutane ring by [2π + 2π] cycloaddition under the influence of a two-photon, or multi-photon process. Accordingly, the present invention further relates to a process for adjusting the polarization (preferably at one or more specific locations of the lens) of an artificial lens comprising a body formed of a polymeric optical material, said optical material of the artificial lens comprising a polymer matrix comprising a covalently bonded photoactive unit comprising a non-aromatic double bond, preferably a carbon-carbon double bond, capable of dimerizing by forming a cyclobutane ring by [2π+2π] cycloaddition under the influence of a two-photon or multi-photon process. In this aspect, the photoactive units within the polymeric optical material of the artificial lens used in the process according to the invention may be the same or different, but are the only photoactive units within said polymeric optical material and are classified in that they are non-aromatic double bonds, preferably carbon-carbon double bonds, capable of dimerizing by forming a cyclobutane ring by [2π+2π] cycloaddition under the influence of a two-photon or multi-photon process, as described above or more preferably below.

[0085] Alternatively, the polymer matrix comprises the aforementioned or hereinafter described photoactive units together with photoactive units that have already dimerized. Thus, the polymer matrix may still contain photoactive units capable of dimerizing. The polymeric optical material (polymer matrix) may be partially dimerized.

[0086] In said aspect of the optical material of the artificial lens used in the process according to the invention, preferably the polymeric optical material of a contact lens or an IOL, such a material is irradiated in either of the aforementioned first or second wavelength regions to reduce or increase the polarization and thus reduce or increase the refractive index of the artificial lens comprising said polymeric optical material. Such a polymeric optical material enables the polarization of the artificial lens to be adjusted. Accordingly, the present invention further relates to a process for adjusting the polarization properties of an artificial lens comprising a body formed of a polymeric optical material (preferably at one or more specific locations of the lens), said optical material of the artificial lens comprising a polymeric matrix comprising a covalently bonded photoactive unit having a non-aromatic double bond, preferably a carbon-carbon double bond, which can dimerize by [2π+2π] cycloaddition to form a cyclobutane ring under the influence of a two-photon or multi-photon process, together with a photoactive unit that has already dimerized. In this embodiment, the photoactive units in the polymeric optical material of the artificial lens used in the process according to the invention may be the same or different, but are the only photoactive units in said polymeric optical material and are classified in that they comprise a non-aromatic double bond, preferably a carbon-carbon double bond, which can dimerize by [2π+2π] cycloaddition to form a cyclobutane ring under the influence of a two-photon or multi-photon process, as described above or preferably as described below, or in that said photoactive units are their dimerized photoactive units.

[0087] The photoactive units in the polymeric optical material of the artificial lens used in the process according to the invention particularly preferably comprise a non-aromatic carbon-carbon double bond bonded to at least one aromatic ring system which can dimerize by [2π+2π] cycloaddition to form a cyclobutane ring under the influence of a two-photon or multi-photon process. Preferably, the non-aromatic double bond and the aromatic ring system bonded to the non-aromatic double bond form a fused ring system, preferably a bicyclic or tricyclic ring system, particularly preferably a bicyclic ring system, as part of the photoactive unit, as described above.

[0088] Examples of such condensed ring systems linked to the non-aromatic carbon double bond described previously as part of the photoactive unit within the polymeric optical material of the artificial lens used in the process according to the present invention are chromen-2-one, chromen-2-thione, thiochromen-2-one, thiochromen-2-thione, quinolin-2-one, quinolin-2-thione, benzo[b]furan, benzo[b]thiophene, benzo[b]pyrrole, indene, 1,2-dihydronaphthalene, 6,7-dihydro-5H-benzo[7]annulene, (Z)-5,6,7,8-tetrahydrobenzo[8]annulene.

[0089] [2π + 2π] Cycloaddition can be visualized by Scheme 1 below. Figure 8 shows a specific [2π + 2π] cycloaddition reaction of poly(M-14); the representative materials are further described in Examples 1 and 2. Scheme 1 further visualizes the retro-cyclization. Figure 9 shows a specific cleavage of the poly(M-14) dimer by retro-cyclization, which is further described in Examples 3 and 5. Scheme 1:

Chemical Structure

[0090] Examples of silicon-containing polymers that can be used as the optical material of the artificial lens used in the process according to the present invention are described in WO2018149857. Examples of acrylate-containing or methacrylate-containing polymers that can be used as the optical material of the artificial lens used in the process according to the present invention are described in WO2017032442, WO2017032443, WO2017032444, WO2018149850, WO2018149852, WO2018149853, WO2018149855, WO2018149856. All citations are incorporated by reference.

[0091] In one preferred embodiment of the present invention, the polymeric optical material comprising a polymer matrix containing a covalently bonded photoactive unit of the artificial lens used in the process according to the present invention comprises a polymerizable monomer according to formula (1),

Chemical formula

[0092] where the symbols used are as follows: u is 0 or 1, Y is the same or different in each case, O, S, NR 0 , or X 1 and 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; Z is the same or different in each case, O or S; X1 is O, S, or SO2; a is 0 or 1; Sp is alkanediyl, alkenediyl, or alkynediyl and may be substituted with one or more R groups;

[0093] R 0 is a straight-chain or branched alkyl group having 1 to 10 carbon atoms; R 1 、R 2 、R 3 、and R 4 are each independently selected from H, F, Cl, Br, I, a straight-chain or branched alkyl group having 1 to 20 carbon atoms, a partially or fully halogenated straight-chain or branched alkyl group having 1 to 20 carbon atoms, and an aryl or heteroaryl group having 5 to 40 ring atoms; R 5 、R 6 、R 7 、R 8 、and R 9 are each independently selected in each case from F, a straight-chain or branched, non-halogenated, partially or fully halogenated alkyl group having 1 to 20 carbon atoms, a non-halogenated, partially or fully halogenated cycloalkyl group having 3 to 6 carbon atoms, a straight-chain or branched, non-halogenated, partially or fully halogenated alkoxy group having 1 to 20 carbon atoms, and a straight-chain or branched, non-halogenated, partially or fully halogenated thioalkyl group having 1 to 20 carbon atoms;

[0094] X 11 is selected from the group consisting of O, S, O-SO2, SO2-O, C(=O), OC(=O), C(=O)O, S(C=O), and (C=O)S; c is 0 or 1; R 10 、R 11 、R 12 are each independently selected from H, F, a straight-chain or branched alkyl group having 1 to 20 carbon atoms which may be partially or fully halogenated, and an aryl group having 6 to 14 carbon atoms; R is the same or different in each case and is selected from F, OH, a linear or branched alkyl group having 1 to 10 C atoms, a partially or fully halogenated linear or branched alkyl group having 1 to 10 C atoms, a linear or branched alkoxy group having 1 to 10 C atoms, and a partially or fully halogenated linear or branched alkoxy group having 1 to 10 C atoms.

[0095] In one preferred embodiment of the present invention, the polymeric optical material comprising a polymer matrix containing a covalently bonded photoactive unit of an artificial lens used in the process according to the present invention comprises a polymerization monomer according to formula (2),

Chemical formula

[0096] where the symbols used are as follows: u is 0 or 1, Y is the same or different in each case and is O, S, NR 0 , or X 1 and 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; Z is the same or different in each case and is O or S; X1 is O, S, or SO2; a is 0 or 1; Sp is alkanediyl, alkenediyl, or alkynediyl and may be substituted with one or more R groups;

[0097] R 0 is a linear or branched alkyl group having 1 to 10 C atoms; R 1 、R 2 、R 3 、およびR 4 are each independently selected from H, F, Cl, Br, I, a linear or branched alkyl group having 1 to 20 C atoms, a partially or fully halogenated linear or branched alkyl group having 1 to 20 C atoms, and an aryl or heteroaryl group having 5 to 40 ring atoms; R 5 、R 6 、R 7 、R 8 、およびR 9 are each independently selected, in each case, from F, a linear or branched, non-halogenated, partially or fully halogenated alkyl group having 1 to 20 C atoms, a non-halogenated, partially or fully halogenated cycloalkyl group having 3 to 6 C atoms, a linear or branched, non-halogenated, partially or fully halogenated alkoxy group having 1 to 20 C atoms, and a linear or branched, non-halogenated, partially or fully halogenated thioalkyl group having 1 to 20 C atoms, provided that R 5 、R 6 、R 7 、R 8 、またはR 9 if any corresponds to formula (2-1), * indicates the link to the remainder of formula (2),

Chemical formula

[0098] X 11 is selected from the group consisting of O, S, O-SO2, SO2-O, C(=O), OC(=O), C(=O)O, S(C=O), and (C=O)S; c is 0 or 1; R is the same or different in each case and is selected from F, OH, a straight-chain or branched alkyl group having 1 to 10 C atoms, a partially or fully halogenated straight-chain or branched alkyl group having 1 to 10 C atoms, a straight-chain or branched alkoxy group having 1 to 10 C atoms, and a partially or fully halogenated straight-chain or branched alkoxy group having 1 to 10 C atoms.

[0099] Halogenation preferably means fluorination, chlorination, or bromination, particularly preferably fluorination. A straight-chain or branched alkyl group having 1 to 10 C atoms means an alkyl group having 1, 2, 3, 4, 5, 6, 7, 8, 9, or 10 C atoms, for example, 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. All examples of straight-chain or branched alkyl groups having 1 to 10 C atoms include any alkyl group 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, included in straight-chain or branched alkyl groups having 1 to 20 C atoms.

[0100] The term, partially halogenated alkyl group, 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, which means that at least one H atom of the alkyl group is replaced by F. The term, fully halogenated alkyl group, means that all H atoms of the alkyl group are replaced by F, Cl, Br, and / or I. Preferably, the alkyl group is fully fluorinated, which means that all H atoms of the alkyl group are replaced by F. A preferred fully fluorinated alkyl group is trifluoromethyl. The term, halogenated, or preferably, fluorinated, also applies to other groups such as halogenated cycloalkyl groups, halogenated alkoxy groups, or halogenated thioalkyl groups.

[0101] Cycloalkyl groups having 3 to 6 C atoms include cyclopropyl, cyclobutyl, cyclopentyl, and cyclohexyl, which, as previously explained, can be partially or fully halogenated or fluorinated.

[0102] A straight-chain or branched alkoxy group having 1 to 20 C atoms means an O-alkyl group having 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, or 20 C atoms, for example, methoxy, ethoxy, iso-propoxy, n-propoxy, iso-butoxy, n-butoxy, tert-butoxy, n-pentyloxy, 1-, 2- or 3-methylbutyloxy, 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-eicosyloxy, which can be partially or fully halogenated or preferably, partially or fully fluorinated. A preferred fully fluorinated alkoxy group is trifluoromethoxy.

[0103] A linear or branched thioalkyl group having 1 to 20 C atoms is an S-alkyl group having 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, or 20 C atoms, for example, thiomethyl, 1-thioethyl, 1-thio-iso-propyl, 1-thio-n-propoyl, 1-thio-iso-butyl, 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, and may be partially or completely halogenated, or preferably, may be partially or completely fluorinated. A preferred fully fluorinated thioether group is trifluoromethylthioether.

[0104] Preferred alkyl, and alkoxy groups have 1, 2, 3, 4, 5, 6, 7, 8, 9, or 10 C atoms.

[0105] An aryl group in the context of the present invention contains 6 to 40 ring atoms, and a heteroaryl group in the context of the present invention contains 5 to 40 ring atoms containing at least one heteroatom. The heteroatom is preferably selected from N, O, and / or S. An aryl group or heteroaryl group is herein understood to mean either a simple aromatic cycle, i.e., phenyl, or a simple heteroaromatic cycle, for example, pyridinyl, pyrimidinyl, thiophenyl, etc., or a fused (annelated) aryl or heteroaryl group, for example, naphthyl, anthracenyl, phenanthrenyl, quinolinyl, or isoquinolinyl.

[0106] The aryl group or heteroaryl group is preferably benzene, naphthalene, anthracene, phenanthrene, pyrene, benzanthracene, chrysene, perylene, fluoranthene, naphthacene, pentacene, benzopyrene, biphenyl, biphenylene, terphenyl, triphenylene, fluorene, spirobifluorene, dihydrophenanthrene, dihydropyrene, tetrahydropyrene, cis or trans indenofluorene, cis or trans indenocarbazole, cis or trans indolocarbazole, torquene, isotorquene, spirotorquene, spiroisotorquene, 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, naphthoimidazole, phenanthroimidazole, pyridoimidazole, pyrazinoimidazole, quinoxalineimidazole, oxazole, benzoxazole, naphthoxazole, anthroxazole, phenanthroxazole, isoxazole, 1,2-thiazole, 1,3-thiazole, benzothiazole, pyridazine, hexaazatriphenylene, benzopyridazine, pyrimidine, benzopyrimidine, quinoxaline, 1,5-diazaanthracene, 2,7-diazapyrene, 2,3-diazapyrene, 1,6-diazapyrene, 1,8-diazapyrene, 4,5-diazapyrene, 4,5,9,10-tetraazaperylene, pyrazine, phenazine, phenoxazine, phenothiazine, fluorubin, 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,derived from 2,3-triazine, tetrazole, 1,2,4,5-tetrazine, 1,2,3,4-tetrazine, 1,2,3,5-tetrazine, purine, pteridine, indolizine, and benzothiadiazole., An aryl having 6 to 14 C atoms is preferably an aryl group selected from the group consisting of phenyl, naphthyl, or anthryl, particularly preferably phenyl.

[0107] In one particularly preferred embodiment of the present invention, the polymer optical material comprising a polymer matrix containing a covalently bonded photoactive unit of an artificial lens used in the process according to the present invention contains a polymerization monomer according to formula (3),

Chemical formula

[0108] In one particularly preferred embodiment of the present invention, the polymer optical material comprising a polymer matrix containing a covalently bonded photoactive unit of an artificial lens used in the process according to the present invention contains a polymerization monomer according to formula (4),

Chemical formula

[0109] In one particularly preferred embodiment of the present invention, the polymeric optical material comprising a polymer matrix containing covalently bonded photoactive units of the artificial lens used in the process according to the present invention contains a polymerization monomer according to formula (5), [Chemical formula] where u is 0, Y is X 1 , X 11 is selected from the group consisting of O-SO2, SO2-O, OC(=O), C(=O)O, S(C=O), and (C=O)S, c is 1, 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 have the meanings described above.

[0110] R 5 , R 6 , R 7 , R 8 and R 9 are selected from H, F, Cl, Br, I, a linear or branched alkyl group having 1 to 20 C atoms, a linear or branched alkoxy group having 1 to 20 C atoms, a partially or fully halogenated linear or branched alkyl group having 1 to 20 C atoms, a partially or fully halogenated linear or branched alkoxy group having 1 to 20 C atoms, and an aryl or heteroaryl group having 5 to 40 ring atoms, preferably independent of each other, R 5 ~R9 At least one group selected from is a linear or branched alkyl or alkoxy group having 1 to 20 C atoms, which is partially or fully halogenated and can form a compound according to formula (1) or (3). R 5 , R 6 , R 7 , R 8 and R 9 are selected from H, F, Cl, Br, I, a linear or branched alkyl group having 1 to 20 C atoms, a linear or branched alkoxy group having 1 to 20 C atoms, a partially or fully halogenated linear or branched alkyl group having 1 to 20 C atoms, a partially or fully halogenated linear or branched alkoxy group having 1 to 20 C atoms, and an aryl or heteroaryl group having 5 to 40 ring atoms for compounds according to formula (2), (4), or (5), and are preferably independent of each other.

[0111] In the compounds of formula (1), (2), (3), (4), or (5), Sp is preferably unsubstituted. In the compounds of formula (1), (2), (3), (4), or (5), R 11 and R 12 are preferably H. In the compounds of formula (1), (2), (3), (4), or (5), R 10 is preferably H or methyl. In the compounds of formula (1), or (2), R 5 is preferably H. In the compounds of formula (1), or (2), R 6 is preferably H. In the compounds of formula (1), or (2), R 8 is preferably H.

[0112] In the compounds of formula (1), or (2), R 9 is preferably a linear or branched alkyl or alkoxy group having 1 to 6 C atoms that can be partially or fully fluorinated, and X1, a, R5 ~R 8 、and R 10 ~R 12 have the meaning as described above, or preferably as described above. 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, X1, a, R 5 ~R 6 、R 9 , and R 10 ~R 12 have the meaning as described above, or preferably as described above. In the compound of formula (2), (4), or (5), R 1 、R 2 、R 3 、and R 4 are preferably H. In the compound of formula (2) or (4), R 5 、R 6 、R 7 、R 8 、and R 9 are selected from H, F, a straight-chain or branched alkyl group having 1 to 20 C atoms, a straight-chain or branched alkoxy group having 1 to 20 C atoms, a partially or fully halogenated straight-chain or branched alkyl group having 1 to 20 C atoms, and a partially or fully halogenated straight-chain or branched alkoxy group having 1 to 20 C atoms, and are preferably independent of each other. 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 5 、R 6 、R 7 、R 8 、and R 9 are F, or an alkyl group having 1 to 8 C atoms which may be partially or fully fluorinated, and the other substituents are H. In the compound of formula (5), R 5 、R6 , R 7 , R 8 , and R 9 are, as described above, or preferably as described above, in addition to one substituent present in formula (2-1), all preferably H.

[0113] In a further aspect of the present invention, the polymeric optical material containing the polymer matrix of the artificial lens used in the process according to the present invention contains polymerization monomers selected from compounds (M-1) to (M-68) and (A-01) to (A-16): [Chemical formula] [Chemical formula] [Chemical formula] [Chemical formula] [Chemical formula] [Chemical formula] [Chemical formula] [Chemical formula] [Chemical formula] [Chemical formula] [Chemical formula] [Chemistry] [Chemistry]

[0114] In a further aspect of the present invention, the polymer optical material containing a polymer matrix contains a polymerization monomer selected from compounds (M-12), (M-14), (M-15), (M-18), (M-53), (M-55), (M-67), (A-01) to (A-16).

[0115] In a further highly preferred aspect of the present invention, the polymer matrix of the polymer optical material used in the process according to the present invention is a copolymer matrix containing a polymerization monomer containing the aforementioned, or preferably the aforementioned photoactive unit, or the polymerization compounds of the aforementioned formulas (1) to (5), or the polymerization compounds (M-1) to (M-68), and (A-01) to (A-16), and further polymerization monomers known in the art.

[0116] Examples of monomers that may be copolymerized with the monomers described above, or preferably monomers containing the photoactive units described above, before constructing a polymeric optical material for an artificial lens (e.g., a contact lens or an IOL) may be selected from the group consisting of styrene, ethoxyethyl methacrylate (EOEMA), methyl methacrylate (MMA), methyl acrylate, n-alkyl acrylate (n-alkyl group containing 2 to 20 C atoms), n-alkyl methacrylate (n-alkyl group containing 2 to 20 C atoms), i-alkyl acrylate (i-alkyl group containing 3 to 20 C atoms), i-alkyl methacrylate (i-alkyl group containing 3 to 20 C atoms), ethoxyethoxyethyl acrylate (EEEA), 2-hydroxyethyl methacrylate (HEMA), tetrahydrofuryl 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.

[0117] Preferred examples of monomers to be copolymerized with the monomers described above, or preferably monomers containing the photoactive units described above, before constructing the polymeric optical material for artificial lenses (e.g., 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.

[0118] Suitable UV absorbers are 2-(3-(t-butyl)-4-hydroxy-5-(5-methoxy-2-benzotriazolyl)phenoxy)ethyl methacrylate, 3-(3-(t-butyl)-4-hydroxy-5-(5-methoxy-2-benzotriazolyl)phenoxy)propyl methacrylate, 3-(3-t-butyl-5-(5-chlorobenzotriazol-2-yl)-4-hydroxyphenyl)propyl methacrylate 3-(3-(tert-butyl)-4-hydroxy-5-(5-methoxy-2H-benzotriazol-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-methacryloxy-2-hydroxybenzophenone, 2-(2'-hydroxy-3'-methallyl-5'-methylphenyl)benzotriazole, 2-hydroxy-4-methacryloyloxybenzophenone, 4-acryloylethoxy-2-hydroxybenzophenone, 2-[3-(2H-benzotriazol-2-yl)-4-hydroxyphenyl]ethyl methacrylate, 2-(2'-hydroxy-5'-methacrylamidophenyl)-5-methoxybenzotriazole, 2-(2'-hydroxy-5'-methacrylamidophenyl)-5-chlorobenzotriazole, 2-(2'-hydroxy-5'-methacryloxypropylphenyl)benzotriazole, 2-(2'-hydroxy-5'-methacryloylpropyl-3'-tert-butyl-phenyl)-5-methoxy-2H-benzotriazole, 2-(3-(tert-butyl)-4-hydroxy-5-(5-methoxy-2H-benzotriazol-2-yl)3-(1H-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-benzo[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.,

[0119] Preferred UV absorbers are selected from the group consisting of 2-[3’-2’H-benzotriazol-2’-yl)-4’-hydroxyphenyl]ethyl methacrylate (BTPEM), 2-(3-(t-butyl)-4-hydroxy-5-(5-methoxy-2-benzotriazolyl)phenoxy)ethyl methacrylate, 3-(3-(t-butyl)-4-hydroxy-5-(5-methoxy-2-benzotriazolyl)phenoxy)propyl methacrylate, 3-(3-t-butyl-5-(5-chlorobenzotriazol-2-yl)-4-hydroxyphenyl)propyl methacrylate and can be polymerized with monomers according to formula (1), (2), (3), (4), or (5).

[0120] Crosslinking agents suitable for use in copolymers containing polymerization monomers of formula (1), (2), (3), (4), or (5) for constructing the polymeric optical material of an artificial lens (contact lens or IOL) are 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-dodecyl 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-dodecyl dimethacrylate, 1,15-pentadecanediol dimethacrylate, 1,16-hexadecanediol dimethacrylate, 1,18-octadecanediol dimethacrylate, and are selected from the group consisting of these.

[0121] When it is necessary to increase the refractive index, another wavelength region can be applied to an artificial lens (contact lens or IOL) made of one or more polymers capable of changing the polarization property. Wavelengths in the range of 400 to 590 nm, preferably 500 to 580 nm, and most preferably 530 to 570 nm can be used.

[0122] Hereinafter, the optical material of the artificial lens used in the process according to the present invention, preferably the polymeric optical material of a contact lens or IOL, will be further and preferably described with respect to the wavelength region of 400 nm to 590 nm, preferably 500 nm to 580 nm, and particularly preferably 530 nm to 570 nm in order to locally increase the polarization property of the said material. To apply this adjustment, the polymeric optical material has a refractive index in the range of 1.45 to 1.60. The polymeric optical material of the artificial lens (contact lens or IOL) for the adjustment can optionally contain the aforementioned ultraviolet blocker or blue light absorber. The polymeric optical material of the artificial lens used in the process according to the invention for the adjustment comprises a polymer matrix containing covalently bonded dimerized photoactive units, preferably in an amount of at least 2% to 100% by weight, preferably 5% to 90% by weight, most preferably 7% to 80% by weight. The dimerized photoactive units in the polymer matrix may be the same or different. The polymer matrix of the polymeric optical material of the artificial lens and / or IOL for the adjustment may be a homopolymer or a copolymer, preferably a matrix from a copolymer. The polymer matrix containing the dimerized photoactive units may be a matrix from a silicon-containing polymer, an acrylic polymer, a methacrylic polymer, or a mixture thereof.

[0123] The dimerized photoactive unit means a photochemically active unit that is photochemically active in the region of the wavelength of 400 nm to 590 nm, as described above or preferably as described above, under the influence of a two-photon or multi-photon process.

[0124] The polymer matrix of the polymeric optical material of the lens and / or IOL for the adjustment contains dimerized photoactive units that can be separated under the influence of a two-photon or generally a multi-photon process. Accordingly, the present invention further relates to a process for adjusting the polarization property of an artificial lens (preferably at one or more specific positions of the lens) comprising a body formed of a polymeric optical material, wherein the polymeric optical material of the artificial lens comprises a polymer matrix containing covalently bonded dimerized photoactive units as the only photoactive units that can be separated under the influence of a two-photon or generally a multi-photon process.

[0125] Preferably, the dimerized photoactive unit comprises a cyclobutane ring that will be cleaved under the influence of two-photon or generally multi-photon processes. Alternatively, the dimerized photoactive unit preferably comprises a cyclobutane ring that can be cleaved under the influence of two-photon or generally multi-photon processes. Accordingly, the present invention further relates to a process for adjusting (preferably at one or more specific positions of the lens) the polarization of an artificial lens comprising a body formed of a polymeric optical material, wherein the polymeric optical material of the artificial lens comprises a polymer matrix comprising a covalently bonded dimerized photoactive unit comprising a cyclobutane ring as the only photoactive unit that can be cleaved under the influence of two-photon or generally multi-photon processes. Cleavage of the dimerized photoactive unit comprising a cyclobutane ring is visualized in Scheme 1 above.

[0126] In one preferred embodiment of the present invention, the polymeric optical material comprising a polymer matrix comprising the dimerized photoactive unit of the artificial lens used in the process according to the present invention is derived from the polymerization monomers described above, or preferably from the formulas (1), (2), (3), (4) or (5) above. In a further aspect of the present invention, the polymeric optical material comprising a polymer matrix comprising the dimerized photoactive unit of the artificial lens used in the process according to the present invention is derived from polymerization monomers selected from the aforementioned compounds (M-1) to (M-68) and (A-01) to (A-16).

[0127] In a still more preferred embodiment of the present invention, the polymer matrix of the polymeric optical material used in the process according to the present invention is a copolymer matrix comprising the aforementioned, or preferably the aforementioned polymerization monomer comprising the dimerized photoactive unit, or is derived from the polymerization compounds of the aforementioned formulas (1) to (5), or from the polymerization compounds (M-1) to (M-68) and (A-01) to (A-16) and further polymerization monomers known in the art. Examples of monomers, UV absorbers, and crosslinking agents have been described above and are appropriately applied to this polymeric optical material containing the aforementioned, or preferably the aforementioned dimerized photoactive units.

[0128] During the production of the artificial lens used in the process according to the present invention, the polymer matrix containing partially or fully dimerized photoactive units can dimerize by one-photon absorption, or two-photon, or generally multi-photon absorption of photoactive units that can dimerize by forming a cyclobutane ring by [2π+2π] cycloaddition, as described above, or preferably as described above. When the process according to the present invention is applied to the eye, two-photon (or generally multi-photon) absorption can be used. For manufacturing an artificial lens comprising a polymeric optical material comprising a polymer matrix containing partially or fully dimerized photoactive units used in the process according to the present invention, two-photon (or generally multi-photon) absorption, or one-photon absorption can be used via any irradiation means such as a UV lamp with a special wavelength filter, a UVLED having one of the wavelengths specified above, or a laser having the wavelength specified above. For manufacturing an artificial lens comprising a polymeric optical material comprising a polymer matrix containing partially or fully dimerized photoactive units used in the process according to the present invention, one-photon absorption is preferably used via any irradiation means such as a UV lamp with a special wavelength filter, a UVLED having one of the wavelengths specified above, or a laser having the wavelength specified above.

[0129] For the production of an artificial lens comprising a polymeric optical material comprising a polymer matrix containing partially or fully dimerized photoactive units used in the process according to the present invention, the same irradiation source as described for the system according to the present invention above can be used by doubling the frequency of the seed laser, or an optical power amplifier can be used, or another irradiation source can be used. Preferably, another irradiation source is used for the production of the artificial lens.

[0130] The present invention further relates to a process for adjusting the polarization of an artificial lens comprising a body formed of a polymeric optical material, based on a two- or multi-photon absorption process, the process comprising the following steps: providing said artificial lens; and adjusting the polarization of said lens through irradiation of said lens by using the foregoing, or preferably the foregoing system, wherein the artificial lens provided comprises a polymer matrix comprising covalently bonded photoactive units comprising non-aromatic double bonds capable of dimerizing by forming a cyclobutane ring by [2π + 2π] cycloaddition, as described above, or preferably as described above, and the artificial lens provided is irradiated with an irradiation beam of a first wavelength, said irradiation causing dimerization of said photoactive units, thereby reducing the polarization of said artificial lens, thereby modifying the artificial lens provided, the modified artificial lens comprising a polymer matrix comprising partially or fully dimerized photoactive units derived from said [2π + 2π] cycloaddition, and optionally irradiating said modified artificial lens with an irradiation beam of a second wavelength to locally increase the polarization of said modified artificial lens by partially cleaving said dimerized photoactive units.

[0131] The present invention further relates to a process for adjusting the polarization of an artificial lens comprising a body formed of a polymeric optical material, based on a two- or multi-photon absorption process, the process comprising the following steps: providing said artificial lens; and adjusting the polarization of said lens through irradiation of said lens by using the foregoing, or preferably the foregoing system, wherein the artificial lens provided comprises a polymer matrix comprising covalently bonded dimerized photoactive units comprising the only photoactive units capable of separating under the influence of the foregoing, or preferably the foregoing two-photon or generally multi-photon process, The provided artificial lens is irradiated with an irradiation beam of a second wavelength, and the irradiation causes separation of the dimerized photoactive units, thereby increasing the polarization of the artificial lens, thereby modifying the provided artificial lens, and the modified artificial lens includes a polymer matrix including photoactive units that can dimerize again, and optionally, the modified artificial lens is irradiated with an irradiation beam of a first wavelength to locally reduce the polarization of the modified artificial lens by partially dimerizing the photoactive units.

[0132] The present invention further relates to a process for adjusting the polarization of an artificial lens including a body formed of a polymeric optical material based on a two- or multi-photon absorption process, the process including the following steps: providing the artificial lens; and adjusting the polarization of the lens through irradiation of the lens by using the aforementioned, or preferably the aforementioned system. Here, the provided artificial lens includes a covalently bonded photoactive unit including a non-aromatic double bond that can dimerize by forming a cyclobutane ring by [2π + 2π] cycloaddition under the influence of a two-photon or multi-photon process together with the already dimerized photoactive units as described above, or preferably as described above, and, the provided artificial lens is irradiated with an irradiation beam of a first wavelength, and the irradiation causes dimerization of the photoactive units, thereby reducing the polarization of the artificial lens, thereby modifying the provided artificial lens, and the modified artificial lens includes a polymer matrix including more dimerized photoactive units derived from the [2π + 2π] cycloaddition, or, The provided artificial lens is irradiated with an irradiation beam of a second wavelength, the irradiation causing separation of the dimerized photoactive units, thereby increasing the polarization of the artificial lens, thereby modifying the provided artificial lens, and the modified artificial lens can dimerize by forming a cyclobutane ring by [2π + 2π] cycloaddition and includes a polymer matrix containing more photoactive units.

[0133] The present invention further relates to a method for locally adjusting the polarization of an intraocular lens disposed in a patient's eye and containing the aforementioned, or preferably the aforementioned, polymer optical material, the method including the following: Preferably, using the aforementioned system and / or process, exposing the intraocular lens to an irradiation beam having a wavelength between 600 nm and 800 nm to locally decrease the polarization of the intraocular lens, or, Exposing the intraocular lens to an irradiation beam having a wavelength between 400 nm and 590 nm to locally increase the polarization of the intraocular lens.

[0134] The present invention further relates to a method for locally adjusting the polarization of an intraocular lens disposed in a patient's eye and containing the aforementioned, or preferably the aforementioned, polymer optical material, the method including the following: Preferably, using the aforementioned system and / or process, exposing the intraocular lens to a first irradiation beam having a first wavelength between 600 nm and 800 nm to locally decrease the polarization of the intraocular lens, and, Exposing the intraocular lens to a second irradiation beam having a second wavelength between 400 nm and 590 nm to locally increase the polarization of the intraocular lens.

[0135] The present invention further relates to a method for locally adjusting the polarization of an intraocular lens disposed in a patient's eye and including the aforementioned, or preferably the aforementioned, polymeric optical material, wherein exposing the intraocular lens is based on input data regarding the lens data of the intraocular lens, particularly regarding the polymeric optical material, and / or treatment plan data regarding a treatment plan for treating the intraocular lens based on exposing the intraocular lens to the irradiation beam, and includes scanning the irradiation beam across the intraocular lens.

[0136] The present invention further relates to a method for locally adjusting the polarization of an intraocular lens disposed in a patient's eye and including the aforementioned, or preferably the aforementioned, polymeric optical material. Lens data includes data regarding one or more dimensions (e.g., diameter and / or thickness), material, particularly the polymeric optical material included in the aforementioned, or preferably the aforementioned, intraocular lens, the refractive index of the intraocular lens, and the mapping of the refractive index for specific locations / coordinates of the intraocular lens.

[0137] The present invention further relates to a method for locally adjusting the polarization of an intraocular lens disposed in a patient's eye and including the aforementioned, or preferably the aforementioned, polymeric optical material, wherein the treatment plan data includes one or more of the following: Scanning procedure control command data for the scanning of the irradiation beam across the intraocular lens (e.g., scanning pattern and / or scanning sequence and / or scanning speed and / or scanning duration of the scanning pattern and / or scanning duration of the scanning sequence and / or pulse duration of the pulses of the irradiation beam of the first and / or second wavelength and / or irradiation beam profile of the irradiation beam and / or radiation (photon) density and / or radiation intensity and / or radiation power and / or radiation wavelength), Temperature data of the current and / or predicted temperature of the intraocular lens during the exposure Refractive index data of the refractive index obtained based on the exposure, particularly refractive index data of the refractive index obtained regarding the mapping of the refractive index obtained for specific positions / coordinates of the intraocular lens Incision dimension data of the incision, Eye data regarding the dimensions and / or shape of the patient's eye, Positioning data regarding the position and / or orientation of the intraocular lens with respect to the eye, and Registration data regarding the identification of the patient and / or a particular eye of the patient.

[0138] The present invention further relates to a method for locally adjusting the polarization of an intraocular lens disposed in a patient's eye, which comprises the aforementioned, or preferably the aforementioned, polymeric optical material, wherein exposing the intraocular lens to the irradiation beam includes exposing a first volume of the intraocular lens before exposing a second volume of the intraocular lens, and the first volume is further away from the patient's eye's cornea than the second volume.

[0139] The present invention further relates to a method for locally adjusting the polarization of an intraocular lens disposed in a patient's eye, which comprises the aforementioned, or preferably the aforementioned, polymeric optical material, wherein the (first) wavelength is between 650 nm and 750 nm, preferably between 670 nm and 720 nm, more preferably between 680 nm and 710 nm. The present invention further relates to a method for locally adjusting the polarization of an intraocular lens disposed in a patient's eye, which comprises the aforementioned, or preferably the aforementioned, polymeric optical material, wherein the (second) wavelength is between 500 nm and 580 nm, preferably between 530 nm and 570 nm. In the above section, the first step of the method can be to provide the intraocular lens.

[0140] In an embodiment, exposing the intraocular lens to the irradiation beam includes exposing a first volume, and / or plane, and / or position of the intraocular lens before exposing a second volume, and / or plane, and / or position of the intraocular lens, where the first volume, and / or plane, and / or position is further away from the cornea of the patient's eye than the second volume, and / or plane, and / or position, and the volume, and / or plane, and / or position irradiated at a later point in the irradiation sequence can be closer to the cornea than the volume, and / or plane, and / or position irradiated at an earlier point. The volume can thereby be associated with one or more planes of the intraocular lens.

[0141] The lens data and treatment plan data are preferably as described above and are preferably part of a system preferably used in a method of locally adjusting the polarization of an intraocular lens containing the aforementioned or preferably the aforementioned polymeric optical material to be placed in the patient's eye as described above.

[0142] The present invention further relates to a method for correcting a patient's vision by modifying the refractive index of an intraocular lens in the patient's eye containing the aforementioned or preferably the aforementioned polymeric optical material, specifying and measuring the degree of correction of the patient's vision; determining the position and type of the refractive structure to be written into the intraocular lens to correct the patient's vision; and preferably, by using the aforementioned system and / or process for exposing the intraocular lens to the irradiation, then exposing the intraocular lens to two - photon or multi - photon irradiation having a wavelength between 600 nm and 800 nm to locally decrease the polarization of the intraocular lens, and / or then exposing the intraocular lens to two - photon or multi - photon irradiation having a wavelength between 400 nm and 590 nm to locally increase the polarization of the intraocular lens.

[0143] As outlined above, a change in polarization results in a change in refractive index, as will be explained in more detail below. The speed of light c0 in a vacuum is a fundamental constant that describes the speed of electromagnetic waves in a vacuum. From 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. These are also fundamental constants.

Number

Number

[0144] The relative permittivity ε r (also called the dielectric constant) is a dimensionless material-dependent quantity that gives the permittivity relative to the electric constant. Thus, the relative permittivity of a vacuum is ε r = 1, which can also be confirmed by comparing the two above equations. Next, the actual permittivity is calculated by multiplying the relative permittivity by ε0.

Number

Number

[0145] The relative permittivity, also called the dielectric constant, explains how the electric field strength decreases when a material, also known as a dielectric, is placed in an electric field. The relative permittivity is determined by 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 up to 10,000 are known. To give some examples, the relative permittivities of polystyrene, cellulose, and water are 2.5, 4.5, and 81, respectively. The relative permittivity of air can be considered as 1, which is a suitable approximation. Generally, the relative permittivity is not constant as it can vary depending on the frequency, humidity, temperature, and other parameters of the applied field. In non-linear media, the permittivity may depend on the strength of the electric field. Therefore, the old term "dielectric constant" for ε is ambiguous and should no longer be used. r Dielectrics with ε r are known. To give some examples, the relative permittivities of polystyrene, cellulose, and water are 2.5, 4.5, and 81, respectively. The relative permittivity of air can be considered as 1, which is a suitable approximation. Generally, the relative permittivity is not constant as it can vary depending on the frequency, humidity, temperature, and other parameters of the applied field. In non-linear media, the permittivity may depend on the strength of the electric field. Therefore,

[0146] In the case of a magnetic field, the values μ0, μ r , and μ are defined similarly to the corresponding values of the electric field. The permeability is

Number

Number

[0147] The refractive index n is a material constant that characterizes the refractive properties of the medium. As previously introduced, the refractive index is the ratio of the speed of light in a vacuum to the speed of light in a given medium. As a result, a vacuum has a refractive index of 1. The refractive index of water is 1.333. The refractive index of commercially available glass products ranges from 1.4 to 1.9. Most organic polymers have a refractive index between 1.4 and 1.6, and specially modified high refractive index polymers have a refractive index exceeding 1.7. The refractive index generally depends on the frequency of light and is a phenomenon called scattering. The refractive index of dry air (n air ≈ 1.0003) is only slightly different from 1, so measurements corresponding to appropriate approximations for air can be made. In technical optics, the refractive index n 0 is used. This is defined as follows.

Number

[0148] The following relationship is obtained.

Number

Number

[0149] This means that the refractive index of the polymer / copolymer changes as its relative permittivity ε r varies. To understand the relative permittivity and how the refractive index of the polymer / copolymer can be modified thereby, it is necessary to examine in detail what happens when light waves interact with matter. The electric field, in this case the electric component of the light wave,

Number

Number

Number

Number

Number

Number

[0150] Polar vector

Number

Number

Number

Number

Number

[0151] The electric susceptibility has been defined previously. It is necessary to distinguish two types of polarities: displacement polarity and orientation polarity. Displacement polarity occurs when the charges of neutral atoms or molecules are displaced relative to each other. That the normal shape is distorted by an external electric field, i.e., the electric field induces an electric dipole moment, is a relative tendency of the charge distribution, such as the electron cloud of an atom or molecule. Orientation polarity occurs by orienting permanent dipoles along the electric field lines. These dipoles have existed in the medium before the electric field is applied. In the visible spectrum range, only the orientation polarity of electrons is considered. The frequency of visible light is relatively high, in the range of about 10 14 Hz to 10 15 Hz. Therefore, the factors contributing to the overall polarity caused by atomic displacement and the orientation of permanent dipoles are very small and can be ignored. Only electrons can "follow" the rapidly oscillating electric field. For displacement polarity, the equation [Number] provides the relationship between the number of particles x per unit volume and the polarity. The proportionality constant α in this equation is called the electric polarizability. The polarizability is a molecular parameter. Quantum particles are not strongly connected to each other, but rather are bound to their equilibrium positions by elastic forces in the first approximation. Therefore, Newton's law F = -kx applies. The external electric field [Number] exerts a force of Q·E on such a charge Q. This force deflects the charge by a distance x = F / k = QE / k. This displacement causes the following induced dipole moment. [Number]

[0152] Comparing, it can be easily seen that α must be proportional to ε r which is proportional to ε.

Mathematics

[0153] It should be pointed out that variations of the embodiments described in the present invention are within the scope of the present invention. Any feature disclosed in the present invention may be replaced with an alternative feature that serves the same purpose, or an equivalent or similar purpose, unless explicitly excluded. Therefore, any feature disclosed in the present invention should be considered as an example of a general series or as an equivalent or similar feature, unless otherwise specified. All features of the present invention can be combined with each other in any way, provided that the specific features and / or steps are not mutually exclusive. This particularly applies to the preferred features of the present invention. Similarly, features of non-essential combinations can be used individually (not in combination). It should also be pointed out that many of the features, particularly those of the preferred embodiments of the present invention, are inventions in themselves and should not be regarded merely as some of the embodiments of the present invention. For these features, independent protection may be sought in addition to or as an alternative to any of the present inventions.

[0154] The technical teachings disclosed in the present invention can be abstracted and combined with other examples. Surely, many other effective alternatives will come to the mind of those skilled in the art. It is understood that the present invention is not limited to the embodiments described and includes modifications that are obvious to those skilled in the art and within the scope of the claims appended hereto.

Brief Description of the Drawings

[0155]

Figure 1

Figure 2

Figure 3

Figure 4

Figure 5

Figure 6

Figure 7

Figure 8

Figure 9

Figure 10

Figure 11

[0156]

Figure 12

Figure 13

Figure 14

Figure 15

Figure 16

Figure 17

Figure 18

Figure 19

Figure 20

Figure 21

Figure 22

Figure 23

Figure 24

Mode for Carrying Out the Invention

[0157] The present invention is illustrated in detail by the following examples without intending to limit it thereby. The following examples are also included in the present disclosure and can be fully or partially incorporated into the aspects of the present invention and the general disclosure. The operation of the UV / Vis spectrum in a single-photon experiment is carried out by placing a cuvette containing the dissolved sample in a sample holder and then irradiating the cuvette. The change in the UV / Vis spectrum is monitored over time by UV / Vis measurement, for example, using a UV / Vis spectrometer Lambda 900 (PerkinElmer). As described below, the operation of the refractive index in a single-photon experiment is performed by placing the sample in a sample holder and preferably irradiating it for 30 seconds. The resulting change in the refractive index is monitored over time by refractive index measurement. The change in the refractive index is measured with a multi-wavelength refractometer (ATR-L of Schmidt & Haensch). The single-photon experiment shows that the described polymeric optical material for an artificial lens used in the process according to the invention can locally change the initial polarization through irradiation at specific first and second wavelengths, causing, for example, [2π + 2π] cycloaddition or retro-cyclization as described above or below. Alternatively, the artificial lens can be treated based on a multi-photon (e.g., two-photon) process as further described below in Examples 14 - 19. Examples Example 1

[0158] Preparation of poly(M-14): First, 1 g of M-14 is dissolved in 10 mL of chloroform. Next, the solution is degassed and 1.33 mg of AIBN is added. Next, the mixture is stirred at 60 °C for 14 hours. Then, the polymer is precipitated in 250 mL of methanol. Next, the obtained polymer, poly(M-14), is dried. Example 2

[0159] In the second embodiment, a solution of 75.4 mg of poly(M-14) in 10 mL of THF is prepared. It is diluted 500-fold. The diluted solution is filled into a quartz glass cuvette (32 / GL14 / S / Q / 10, manufactured by STARNA, path length 10 mm). The UV / Vis spectrum is obtained by using a UV / Vis spectrometer Lambda 900 (PerkinElmer). The sample is alternately irradiated at 340 nm, and the UV / Vis spectrum is obtained. The results are shown in Figure 12, showing the absorption as a function of the wavelength of the single-photon process. There are three isosbestic points in Figure 12. This indicates a controlled conversion. The photochemical reaction indicated by the conversion is a [2π + 2π] cycloaddition, and as shown in Figure 8, it becomes a crosslinked polymer. The dimerization of the photoactive unit is indicated by the decreasing signal at 332 nm. The signal intensity increases in the range of 260 nm to 275 nm.

[0160] The reaction mixture is dried and analyzed by NMR. 1 HNMR (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 The 1 The singlets at 4.72 and 4.96 ppm in the 1H NMR spectrum are assigned to the cyclobutane rings formed via the photochemical [2π + 2π] cycloaddition reaction. These two signals are due to the formation of a mixture of photodimers composed of syn and anti, each in head-to-head and head-to-tail arrangements. The NMR signals and conclusions are consistent with the literature [Rao et al., Chem. Ber., 1973, 106(2), 388]. Example 3

[0161] In the third example, the irradiated poly(M-14) created by Example 2 is used. A UV / Vis spectrum is obtained. The sample is irradiated at 275 nm, and the UV / Vis spectrum is obtained alternately. The results are shown in Figure 13, showing the absorption as a function of the wavelength of the single photon process. The experiment shows that a typical polymer optical material can cleave a photoactive unit dimerized. The amount of cyclobutane moieties in the crosslinked poly(M-14) decreases. The mechanism of the cleavage is shown in Figure 9. The backconversion is indicated by the increasing signal at 332 nm.

[0162] The reaction mixture is dried and analyzed by NMR. 1 HNMR (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 As further seen, the singlets at 4.74 and 4.98 ppm previously assigned to the cyclobutane ring formed via the photoinduced photochemical [2π + 2π] cycloaddition reaction in Example 2 disappear, demonstrating the cleavage as shown in Figure 9. 1 The experiment shows that a typical polymer optical material can cleave a photoactive unit dimerized. Example 4

[0163] In the fourth example, a polymer optical material with a copolymer matrix is created.

[0164] 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 are first degassed. Then, 25.57 mg of 1,1'-(3,3,5-trimethylcyclohexylidene)bis[2-(1,1-dimethylethyl) peroxide] is added. The mixture is filtered and placed into a 1 mm thick sheet form. Polymerization is thermally initiated under conditions considered appropriate by those skilled in the art. After the polymerization process is complete, the polymer is demolded to obtain a 1 mm thick polymer sheet. Example 5

[0165] In the fifth example, a cylindrical blank of the polymer optical material created according to Example 4 is punched out from the sheet. For the determination of the refractive index, a multi-wavelength refractometer with a heating stage is used. Before measurement, the blank is heated to 80 °C within the device to release stress from the material. The refractive index measurement is performed at 546 nm and 35 °C in this example. Outside the refractometer, within the device shown in FIG. 10, the blank is irradiated at 340 nm. The sample is returned to the refractometer, heated to 80 °C, and the refractive index is measured at 546 nm and 35 °C. FIG. 14 shows the change in the refractive index of the single-photon process as a function of the applied energy. As the applied energy increases, the refractive index of the irradiated polymer optical material decreases. This is due to the cross-linking reaction shown in FIG. 8. Through the cycloaddition reaction shown in FIG. 8, a low-birefringence photoactive unit (cyclobutane ring) is obtained, resulting in a decrease in the refractive index. The sample irradiated at 340 nm is further used in the procedure described herein, but the irradiation wavelength is 275 nm.

[0166] The effect shown in FIG. 15 is due to the cleavage or back-conversion of the cyclobutane moiety (see FIG. 9). This results in increased birefringence and an increase in the refractive index. FIG. 15 shows the change in the refractive index of the single-photon process as a function of the applied energy.

[0167] Figure 10 shows a system (400) for the aforementioned irradiation setup using an LED system for single photon experiments. The system (400) includes an irradiation source (402), a beam collimator (404), and a sample holder (408) for mounting a sample (406). In this Example 5, the irradiation source (402) is Thorlabs' MountedLEDM340L4 - 340nm, 53mW.

[0168] Examples 6 - 10 are carried out in the same manner as Examples 1 - 5 outlined above. Example 6 Preparation of poly(M - 18): 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 hours. Precipitate the polymer into 250 mL of methanol. Dry the resulting polymer, poly(M - 18). Example 7

[0169] In the seventh example, a solution of 12.67 mg of poly(M - 18) in 25 mL of THF is prepared. Dilute it 20 - fold. Fill the diluted solution into a quartz glass cuvette. Obtain a UV / Vis spectrum. Irradiate the sample alternately at 340 nm and obtain a UV / Vis spectrum. The results are shown in Figure 16. Figure 16 shows the absorption as a function of wavelength of the single - photon process. Example 8

[0170] In the eighth example, a sample of irradiated poly(M - 18) according to Example 7 is used. Obtain a UV / Vis spectrum. Irradiate the sample further at 275 nm and alternately obtain a UV / Vis spectrum. The results are shown in Figure 17. Figure 17 shows the absorption as a function of wavelength of the single - photon process. Example 9

[0171] In the ninth example, a second polymeric optical material with a copolymer matrix is prepared. Degas 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 methacrylate. Then add 26.42 mg of 1,1'-(3,3,5-trimethylcyclohexylidene)bis[2-(1,1-dimethylethyl)peroxide]. Filter the mixture and place it into a sheet form with a thickness of 1 mm. Thermally initiate polymerization under conditions that are considered appropriate by those skilled in the art. After the polymerization process is completed, release the polymer from the mold to obtain a polymer sheet with a thickness of 1 mm. Example 10

[0172] In the 10th example, a cylindrical blank of the ophthalmic material created in Example 9 is punched out from the sheet. For the determination of the refractive index, a multi-wavelength refractometer with a heating stage is used. Before measurement, the sample is heated to 80 °C in the device to release the stress from the material. The refractive index is measured at 546 nm and 35 °C. Alternately, the sample is irradiated at 340 nm, the sample is returned to the refractometer, heated to 80 °C, and the refractive index is measured at 546 nm and 35 °C. The results are shown in FIG. 18. Thus, FIG. 18 shows the change in the refractive index of the single-photon process as a function of the applied energy. The sample irradiated at 340 nm is further used in the procedure described herein, but the irradiation wavelength is 275 nm. The effect shown in FIG. 19 is due to the cleavage or back-conversion of the cyclobutane moiety (see FIG. 9). FIG. 19 shows the change in the refractive index of the single-photon process as a function of the applied energy. Examples 11 - 13

[0173] The following Examples 11 to 13 have a copolymer matrix containing the amounts of polymerization monomers M-58, M-56, or M-15 shown in the following table, and show the refractive index change upon irradiation in the single-photon process of the polymer optical material based on the formulation described in Example 9: [Table 1]

[0174] Examples of irradiation involving two - photon / multi - photon absorption: Example 14 The experimental device used within Example 14 is shown in FIG. 11. In the two - photon experiment system (410) in FIG. 11, a wavelength - tunable laser (412) (Ti:Sapphire laser (Chameleon Ultra II by Coherent, Santa Clara, CA, USA)) is incorporated as an irradiation source configured to generate pulsed laser radiation. The irradiation beam is expanded within a beam shaper (414). The pulsed laser radiation generated by the laser light source (412) is then sent to a microscope objective lens (416) (LUCPLFLN of Olympus) and results in an output of focused laser radiation. The region of the polymer optical material with a varying refractive index (sample 418) is directed towards the target via a voice - coil - driven linear stage (422) (PIMag (registered trademark)) used to position a sample holder (420).

[0175] The polymer sample (418) in this specification is a flat button with a diameter of 6.0 mm of the polymer optical material described below. All polymers of the polymer sample are copolymers containing at least a cross - linking agent. The main monomers used in the production of the polymer optical material including the copolymer matrix are summarized in the following table for each button material.

Chemical formula

[0176] During the irradiation process, the flat button of the polymer material described above as the polymer sample (418) is placed at 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 high numerical aperture microscope objective lens. The refractive index formed body is created near the surface. This is similar to the "bottom-up" and "spot-to-spot" procedures. The sample holder (420) is driven by a voice coil linear stage (422) as described above. This is similar to the movement of a scanner. 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 scanning speed and the interval x between the lines of the layer. Three parameters are adjusted to create a uniform solid refractive index formed body. The change in refractive index is measured with a multi-wavelength refractometer (ATR-L by Schmidt & Haensch).

[0177] The results of the two-photon laser experiment correlate with the refractive index diagram of the refractive index that depends on the electromagnetic energy input of the one-photon experiment. Example 15

[0178] In the 15th example, a solution of 288 mg of poly(M-14) (Example 1) is prepared in 4 mL of acetonitrile. The solution is filled into a quartz glass cuvette (32 / GL14 / S / Q / 10, manufactured by STARNA, path length 10 mm). The cuvette containing the liquid solution of poly(M-14) is irradiated at a wavelength of 680 nm with 1 μJ pulses at a repetition rate of 100 kHz using a NA0.1 microscope objective lens. The two-photon generated fluorescence of the solution is measured as a function of the irradiation time using the pulsed irradiation source as described above. The fluorescence is measured at a sensitivity of 350 to 1050 nm using a fiber-coupled and diffraction grating-based spectrometer in a geometry 90 degrees with respect to the irradiation beam. The fluorescence spectra as a function of the increasing irradiation time are tabulated in FIG. 20. The two-photon induced [2π+2π] cycloaddition reaction of the photoactive unit is indicated by the decreasing signal between 400 and 500 nm. The conversion to non-fluorescent dimers in poly(M-14) causes a decrease in the emission peak. The reaction mixture is dried and analyzed by NMR in chloroform-d. The singlets at 4.74 and 4.98 ppm are assigned to the cyclobutane ring formed via the two-photon induced photochemical [2π+2π] cycloaddition reaction. The NMR spectrum correlates with the NMR spectrum of Example 2. Both the single-photon and the two-photon induced photochemical [2π+2π] cycloaddition reaction give the same product. Example 16

[0179] In the 16th example, the irradiated poly(M-14) prepared in Example 14 is used as an acetonitrile solution (4 mL) in a quartz glass cuvette (32 / GL14 / S / Q / 10, manufactured by STARNA, path length 10 mm). The solution is irradiated at a wavelength of 532 nm with 1 μJ pulses at a repetition rate of 100 kHz using a NA0.1 microscope objective lens. The amount of the cyclobutane moiety in the substrate decreases over time during the laser irradiation due to the two-photon induced photochemical [2π+2π] retrocyclization reaction. The reaction mixture is dried and analyzed by NMR in chloroform-d. The singlets at 4.74 and 4.98 ppm, which were previously assigned to the cyclobutane ring formed via the two-photon induced photochemical [2π + 2π] cycloaddition reaction in Experiment 14, disappear. The results of the two-photon induced photochemical [2π + 2π] retrocyclization correlate with the single-photon induced photochemical [2π + 2π] retrocyclization experiment of Example 3. Example 17

[0180] In the 17th example, a solution of 288 mg of the poly(M-14) of Example 1 in 4 mL of acetonitrile is prepared. The solution is filled into a quartz glass cuvette (32 / GL14 / S / Q / 10, manufactured by STARNA, path length 10 mm). In this example, the two-photon generated fluorescence from the solution is measured as a function of the irradiation wavelength using the pulsed irradiation source as described above. The cuvette containing the liquid solution of poly(M-14) is irradiated with 1 μJ pulses at a repetition rate of 100 kHz using a NA0.1 microscope objective lens. The fluorescence is measured at a sensitivity of 350 - 1050 nm in a geometry 90 degrees with respect to the irradiation beam using a fiber-coupled and diffraction grating-based spectrometer. The peak of the fluorescence spectrum at 420 - 430 nm is determined for each irradiation wavelength and plotted in Figure 21 as a function of the irradiation wavelength. As seen in Figure 21, the two-photon induced fluorescence has a high value around 680 nm and decreases with increasing irradiation wavelength. The excitation is maximized at approximately twice the wavelength (340 nm) where one-photon excitation is maximized. This observation is typical for the two-photon absorption process. Example 18

[0181] In the 18th example, a polymeric optical material having a copolymer matrix is prepared. A molten mixture of 4.1 g of M-14, 21 mg of 2-[3-(2H-benzotriazol-2-yl)-4-hydroxyphenyl]ethyl methacrylate, 143.6 mg of 1,18-octadecanediol diacrylate, and 506.7 mg of 2-hydroxyethyl methacrylate is first degassed. Thereafter, 52 mg of 1,1’-(3,3,5-trimethylcyclohexylidene)bis[2-(1,1-dimethylethyl) peroxide is added. The mixture is filtered and placed into a sheet form with a thickness of 1 mm. Polymerization is thermally induced under conditions known in the art. After the polymerization process is completed, the polymer is demolded to obtain a polymer sheet with a thickness of 1 mm. A cylindrical blank of the optical material is punched out from the sheet. Example 19

[0182] In the 19th example, a cylindrical blank of the optical material created by Example 18 is used. The two-photon induced photochemical cross-linking reaction of the optical material is shown using two different irradiation sources as described above in the setup shown in FIG. 11. One irradiation source classified as "kHz" in FIG. 22 is a femtosecond laser operating at 680 nm and emitting μJ pulses at a repetition rate of 100 kHz. The second irradiation source classified as "MHz" in FIG. 22 is a femtosecond laser operating at a wavelength of 680 nm and emitting nJ pulses at a repetition rate of 80 MHz. The cylindrical blank is treated with an average power of 400 mW. Following the irradiation treatment, for each measurement, the optical path length difference of the entire sample is measured with an optical phase-sensitive camera. The refractive index of the material within the irradiation area is estimated from the optical path length difference and the thickness of the sample. The refractive index change (Δn) shown in FIG. 22 is obtained by comparing the irradiated area and the non-irradiated area. Subsequent data points from low to high values of the radiation exposure (= added energy) show the cumulative effect of the irradiation treatment as the irradiation duration increases. Due to this cumulative effect, the requirements of the physician can be accurately converted into corresponding treatment plans.

[0183] FIG. 22 also shows the difference in the overall system efficiency between the kHz and MHz irradiation sources. When all system settings are the same, the kHz system has a significantly increased writing speed, and thus, a shorter and more desirable treatment time. This result indicates that the two-photon induced photochemical [2π + 2π] cycloaddition reaction is more efficient for the kHz system, which is consistent with the conclusion derived from the excited state lifetime described above. Example 20

[0184] In this example, a cylindrical blank of the optical material created by Example 18 is used. The two-photon induced photochemical crosslinking reaction of the optical material is shown using different irradiation wavelengths. The radiation source used is a femtosecond laser adjustable between 666 and 722 nm, emitting μJ pulses at a repetition rate of 100 kHz. The setup shown in FIG. 11 is used. In each measurement, a 1 mm x 6 mm area on the optical material is treated with an average power of 400 mW at the same overall radiation exposure. The refractive index of the material within the irradiation area is estimated from the optical path length difference and the thickness of the sample. The refractive index change (Δn) shown in FIG. 23 is obtained by comparing the irradiated area with the non-irradiated area. The data shown in FIG. 23 demonstrated that refractive index modifications can be created within the optical material by efficiently using the range of 680 - 720 nm.

[0185] FIG. 24 shows a selected example of the refractive index profile written into the optical material during the course of this experiment. In this example, the irradiation source operates at 710 nm with 5-μJ pulses at a repetition rate of 100 kHz. An optical scanner is used to irradiate a 0.6 mm x 6 mm rectangular area on the optical material with spatially overlapping optical pulses. The data is collected with a phase-sensitive camera system attached to a microscope at a magnification of 10x. The phase-sensitive camera records the optical phase difference with a lateral resolution of 30 μm. The recorded values are then converted to refractive index changes taking into account the thickness of the sample. FIG. 24 shows that the refractive index of the irradiated area is decreased by approximately 0.011 compared to the surrounding non-irradiated material.

Claims

**Claim 1** A system for irradiating an artificial lens, the system comprising: one or more irradiation sources (1) for two-photon or multi-photon irradiation of the artificial lens (3) with an irradiation beam (2) focused by an optical unit (16) at a first wavelength and / or 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 artificial lens (3); and an input unit (6) connected to the one or more irradiation sources (1) and the scanner (4), the input unit (6) being configured to input data for treating the artificial lens (3) by scanning the irradiation beam (2) across the artificial lens (3) based on input data (8); the first wavelength being between 600 nm and 800 nm for locally reducing the polarization of the artificial lens based on the treatment of the artificial lens; the second wavelength being between 400 nm and 590 nm for locally increasing the polarization of the artificial lens (3) based on the treatment of the artificial lens; the system. **Claim 2** The system according to claim 1, wherein the artificial lens (3) is a contact lens or an intraocular lens. **Claim 3** The system according to claim 1 or 2, wherein the artificial lens (3) is disposed within a patient's eye. **Claim 4** The system according to any one of claims 1 to 3, wherein the input data (8) includes lens data (10) of the artificial lens (3) and / or treatment plan data (12) regarding a treatment plan for the treatment of the artificial lens (3). **Claim 5** The system according to claim 4, wherein the lens data (10) includes data regarding the radiation absorption characteristics of the artificial lens (3), and the system is configured to adjust the first wavelength and / or the second wavelength such that the artificial lens locally changes its polarization based on a two-photon or multi-photon absorption process. **Claim 6** further comprising a positioning system (20) for determining the position of the focus of the irradiation beam (2) within the patient's eye, the positioning system (20) being connected to the scanner (4), and the scanning of the irradiation beam (2) across the artificial lens (3) by the scanner being based on the position of the focus of the irradiation beam within the eye. The system according to any one of claims 2 to 5. **Claim 7** The system is configured to determine the position and / or orientation of said artificial lens (3) relative to the eye and the exit of the irradiation beam, The system according to any one of claims 2 to 6, wherein the scanning of the irradiation beam (2) across the artificial lens (3) by the scanner (4) is based on the position and / or orientation of the artificial lens (3) relative to the eye.

8. A system according to any one of claims 1 to 7, further comprising (i) one or more irradiation sources (1) and (ii) a temperature control unit (14) connected to one or both of the scanner (4), The temperature control unit (14) is configured to determine the temperature of a part of the artificial lens (3) during the treatment of the artificial lens (3) by the scanning, based on the irradiation beam characteristics of the irradiation beam (2) and the artificial lens characteristics of the artificial lens (3), The system is configured to control one or both of (i) one or more irradiation sources (1) and (ii) the scanner (4) based on the determination of the temperature. Said system.

9. The system according to claim 8, wherein the temperature control unit (14) is configured to predict the temperature during the treatment of the artificial lens (3), and the input data (8) includes the predicted temperature.

10. The system according to any one of claims 2 to 9, further comprising an eye interface system (18) configured to keep the eye of the patient in a fixed position.

11. An operating method of a system for adjusting the polarization of an artificial lens including a body formed of a polymer optical material based on a two- or multi-photon absorption process, wherein the system according to any one of claims 1 to 10 adjusts the polarization of the lens through irradiation of the lens, thereby changing the polymer optical material with a significant difference in the UV / Vis spectrum with respect to the non-irradiated polymer optical material of the artificial lens. Method.

12. The adjustment of the polarization property of the artificial lens, wherein the system according to any one of claims 1 to 10 irradiates the artificial lens with an irradiation beam having a wavelength between 600 nm and 800 nm to reduce the polarization property, and as a result, changes the polymer optical material with a significant difference in the UV / Vis spectrum, that is, a loss of peak absorption in the range of 300 nm to 400 nm, for the non-irradiated polymer optical material of the artificial lens, the method according to claim 11.

13. The adjustment of the polarization property of the artificial lens, wherein the system according to any one of claims 1 to 10 irradiates the artificial lens with an irradiation beam having a wavelength between 400 nm and 590 nm to increase the polarization property, and as a result, changes the polymer optical material with a significant difference in the UV / Vis spectrum, that is, an increase of peak absorption in the range of 300 nm to 400 nm, for the non-irradiated polymer optical material of the artificial lens, the method according to claim 11.

14. The method according to claim 11 or 12, wherein the polymer optical material of the artificial lens comprises a polymer matrix comprising a covalently bonded photoactive unit comprising a non-aromatic double bond capable of dimerizing by forming a cyclobutane ring by [2π + 2π] cycloaddition under the influence of a two-photon or multi-photon process.

15. The method according to any one of claims 11 to 14, wherein the optical material of the artificial lens comprises a polymer matrix comprising a covalently bonded photoactive unit comprising a non-aromatic double bond capable of dimerizing by forming a cyclobutane ring by [2π + 2π] cycloaddition under the influence of a two-photon or multi-photon process together with a photoactive unit that has already been dimerized.

16. The method according to claim 11 or 13, wherein the polymer optical material of the artificial lens comprises a polymer matrix comprising a covalently bonded dimerized photoactive unit as the only photoactive unit capable of separating under the influence of a two-photon or generally a multi-photon process.

17. The method according to any one of claims 11 to 14, wherein The system according to any one of claims 1 to 10 irradiates an artificial lens including a polymer matrix including a covalently bonded photoactive unit including a non-aromatic double bond capable of dimerizing by forming a cyclobutane ring by [2π + 2π] cycloaddition with an irradiation beam of a first wavelength, and the irradiation causes dimerization of the photoactive unit, thereby reducing the polarization property of the artificial lens, thereby modifying the provided artificial lens, and the modified artificial lens includes a polymer matrix including a partially or completely dimerized photoactive unit derived from the [2π + 2π] cycloaddition, Optionally, in order to locally increase the polarization property of the modified artificial lens by partially cleaving the dimerized photoactive unit, the system according to any one of claims 1 to 10 irradiates the modified artificial lens with an irradiation beam of a second wavelength, Method.

18. The system according to any one of claims 1 to 10 irradiates an artificial lens with an irradiation beam of a second wavelength, and the irradiation causes separation of the dimerized photoactive unit, thereby increasing the polarization property of the artificial lens, thereby modifying the provided artificial lens, and the modified artificial lens includes a polymer matrix including a photoactive unit capable of dimerizing again, Optionally, in order to locally reduce the polarization property of the modified artificial lens by partially dimerizing the photoactive unit, the system according to any one of claims 1 to 10 irradiates the modified artificial lens with an irradiation beam of a first wavelength, the method according to claim 16.

19. The system according to any one of claims 1 to 10 irradiates an artificial lens with an irradiation beam of a first wavelength, and the irradiation causes dimerization of the photoactive unit, thereby reducing the polarization property of the artificial lens, thereby modifying the provided artificial lens, and the modified artificial lens includes a polymer matrix including more dimerized photoactive units derived from the [2π + 2π] cycloaddition, or, The method according to claim 15, wherein the system according to any one of claims 1 to 10 irradiates an artificial lens with an irradiation beam of a second wavelength, said irradiation causing separation of the dimerized photoactive units, thereby increasing the polarization of said artificial lens, thereby modifying the provided artificial lens, and the modified artificial lens containing a polymer matrix containing more photoactive units that can dimerize by forming a cyclobutane ring by [2π + 2π] cycloaddition.

20. A kit of parts comprising the system according to any one of claims 1 to 10 and at least one artificial lens suitable for said system.

Images