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

[0002] The photo-inducible changes in material properties are applicable to several technological fields such as microfabrication, 3D printing, nanostructures, or two-photon lithography. This can lead to various processes, including photopolymerization, photo-inducible material degradation, or photochemical crosslinking. These processes result in altered properties of the irradiated material, potentially changing mechanical properties, solubility, transparency, refractive index, and other characteristics. In 3D printing (typically using a photolithographic approach), femtosecond lasers can be used to polymerize specific arrays. This can be done by a photopolymerization reaction. Photosensitizers can be added to make this mixture curable. This can enable printing at a micrometer resolution, which is not possible with conventional 3D printing techniques. Multibeam arrays can be used to increase production speed. Nanostructures are also used in the biomedical field. In the field of ophthalmic 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 IOLs, photosensitizers in the material are typically utilized, for example, by absorbing UV light. Two or more photon processes can target voxels in the internal material without affecting the surface of the IOL. When irradiated, the photosensitizer absorbs light and can supply energy to the surrounding material. In WO2017221068A1, the emitted light is supplied to the hydrogel material in the form of heat. This can lead to degradation of the polymer and a change in refractive index. Another approach is the formation of non-degrading microcrystals within the material by femtosecond laser irradiation. The higher molecular order of microcrystals can lead to a localized increase in density within the material, as shown in US2010228345A1, which in turn can result in a localized increase in refractive index.

[0003] US2009143858 describes a method for modifying the refractive index of an optical polymer material, comprising irradiating a selected region 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, thereby forming a refractive optical structure. The refractive optical structure is characterized by a change in refractive index with little or no scattering loss and without significant difference in the Raman spectrum compared to the unirradiated optical polymer material used. US2016081852 describes a method for altering the refractive properties of the eye, which includes applying a photosensitizer to the internal tissue of the cornea of ​​the eye, irradiating the cornea to promote crosslinking of the internal tissue of the cornea, activating the crosslinking agent in the internal tissue of the cornea, and altering the cornea to change the refractive properties of the eye. US2008004610 describes specific refractive index adjustable lenses and refractive index measurements during treatment with a refractometer. The adjustments described are destructive.

[0004] Cataracts are a condition in which the lens of the eye becomes cloudy, potentially obstructing the passage of light. Most cases of cataracts are associated with the aging process. However, children can be born with cataracts or develop them at a young age. Furthermore, cataracts can develop after eye injury, inflammation, or several other eye diseases. According to the World Health Organization, more than 50 million people worldwide currently suffer from cataracts, and they account for approximately half of all cases of blindness worldwide. While cataracts can be surgically removed, surgical services are unavailable in many countries, and cataracts remain a leading cause of blindness. As life expectancy increases, so does the number of people with cataracts. Therefore, cataracts are a significant cause of poor vision in both developed and developing countries. Comprehensive prevention of cataract development is still unknown. Cataracts can be treated surgically, potentially restoring normal vision. The cloudy lens is then removed and replaced with an artificial lens. As with all modern lenses, artificial lenses are implanted in the remaining lens capsule, or in the sulcus if there is no lens capsule, after the natural lens is removed through a small incision.

[0005] A typical problem with IOL implantation is that, considering optimal visual acuity, the results obtained are not optimal in most cases. Biometric data of the eye before IOL implantation, particularly corneal curvature radius and eyeball length, cannot be determined with the desired accuracy. Predicting IOL positioning during surgery, unpredictable effects of wound healing, and postoperative IOL migration that occurs within weeks to months after cataract surgery is currently difficult. Various approaches and formulas have been used to predict IOL power before cataract surgery, but a suitable solution has yet to be found.

[0006] Clinical trials dealing with the outcomes of cataract surgery have shown that more than 80% of patients are within 1 diopter (D) of their desired refractive error. Nevertheless, many have refractive errors, and therefore require some degree of correction to provide optimized visual acuity. Post-cataract surgery refractive errors have been shown to be virtually unavoidable, although the magnitude of the refractive error is reduced. Problems can also occur in the presence of specific eye conditions, such as when the axial length of the eye is significantly longer or shorter than average. Pediatric cases are generally more prone to complications related to refractive power prediction. Power errors in 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 that the applicable ISO 11979 standard allows tolerances of ±0.33D at the corneal surface for IOLs greater than 25.00D and ±0.66D for IOLs greater than 30.00D.

[0007] Refractive errors are defined as errors in the eye's ability to focus light and are a common reason for decreased visual acuity. An eye that does not have refractive errors when viewing distant objects is called emmetropic. Eyes that exhibit refractive errors when viewing distant objects are said to have atypical vision. Refractive errors can be classified into spherical and cylindrical types. Spherical errors occur when the light power of the eye is too great or too weak to focus light onto the retina. Cylindrical errors occur when the curvature of two meridians differs. People with refractive errors often experience blurred vision.

[0008] Myopia, also known as near-sightedness or short-sightedness, is a refractive defect in the eye where, when the eye is relaxed, parallel light does not form an image in front of the retina. People with myopia see nearby objects clearly, but distant objects appear blurry. In myopia, the eyeball is either too long or the cornea is too steep; in other words, the power of the cornea is too high relative to the length of the eyeball. As a result, the image focuses in the vitreous humor inside the eye rather than on the retina. Hyperopia, also known as farsightedness or long-sightedness, is a visual impairment resulting from an imperfection in the eye. Insufficient optical power for a given length of the eyeball can cause an inability to focus on near objects. In extreme cases, a person may be unable to focus on objects at any distance. As an object moves towards the eye, the eye needs to increase its light power to keep the image focused 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 that can cause blurred vision because the optics of the eye cannot focus point objects onto the retina as a sharply focused image. Irregular or toric curvature of the cornea or lens can cause astigmatism. There is a difference in the degree of curvature and refraction between two different meridians. In other words, the eye has different focal points in different planes. For example, an image may be clearly focused on the retina in the horizontal plane, but not in front of the retina in the vertical plane. Contours in certain directions may appear blurred, while contours perpendicular to them may appear sharp. People with astigmatism may have difficulty seeing fine details. In some cases, vertical lines (e.g., a wall) may appear tilted relative to the patient. The optics of astigmatism can often be corrected with corrective optics such as eyeglasses, hard contact lenses, or contact lenses.

[0009] There are approximately six different forms of cataracts, and more than 20 causes that can lead to cataracts have been identified. Currently, drug treatment is not possible once diagnosed with cataracts. The only current treatment is the replacement of the natural lens, followed by the implantation of an artificial IOL. The standard treatment today is a foldable IOL. Here, the IOL can be immersed in the fluid of the ocular chamber. The optically effective portion of the IOL typically has a diameter between 5 mm and up to 7 mm. Depending on the specific model, an elastic loop or bracket is attached to the end of the optical portion of the IOL. These loops, called tactile loops, allow the lens to be centered in the lens capsule and hold the IOL in place. The overall diameter of the IOL is approximately 12 mm, and its thickness depends on the refractive power, usually varying between 0.7 mm and up to 2 mm. The weight of the IOL is on the order of 50 mg.

[0010] Polymers that can be used to manufacture foldable IOLs can be classified into two subgroups. IOLs can be made of (1) acrylic or methacrylic polymers, or (2) silicone-based polymers. Furthermore, hydrophobic and hydrophilic materials can be used in IOLs. Hydrophilic materials can become soft by utilizing approximately 10-30% water absorption, while hydrophobic materials can be designed to become soft without water absorption. Many variations of IOLs, and many IOLs with various optical profiles (multifocal, toric, extended depth of field, etc.), have been studied and are commercially available. However, currently, it is difficult to determine biometric data with the precision required for IOLs to deliver the 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] cyclic addition reaction between coumarins can be carried out photocatalyzed. One coumarin is photochemically excited and can react with a ground-state molecule within its range. According to the Yablonski diagram, photon absorption leads to the organic molecule being excited into a singlet state. This can be converted to a triplet state via intersystem crossing. In contrast to the singlet state, whose population can be reduced by fluorescence, the triplet state can only be reduced 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. Thus, in the intermolecular [2+2] cyclic addition reaction of coumarin, the triplet state and its population are most suitable because its long lifetime allows for numerous collisions with other molecules and high specific mobility, increasing the possibility of cyclic dimerization [T. Wolffetal, Phys. Chem. Chem. Phys., 2004, 6, 368-376].

[0013] Aside from errors in biometric data measurement, accurately predicting refraction after surgery is virtually impossible. This is primarily due to unpredictable effects that can occur during the healing process within weeks or months after cataract surgery. These effects include, for example, the influence of pseudolenticular anterior chamber depth, which is the conceptual distance between the corneal apex and the effective primary surface of the IOL. Furthermore, changes in corneal shape can occur during the healing process. The precise values ​​of these changes can depend on various factors, including the uniqueness of the eye, the type of IOL, and the surgeon and instruments used. Uncertainty in IOL specifications can also make it difficult to predict correct refraction. After wound healing, treatment, specifically adjustment of the IOL's optical profile, may be applied on an individual basis, or patients treated with an IOL may require prescription eyeglasses to achieve ideal vision. Alternatively, a patient may require contact lenses that match the ideal corrected visual acuity of their natural lens. Because there are currently unresolved shortcomings in preoperative IOL refractive power prediction, the objective of the systems and methods of this disclosure is to provide solutions for non-invasively adjusting the optical profile of an already implanted IOL by altering the polarization of the organic molecules from which the IOL is made. Furthermore, the objective of the systems and methods of this disclosure is to provide solutions for altering the polarization of artificial lenses in particular by using two-photon (or generally multi-photon) processes to create and / or modify artificial lenses (which may or may not be placed in the patient's eye). Multiphoton excitation is a nonlinear 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, excitation light focused by the objective lens of a microscope has an 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, explain that heat has been shown to induce a thermal cycloreversion reaction, which negatively affects the yield of cyclic dimers formed from photoreactions. [Overview of the project]

[0015] The inventors have found that the above-mentioned objectives can be achieved individually or in any combination by the system and processes of this application. The present invention relates to a system for irradiating artificial lenses, and the system includes: The artificial lens is provided with one or more irradiation sources for two-photons or multi-photons, which are focused in the optical section and irradiate the lens with an irradiation beam having a first wavelength and / or a second wavelength different from the first wavelength. A scanner connected to one or more light sources and configured to scan the light beam across the artificial lens, and The system includes 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 the 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, and 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.

[0016] The present invention further relates to a system for irradiating an artificial lens, preferably placed inside a patient's eye, the system comprising: The artificial lens is provided with one or more irradiation sources for two-photons or multi-photons, which are focused in the optical section and irradiate the lens with an irradiation beam having a wavelength between 600 nm and 800 nm. A scanner connected to one or more light sources and configured to scan the light beam across the artificial lens, and The system includes 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 the input data, The reason for this is that the wavelength locally reduces 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 placed inside a patient's eye, the system comprising: The artificial lens is provided with one or more irradiation sources for two-photons or multi-photons, which are focused in the optical section and irradiate the lens with an irradiation beam having a wavelength between 400 nm and 590 nm. A scanner connected to one or more light sources and configured to scan the light beam across the artificial lens, and The system includes 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 the input data, The wavelength is chosen to locally increase 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 intraocular lens not placed inside a patient's eye. The irradiation beam (2) emitted from the irradiation source (1) is deflected by the scanner (4) and focused by the optics unit (16) to perform the desired adjustment of the polarization of the artificial lens (3). The positioning system (20) determines the working position of the focal point within the artificial lens (3). Position information, along with the power and existing optical profile of the artificial lens (3), is part of the input data (8) regarding the artificial lens (3). Lens data (10) and treatment plan data (12) are described further below. The temperature control 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 the system for irradiating the intraocular lens placed inside the patient's eye. Figure 2 is a schematic diagram of the system for irradiating an intraocular lens placed inside the patient's eye. The irradiation beam (2) emitted from the irradiation source (1) is deflected by a scanner (4) and focused by an optical unit (16) to perform the desired adjustment of the polarization of the artificial lens (3) inside the patient's eye, which is linked to an eye interface system (18) that keeps the patient's eye in a fixed position. A positioning system (20) determines the working position of the focal point within the artificial lens (3). Position information, along with the power and existing optical profile of the artificial lens (3), is part of the input data (8) for the artificial lens (3). Lens data (10) and treatment plan data (12) are described further below. A temperature control unit (14) predicts and / or measures the temperature of the material of the artificial lens (3) before and / or during irradiation.

[0020] The present invention further relates to a process for adjusting the polarization of an artificial lens, which includes a body formed of a polymer optical material, based on a two- or multiphoton absorption process, the process comprising the following steps: To provide the aforementioned lens; and The polarization of the lens is adjusted by using the system described above, or preferably below, according to the present invention, through irradiation of the lens, thereby changing the polymer optical material with respect to the non-irradiated polymer optical material of the artificial lens with a significant difference in the UV / Vis spectrum.

[0021] The present invention further relates to a method for locally adjusting the polarization of an intraocular lens, which includes a polymerized optical material placed inside a patient's eye, the method comprising: To locally reduce the polarization of the intraocular lens, the intraocular lens is exposed to an irradiation beam having a wavelength between 600 nm and 800 nm, or To locally increase the polarization of the intraocular lens, the intraocular lens is exposed to an irradiation beam having a wavelength between 400 nm and 590 nm.

[0022] The present invention also further relates to a method for correcting a patient's vision by altering the refractive index of an intraocular lens within the patient's eye, and includes the following: To identify and measure the degree of vision correction required by a patient; Determining the position and type of refractive structure to be inscribed on the intraocular lens to correct the patient's vision; and Subsequently, the intraocular lens is exposed 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 the intraocular lens is exposed to, Subsequently, the intraocular lens is exposed 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 the systems described above, or preferably below, and a kit of components including at least one artificial lens suitable for the system.

[0024] Detailed description of the invention Throughout this disclosure, any reference to a body / element / component of a system that is linked to another body / element / component (and potentially further bodies / elements / components) should be noted as involving a body / element / component that is directly and / or indirectly linked to the other body / element / component.

[0025] In the foregoing disclosure, lenses or artificial lenses are defined as contact lenses or intraocular lenses. An intraocular lens according to the present invention is an implantable 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 may be, for example, a posterior chamber intraocular lens or an anterior chamber intraocular lens. There are no limitations on the type of intraocular lens. For example, it may be a pseudophakic intraocular lens or a phakic intraocular lens. The former type replaces the eye's natural clear lens, typically replacing a removed cataract lens. The latter type is used to complement an existing lens, functions as a permanent corrective lens, and is implanted in the anterior or posterior chamber to correct refractive errors of the eye. The artificial lens treated by the present invention may include, for example, one or more optical elements and one or more tactile elements, where one or more optical elements function as a lens, and one or more tactile elements are attached to one or more optical elements to hold one or more optical elements in place in the eye. The artificial lens treated by the present invention may be a one-piece design or a multi-piece design, depending on whether the one or more optical elements and one or more tactile elements are formed from a single material (one-piece design) or are made separately and then joined together (multi-piece design).

[0026] An artificial lens, preferably an IOL, may include a polymerized optical material, thereby allowing the optical properties of the lens to be non-invasively altered by the system. Using the system, specifically based on a multiphoton process, the polarization, and therefore the refractive index, can be altered. Preferably, the artificial lens (contact lens or IOL) comprises a polymerized optical material, as more preferably described below, thereby allowing the optical properties of the IOL to be non-invasively altered by the system. Particularly preferably, the artificial lens (contact lens or IOL) is made of a polymerized optical material, as more preferably described below. Typically, the optical portion of the lens has a diameter of 5 mm to 7 mm and a thickness of 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, which is to translate ophthalmic requests into control commands for the writing process, as will be described in more detail below. During the writing process, the optical pattern is written by illumination into the artificial lens. The term "control command" refers to a command that directly controls the writing process, as previously defined, or preferably as described below. A control command may, for example, control the movement of a scanner. The term "scanner" as used in this description is not part of the input unit according to the present invention. The "scanner" as described herein is an element of the system according to the present invention that controls the movement of an 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] An optical profile is a necessary change defined by the surgeon based on the patient's examination results before or after implantation of an artificial lens, and may include, but is not limited to, spherical total diopter changes, toric profiles, EDOF profiles, or 2-, 3-, or multifocal profiles. Alternatively, an optical profile is the adjustment of the optical properties of a contact lens. An optical pattern is a necessary change in polarization that results in a change in refractive index in every voxel of an artificial lens.

[0029] The previously defined input data is intended to include common input data, individual input data, or input data being processed. Common input data is intended to include general data that is used by default for systematic reasons. Examples of such common input data are described below. Individual input data consists of all data relevant solely to ophthalmology requests. Examples of such individual input data are described below. Input data during processing is data created and used during the writing process.

[0030] The term "positioning system" used in this explanation refers to a system that determines the position of the laser focal point within the eye. The term "assessment system," used as part of the positioning system in this description, 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 section of the system according to the present invention. As used herein as part of the system according to the present invention, the term “optical unit” includes all optical instruments necessary to control the spatial distribution of the illumination source (focal point) on the artificial lens. Key parameters of the focal point include the lateral focal size (or beam waist) and the focal length (or Rayleigh length). The optical unit includes all elements along the optical beam path that determine the focal point, such as a beam expander, aperture diaphragm, shutter, and focusing optics, particularly a microscope objective or a single aspherical lens. Irradiation within the focal volume results in a refractive optical structure characterized by a change in polarization / rate related to the polarization / refractive index of most of the artificial lens, or the unirradiated portion of the artificial lens. In other words, by using the change in polarization / refractive index, a desired patterned refractive structure can be formed within the artificial lens, as described below, or preferably as described below.

[0031] It is preferable to provide a refractive structure that exhibits a change in refractive index and shows little to no scattering loss, so that detachment, removal, or destruction of the intraocular lens material is not observed within the illuminated area. The aforementioned illuminated area 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 provide refractive power correction in both physical directions. Furthermore, the optical structures can be stacked vertically or written on separate planes within an artificial lens, which will be further described below, to function as a single lens element. Multiphoton excitation is generated only near the focal point, preferably by using ultrashort laser pulses. The average power is limited by a sample damage threshold, which is part of the common input data defined before and after the sample damage.

[0032] As described above, or preferably below, the system advantageously enables postoperative and non-invasive adjustment of the optical properties / profile of an implanted IOL to eliminate visual impairments such as refractive errors. Furthermore, when manufacturing artificial lenses (e.g., contact lenses, or, for example, before an intraocular lens is inserted into the patient's eye), the system advantageously enables gentle fabrication of the artificial lens, particularly allowing for refractive structures that can provide spherical, aspherical, toroidal, or cylindrical corrections, and / or maintaining the flexibility of the lens even after the lens fabrication is complete. The polarization of the artificial lens is modified based on a two-photon (or generally multi-photon) process that allows for adjustment of the optical properties / profile of the artificial lens, or adjustment of the optical properties of the artificial lens in different planes. Furthermore, modification of polarization based on a two-photon or multi-photon process can improve the maintenance of lens flexibility when treated with wavelengths of 400 nm to 590 nm. The artificial lens is preferably an IOL.

[0033] Criteria for selecting and optimizing system parameters: One ultimate objective of this invention is to produce local refractive index modifications of post-implant IOLs as prescribed by a physician, thereby improving the patient's vision. A key criterion for refractive index modification procedures is the total treatment time required to achieve the desired result. It is generally recognized that such procedures should not take more than a few minutes to be considered feasible. State-of-the-art systems capable of local refractive index modification do not include an approach to obtain the actual treatment time for IOL applications.

[0034] Consideration of system trade-offs and limitations: In the case of implanted artificial lenses in general, or especially in practical, high-performance systems that allow for adjustment of IOLs, it is recognized that many interdependencies and trade-offs exist between subcomponents, and therefore these subcomponents must be treated as a system and thus optimized in conjunction. Subcomponents include the irradiation source, optics, scanner, and treatment plan. A critical requirement for optimizing any system / parameters is that the lens material (if the artificial lens treatment is a contact lens), the lens material (if the artificial lens treatment is an IOL), and the eye as a whole (e.g., the retina) remain within safety limits. Such requirements form the basis of the aforementioned common input data. In particular, two main damage mechanisms of radiation from an irradiation source, preferably a pulsed laser source, are identifiable: single-pulse damage (dielectric breakdown and avalanche breakdown), and thermal damage, where the temperature of the lens material and / or the eye is subsequently heated due to repeated pulses for the same volume. For example, the average power of the pulsed irradiation source is related to heating, and therefore to potential damage to the lens material and / or the eye. Thus, while the average power of the irradiation source is kept below the threshold for overheating of the lens material and / or the eye, the pulse energy and pulse repetition rate are inversely proportional to the pulse energy, and the number of pulses per second (= reciprocal of the repetition rate) is equal to the average power. Average power is defined as the pulse energy multiplied by the number of pulses per second, and is expressed in watts (W). The irradiation dose is the flux density (W / cm²). 2 (Equivalent to) Radiation exposure is equivalent to flux (J / cm²). 2 (Equivalent to)

[0035] One overall objective is to minimize the treatment time for post-implant IOL adjustment. Theoretically, more frequent pulses (higher repetition rates) allow for increasingly higher pulse energies, but typically, exceeding an average power of 1 watt leads to dangerous conditions for the IOL material and retina due to overheating. Therefore, to stay within safe operating limits, a preferred radiation exposure can be defined, allowing for the treatment of the entire IOL volume to be completed within a few minutes. A preferred radiation exposure is ≤5 kJ / cm². 2 Particularly preferably <1 kJ / cm 2 And, very preferably, <0.3 kJ / cm 2 This described radiation exposure amount is further applied to the processes and methods according to the present invention, as will be further described below. If the treatment plan is too extensive and exceeds the laser's safety limits regarding overheating, the treatment may be interrupted to allow cooling of all the artificial lens material and tissue affected by the treatment. After cooling, the evaluation system can compare the treated voxels within the artificial lens to the optical pattern, and the treatment may be resumed.

[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 by the treatment plan described above. According to the treatment plan, for example, toric, spherical, multifocal, or EDOF (extended depth of field) profiles can be written to the lens. An algorithm can be used to write profiles for toric, spherical, multifocal, or EDOF (extended depth of field) profiles, for example.

[0037] By combining information on the desired optical profile with common and individual input data, the required optical pattern and control commands for the irradiation source, optics, 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 such as the precise position and orientation of the artificial lens in the patient's eye, which is part of the treatment plan data. Control commands can be updated and modified during the writing process using, for example, input data during processing such as patient eye temperature data obtained by IR temperature measurement, positioning data of the irradiation beam, artificial lens, or eye during processing obtained by, for example, OCT (optical coherence tomography), and / or refractive data obtained from shineproof images.

[0038] In a further embodiment of the input data, the input data includes lens data of the artificial lens, preferably the intraocular lens, and / or treatment plan data relating to the treatment plan for the treatment of the artificial lens. For example, the lens data may include data relating to one or more of 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, shape, diopter, cylindrical and spherical, and / or its individual anomalies in the dimensions. Thus, the polarization may 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, the lens data may also include data relating to one or more of the dimensions of the artificial lens (e.g., diameter and / or thickness), lens shape, diopter, cylinder, sphere, and / or any individual abnormalities in the said dimensions, and data relating to the materials contained in the artificial lens, preferably an intraocular lens. Preferably, the lens data includes data relating to one or more dimensions of the artificial lens or IOL (e.g., diameter and / or thickness), or data relating to one or more of the polarization and / or refractive index of the artificial lens as a function of the volume or position of each part of the artificial lens, lens shape, diopter, cylinder, sphere, and / or its individual anomalies in the dimensions, and data relating to the material contained in the artificial lens, which is part of an individual input dataset. Preferred materials for artificial lenses, preferably intraocular lenses, are described below.

[0039] In some cases, the calculation of the treatment plan may generate control commands that result in one or more treatment plan data, including: Scanning procedure control command data for scanning the first and / or second wavelength irradiation beam 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 first and / or second wavelength irradiation beam (e.g., nanosecond, picosecond, or femtosecond pulses), and / or irradiation beam profile of the first and / or second wavelength irradiation beam, and / or radiation (photon) density, and / or radiation intensity, and Individual input data such as temperature data, including the current and / or predicted temperature of the artificial lens during exposure (and / or radiant power and / or radiant wavelength), refractive index / polarization data, refractive index / polarization data, refractive index / polarization data, refractive index / polarization data, in particular, with respect to the mapping of the refractive index / polarization to a specific location / coordinate of the artificial lens, incision dimension data, incision dimensions, and eye data, relating to the dimensions and / or shape of the patient's eye, positioning data, relating to the position and / or orientation of the artificial lens relative to the eye, and registration data, relating to the identification of the patient and / or a specific eye of the patient.

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

[0041] Those skilled in the art are well aware that the optimal illumination focus condition is achieved when the depth of field (Rayleigh length) of the illumination beam matches the desired thickness of the optical structure written on the artificial lens. Those skilled in the art are well aware that the optimal illumination focus condition is achieved when the depth of field (Rayleigh length) of the illumination beam matches the local thickness of the artificial lens.

[0042] In a further embodiment, the lens data includes data relating to the radiative absorption characteristics of the artificial lens (e.g., absorption and / or attenuation coefficients that may depend on the wavelength of light), and the system is configured to tune a first wavelength and / or a second wavelength of the artificial lens to locally change the polarization based on a multiphoton absorption process. For example, based on the material used in the artificial lens, a specific wavelength or wavelength range can be input to precisely locally change the polarization of the artificial lens.

[0043] As part of the system according to the present invention, as described above and further below, the input unit is configured to input the aforementioned input data for treating artificial lenses that may be on a sample holder for the treatment of contact lenses or that may be in the patient's eye for the non-invasive adjustment of intraocular lenses. Accordingly, the present invention further relates to the aforementioned or later systems, wherein the input data includes lens data of the artificial lens and / or treatment plan data relating to the treatment plan for the treatment of the artificial lens. Accordingly, the present invention further relates to the systems described above or below, wherein the lens data includes data relating to the radiant absorption characteristics of the artificial lens, and the system is configured to tune a first wavelength and / or a second wavelength based on a multiphoton absorption process so that the artificial lens locally changes its polarization.

[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 used to generate nanosecond pulses, preferably picosecond pulses, and more preferably femtosecond pulses. Preferably, one irradiation source is used. Particularly preferably, one or more irradiation sources include one or more pulsed lasers used to generate femtosecond pulses. Particularly preferably, one pulsed laser is used to generate femtosecond pulses used as irradiation for the system according to the present invention, or for processes and methods according to the present invention.

[0045] In one embodiment of the present invention, one or more irradiation sources include lasers tuned to emit laser beams having first and second wavelengths, respectively. This may be particularly advantageous because 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 as the irradiation source in the system according to the present invention. MHz and kHz lasers are suitable and have specific advantages. For example, MHz laser systems operate at lower pulse energies, but the focused laser spot can be kept on the μm scale (<1 μm to several μm), so they can be used for precise local index modification in all three dimensions, for example, to generate diffraction structures. A preferred MHz irradiation source is an 80 MHz laser with pulse energies in the range of 0.1 to 10 nJ. On the other hand, kHz lasers typically operate at higher pulse energies of 0.1–10 μJ, requiring larger spot sizes, such as 10–100 μm, to avoid damaging the lens material. However, a larger laser spot size means a deeper depth of field (longer Rayleigh length), which may be equal to or exceed the thickness of the artificial lens material. With such long Rayleigh lengths, it may be impossible to modify the refractive index layer by layer within the IOL, and it may only be possible to modify it uniformly along the line around the focal point. A preferred kHz irradiation source is a laser with a repetition rate of 100–500 kHz. The average power of the aforementioned, or preferably the aforementioned, irradiation source is preferably between 300 and 600 mW, and particularly preferably between 400 and 500 mW.

[0046] In a further embodiment of the present invention, to generate an irradiation beam having wavelengths outside the range given to the first and second wavelengths, 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 present invention preferably includes a tunable laser capable of providing a tunable wavelength in the range of about 680 to 1080 nm, such as a titanium-sapphire laser (e.g., ChameleonUltraII by Coherent, Santa Clara, CA, USA). The system may also include an optical parametric oscillator (e.g., frequencydoubledChameleonCompactOPO-Vis by Coherent, Santa Clara, CA, USA).

[0048] The irradiation source as part of the system according to the present 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 repetition rate of 0.1 to 700 kHz and pulses <350 fs. The emission of the excitation laser is directed to an 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 to 800 nm. A preferred repetition rate is between 50 and 600 kHz. A 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 includes a femtosecond-excited laser with an average power >10 watts at 1030 nm, combined with an optical parametric amplifier, which emits irradiation pulses <350 fs at a repetition rate of 1 to 700 kHz. The radiation from the pump laser is directed to 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. A preferred repetition rate is between 50 and 600 kHz. A particularly preferred repetition rate is between 100 and 500 kHz.

[0049] The aforementioned, or preferably the aforementioned, laser type generates a parallel optical beam with a diameter of several millimeters, which is then directed towards the optical unit and scanner. The quality of the optical beam (M 2 (Measured in units of ) Ideally, it should be between 1.0 and 1.5, and more ideally between 1.0 and 1.3.

[0050] Multiphoton excitation occurs only near the focal point and is preferably generated by using the aforementioned ultrashort laser pulses. The average power is limited by a sample damage threshold, which is part of the common input data defined earlier. The ideal parameters for a two-photon-induced cyclic dimerization reaction are linked to the pulse duration and repetition rate from the system, and further, or preferably as described below, to the specific time constant of the artificial lens material that can be cyclic dimerized, which in short is the lifetime of the molecule's S1 state (~several ns), the lifetime of the long-lived triplet state (many ns to >μs), and the specific thermal diffusion time (~1μs). Considering the lifetime of the long-lived triplet state, longer pulse intervals are advantageous. The lifetime of the triplet state in the photochemically active group (from many ns to > μs) is much longer than the repetition rate of the 80 MHz system (12.5 ns). Therefore, it is advantageous to use the aforementioned, or preferably the aforementioned kHz laser, as most of the triplet state is cleared before the next pulse begins. This effect results in a significant increase in the efficiency of the cyclic dimerization reaction of artificial lens materials, as more preferably described below. The temperature rise within the focal point due to linear absorption, referenced by a specific thermal diffusion time, is mitigated within microseconds, approximately 80 times slower than the typical ~80 MHz pulse interval. Therefore, the temperature rise is large. This is not the case for kHz pulses, where the thermal diffusion time is 10 times faster than the typical 100 kHz pulse interval. Consequently, when irradiated with a constant laser fluence, the localized temperature rise due to laser heating is more pronounced at higher repetition rates.

[0051] The first wavelength of the irradiation beam in 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 more preferably between 680 nm and 710 nm, in order to (locally) reduce the polarization (and therefore refractive index) of the IOL. The second wavelength of the irradiation beam in the system according to the present invention is between 400 nm and 590 nm, preferably between 500 nm and 580 nm, and more preferably between 530 nm and 570 nm, in order to increase the polarization (and therefore refractive index) of the IOL (locally). This allows the polarization to change locally and with particular precision.

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

[0053] Optical component in the system according to the present invention: The primary function of the optics unit is to focus the irradiation beam, emitted from the irradiation source and controlled by the scanner, onto an artificial lens. As previously mentioned, important considerations are the spot size and depth of focus to minimize treatment time while remaining within the limits imposed by laser safety requirements and material damage, as previously stated as part of the common input data. The most important characteristics of the optics unit are its effective focal length (EFL) and the diameter of the irradiation beam at the entrance aperture of the focusing optics unit, as well as its numerical aperture (NA). Furthermore, all optical elements within the system according to the present invention should be selected for diffraction-limited or near-diffraction-limited characteristics so as not to substantially degrade the quality of the optical beam. Since the spatial resolution obtained is determined by the spot size, the required spot size will differ depending on the ophthalmic needs. Ideally, the spot size should be between 1 and 100 μm, and more ideally between 50 and 100 μm, in order to minimize treatment time and reduce the possibility of material damage.

[0054] Scanner in the system according to the present invention: Scanners used in the system according to the present invention may include galvanometer scanners, piezo scanners, rotary scanners, or acousto-optic modulators, and may be digital, such as spatial light modulators, digital micromirror devices, or stereolithography apparatuses. Preferably, the scanner as part of the system of the present invention as described herein is selected from galvanometer scanners, piezo scanners, rotary scanners, acousto-optic modulators, spatial light modulators, digital micromirror devices, or stereolithography apparatuses. A preferred galvanometer scanner is a single-pivot point scanner. Preferably, the scanner is configured to operate at a scanning speed of 50 mm / s or more. This helps to keep the treatment time short. In principle, the treatment time should not exceed a few 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 0.2 mm to 2.0 mm.

[0055] To accommodate the entire volume of the artificial lens while keeping the overall radiation exposure low and shortening the treatment time, the optimal radiation exposure dose is <1 kJ / cm². 2 Ideally, it should be <0.3 kJ / cm². 2 That is the case.

[0056] Particularly preferably, a random scanning pattern or interleaved scanning lines are used to diffuse the irradiation energy of the irradiation beam. Scanning can be performed in three modes. In bottom-up scanning, the laser moves from spot to spot with a specific dwell time at each spot (bottom-up, spot-to-spot). Alternatively, in bottom-up scanning, the laser can remain in overlapping spots (bottom-up, spot overlay). Or, the laser can move at a constant speed without remaining in any particular spot (flyby, constant velocity). Figure 3 shows a schematic diagram (1500) of the scanning procedure described above. In one aspect of the scanning pattern, the IOL is scanned by the illumination source, as described above, or preferably as described above, by illuminating it through the pupil. The IOL, which is contained within the lens capsule during scanning, is pre-inserted through a corneal incision using conventional surgical procedures. In this aspect, the entire volume of the IOL is scanned, and the scanning 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 mentioned above, a key consideration when selecting a scanning program is minimizing local heating of the artificial lens and / or the patient's eye; therefore, various variables are used in the scanning program. Considering anatomical features such as the incision and pupil size, as well as optical features such as numerical aperture and laser pulse characteristics, a laser program is created using a specific scanning speed and sequence. In this embodiment, the relationship between lens coordinates and eye coordinates is automatically considered. Figure 4 shows a schematic diagram (1600) of the variables used in the aforementioned scanning program, considering the irradiation of the lens within the patient's eye.

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

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

[0060] The aforementioned, or preferably the aforementioned system, further includes, in one further embodiment of the system, a microscope-coupled objective lens for focusing the irradiation beam onto the artificial lens by a microscope objective lens, wherein the microscope objective lens has a numerical aperture between 0.1 and 0.8, preferably between 0.2 and 0.5, and more preferably between 0.2 and 0.4. Providing a microscope objective lens having such a numerical aperture may enable high irradiation beam quality, particularly with respect to the focusing and resolution characteristics of a beam used to treat an intraocular lens. The microscope objective lens includes, for example, a typical lens configuration that allows for correction of chromatic aberration. The microscope objective lens is preferably linked to an eye interface system, which typically holds the patient's eye in a fixed position, as further described below. In a further embodiment of the objective lens used in the system according to the present invention described above, the objective lens is an OlympusLUCPLFLN objective lens for focusing the illumination beam onto an artificial lens. Accordingly, the present invention further relates to the above system, further comprising a microscope objective lens coupled to a scanner for focusing the irradiation beam onto the artificial lens using a microscope objective lens, wherein the microscope objective lens has an numerical aperture between 0.1 and 0.8, preferably between 0.2 and 0.5, and more preferably between 0.2 and 0.4.

[0061] The alternative focusing optical unit / image group preferably consists of a single aspherical lens with an effective focal length in the range of 50 to 150 mm and preferably a numerical aperture of 0.025 to 0.1. Accordingly, the present invention further relates to the aforementioned system, comprising a focusing optical unit / image group consisting of a single aspherical lens having an effective focal length preferably within 50 to 150 mm and preferably a numerical aperture of 0.025 to 0.1.

[0062] The aforementioned system, or preferably the aforementioned system, further comprises, in one further embodiment, a positioning system for determining the location of the focal point of the irradiation beam within the patient's eye, wherein the positioning system is coupled to a scanner, and the scanner's scanning of the irradiation beam across the intraocular lens is based on the location of the focal point of the irradiation beam within the eye. The positioning system may include an assessment system such as an optical coherence tomography system, a confocal microscope, or a Scheinproof camera. The positioning system may be coupled directly or indirectly to the scanner. In some embodiments in which a confocal microscope is used, the confocal microscope may be coupled directly to the scanner. The aforementioned assessment system is used to provide local data of the eye to the positioning system in order to determine the position of the laser focal point according to the eye and the intraocular lens. In the case of a confocal microscope, a partially transparent mirror is used to enable video imaging.

[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 scanner scanning of the irradiation beam across the intraocular lens is based on the position and / or orientation of the intraocular lens relative to the eye. This may be particularly advantageous because the position of the intraocular lens cannot be centered relative to the eye, so that 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 intraocular lens, since the two cannot be centered relative to each other. Regarding the position of the IOL, it can be considered that at least two coordinate systems are involved: the x, y, and z coordinates of the eye, and the x, y, and z coordinates of the intraocular lens, because the two cannot be centered relative to each other.

[0065] In one embodiment, the assessment system generates individual input data. This individual input data includes, for example, data about the lens position and / or orientation of the artificial lens in the eye, and data about the laser beam exit, and / or optical power mapping of the eye and / or the artificial lens. This data is used for calculating optical patterns or continuing the procedure. Furthermore, the rating system can generate input data during the writing process. This processing-intensive input data includes, for example, data about the lens position and / or orientation of the artificial lens within the eye, and data about the laser beam exit, and / or optical power mapping of the eye and / or artificial lens. This data is used to modify the control commands used for generating the optical pattern during processing. Accordingly, the present invention further relates to the aforementioned system, further comprising a positioning system for determining the focal position of the irradiation beam within the eye of the patient, wherein the positioning system is connected to a scanner, and the scanning of the irradiation beam across the artificial lens by the scanner is based on the focal position of the irradiation beam within the eye. Accordingly, the present invention further relates to the aforementioned system, wherein the system is configured to determine the position and / or orientation of the artificial lens and the exit of the irradiation beam relative to the eye, and the scanning of the irradiation beam across the artificial lens by the scanner is based on the position and / or orientation of the artificial lens relative to the eye.

[0066] The aforementioned system, or preferably the aforementioned system, further comprises, in one further embodiment, (i) one or more irradiation sources and (ii) a temperature control unit connected to one or both of the scanners, wherein the temperature control unit is configured to determine the temperature of a portion of the artificial lens during the treatment of the artificial lens by scanning, based on the irradiation beam characteristics of the irradiation beam and the artificial lens characteristics of the artificial lens, and the system is configured to control (i) one or more irradiation sources and (ii) one or both of the scanners based on the temperature determination. This may make it 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 control unit is preferably configured to predict the temperature of the artificial lens during the treatment, and the input data includes the predicted temperature. This may make it possible to take precautions to ensure that the eye and / or the artificial lens are not adversely affected based on the treatment with the irradiation beam. Alternatively, the temperature control unit is an infrared camera that records the eye temperature and correlates the measured data with common data, including calibration data, to calculate the true temperature of the eye. In another embodiment, 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 writing the predicted refractive power map, the temperature within the lens can be calculated during processing.

[0067] In another embodiment, 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 measured emission peak wavelength and / or peak width deviation, the temperature in the focal point can be calculated during processing. Accordingly, the present invention further relates to the aforementioned system comprising (i) one or more irradiation sources, and (ii) a temperature control unit connected to one or both of the scanners, The temperature control unit is configured to determine the temperature of a portion of the artificial lens during the scanning treatment of the artificial lens, 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 temperature determination. Accordingly, the present invention further relates to the aforementioned system, wherein the temperature control unit is configured to predict the temperature of the artificial lens during the treatment, and the input data includes the predicted temperature.

[0068] The aforementioned, or preferably the aforementioned system, further includes, in one further embodiment, an eye interface system configured to keep the patient's eye in a fixed position. The eye interface system may include a suction system for fixing the position of the patient's eye during the procedure. The patient can be "docked" to the system in a lying or standing position. Accordingly, the present invention further relates to the aforementioned system, which includes an eye interface system configured to keep the patient's eye in a fixed position.

[0069] The aforementioned system, or preferably the aforementioned system, in one further embodiment, includes a wireless or wired receiver and / or transceiver for one or more of the following: (i) transmitting control commands to one or more light sources; (ii) transmitting control commands to a scanner; and (iii) inputting control command data necessary to create an optical pattern into the scanner. Therefore, one or more irradiation sources and / or scanners can be remotely controlled. Furthermore, data relating to either or both of the lens data and / or treatment plan data may be stored outside the system and provided to the system as needed. In some embodiments, it may be preferable to provide a wired receiver or transceiver to control at least one or more irradiation sources and / or to control the scanner to reduce (or avoid) any delay when transmitting control signals to one or more irradiation sources and / or scanners. In another embodiment, the receiver / transmitter transmits 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, which then provides it to the system.

[0070] The aforementioned system, or preferably the aforementioned system further, in one further embodiment, includes a device for locally measuring the refractive power of the artificial lens during the treatment of the artificial lens. This allows for adjustments to one or more irradiation sources, scanners, and input data during the treatment process. The aforementioned system, or preferably the aforementioned system further, in one further embodiment, includes a refractometer for locally measuring the refractive index of the artificial lens during the treatment of the artificial lens. This allows for adjustments to one or more light sources, scanners, and input data during the treatment process.

[0071] Further elements of the photon-providing system are, optionally, a cover into which all the equipment is 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 system. In addition to the elements mentioned above, a controller, firmware, a graphical user interface (GUI), and a processing algorithm may be provided. Connectivity can be established via Bluetooth®, Wi-Fi, or other ports such as RS-232 to connect to the system.

[0072] Figure 5 shows a further schematic diagram of a system (100) for irradiating an intraocular lens to be placed inside the eye of a patient (136). System (100) generally relates to a laser system comprising at least one femtosecond laser source (102, 104) capable of generating at least one, preferably two, different wavelengths. System (100) further includes a focal or Z-shifter optics unit (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 unit (108) for supplying laser pulses to a predetermined area. System (100) may be able to achieve the same level of energy supplied to a target area of ​​a polymer material containing a photochemically active unit that forms an intraocular lens placed inside the eye of a patient (136). The system further includes an eye interface (112) for fixing the eye of the patient (136) in Figure 5. In Figure 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 in the treatment planning system to calculate the level of energy supplied to a target region of polymer material containing photochemically active units that form the intraocular lens. System parameters and process treatment plans (134) are monitored via the GUI (120). Inputs and adjustments from the patient (136), such as lens data (130) and refractive index formation plans (132), can be entered via the GUI (120). The laser source, subsystems, and body fixation (124) may be integrated into a single module connected to a power supply (126) sealed by a cover (128).

[0073] Figures 6 and 7 show schematic diagrams of the elements of the system according to the present invention as described herein. Photons generated by the irradiation source (202) are guided in the embodiment of Figure 6 through mirrors (optical system 1, e.g., beam shaper (204), focus shifter / Z shifter (206) to a scanner (208) (e.g., a digital scanner using a galvanometer, piezo scanner, or rotary scanner, or an acousto-optic modulator, or 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 Figure 7, the Z-shifter (302) includes a first lens (304), a second lens (306), and a third lens (308). The irradiation beam is then moved to a scanner (310) which includes multiple mirrors (312), (314), and (316), thereby changing the x and y positions of the irradiation beam on the IOL. After passing through the scanner (310), the irradiation beam moves 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, which includes a body formed of a polymer optical material based on a two- or multiphoton absorption process (preferably at one or more specific locations on the lens), the process comprising the steps of: providing the lens; and adjusting the polarization of the lens by using a system described throughout this disclosure or preferably described, thereby changing the polymer optical material with respect to the unirradiated polymer optical material of the artificial lens with respect to the UV / Vis spectrum. The artificial lens is preferably a contact lens or IOL comprising a polymer optical material as described below or preferably described below. The process for adjusting the polarization according to the present invention, as described above or preferably below, is carried out 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 or reflection spectroscopy of a portion of the ultraviolet spectrum and the adjacent visible spectrum. Suitable UV / Vis spectrometers are commercially available. The choice of UV / Vis spectrometer is not important for comparing the UV / Vis spectrum of the original artificial lens with the UV / Vis spectrum of the irradiated artificial lens made according to the present invention, as long as both measurements are performed under equivalent conditions known to those skilled in the art, so that the results can be compared. A suitable spectrometer is the PerkinElmer Lambda900 UV / Vis spectrometer.

[0076] Next, the artificial lens may, in some embodiments, be subsequently inserted into the patient's eye. In some embodiments, the lens may include an intraocular lens that allows for adjustment of the lens's polarization while it is positioned within the patient's eye. Within the aforementioned process, the adjustment of the polarization of the artificial lens involves reducing the polarization by irradiating the artificial lens with an irradiation beam having a wavelength between 600 nm and 800 nm, thereby changing the polymer optical material with respect to the unirradiated polymer optical material of the artificial lens, i.e., a loss of peak absorption in the range of 300 nm to 400 nm. Accordingly, the present invention further relates to the aforementioned process, and the adjustment of the polarization of the artificial lens includes reducing the polarization by irradiating the artificial lens with an irradiation beam having a wavelength between 600 nm and 800 nm, thereby changing the polymer optical material with respect to the unirradiated polymer optical material of the artificial lens, i.e., a loss of peak absorption in the range of 300 nm to 400 nm.

[0077] Within the aforementioned process, the adjustment of the polarization of the artificial lens involves increasing the polarization by irradiating the artificial lens with an irradiation beam having a wavelength between 400 nm and 590 nm, thereby changing the polymer optical material with respect to the unirradiated polymer optical material of the artificial lens, i.e., an increase in peak absorption in the range of 300 nm to 400 nm. Accordingly, the present invention further relates to the aforementioned process, and the adjustment of the polarization of the artificial lens includes increasing the polarization by irradiating the artificial lens with an irradiation beam having a wavelength between 400 nm and 590 nm, thereby changing the polymer optical material with respect to the unirradiated polymer optical material of the artificial lens, i.e., an increase in peak absorption in the range of 300 nm to 400 nm.

[0078] Accordingly, the present invention further relates to a process for adjusting the polarization of an artificial lens, which includes a body formed of a polymer optical material, based on a two- or multiphoton absorption process (preferably at one or more specific positions on the lens), the process comprising the following steps: To provide the aforementioned lens; and The polarization of the lens is adjusted by using a system that includes the following: The artificial lens is provided with one or more two-photon or multiphoton irradiation sources that are focused in the optical section and irradiate the lens with an irradiation beam of a first wavelength and / or a second wavelength different from the first wavelength. A scanner connected to one or more light sources and configured to scan the light beam across the artificial lens, and One or more irradiation sources and an input unit connected to a scanner, wherein 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, thereby changing the polymer optical material with respect to the non-irradiated polymer optical material of the artificial lens, i.e., 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. 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, thereby changing the polymer optical material with respect to the non-irradiated polymer optical material of the artificial lens, i.e., with a significant difference in the UV / Vis spectrum, i.e., an increase in peak absorption in the range of 300 nm to 400 nm.

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

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

[0081] The following further and preferably describes 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 nm to 710 nm, which are used in the process of the present invention to locally reduce the polarization of the optical material of the artificial lens, preferably the polymer optical material of the contact lens or IOL. 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 artificial lenses (contact lenses, or IOLs) may optionally contain ultraviolet blocking agents or blue light absorbing agents.

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

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

[0084] A photoactive unit means a photochemically active unit that is photochemically active in the aforementioned, or preferably, applicable wavelength range 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 be dimerized by forming a cyclobutane ring by [2π+2π] cyclic addition under the influence of a two-photon or multi-photon process. Accordingly, the present invention further relates to a process for adjusting the polarization of an artificial lens (preferably at one or more specific positions on the lens) including a body formed of a polymer optical material, wherein the optical material of the artificial lens comprises a polymer matrix containing a covalently bonded photoactive unit containing a non-aromatic double bond, preferably a carbon-carbon double bond, which can be dimerized by forming a cyclobutane ring by [2π+2π] cyclic addition under the influence of a two-photon or multi-photon process. In this embodiment, the photoactive unit in the polymer optical material of the artificial lens used in the process according to the present invention may be the same or different, but is the only photoactive unit in the polymer optical material and is classified in that it contains a non-aromatic double bond, preferably a carbon-carbon double bond, which can be dimerized by forming a cyclobutane ring by [2π+2π] cyclic addition under the influence of a two-photon or multi-photon process, as described above, or more preferably below.

[0085] Alternatively, the polymer matrix may include the aforementioned or later photoactive units along with already dimerized photoactive units. Therefore, the polymer matrix may still contain photoactive units that can be dimerized. The polymer optical material (polymer matrix) may be partially dimerized.

[0086] In the aforementioned embodiment of the optical material for an artificial lens used in a process according to the present invention, preferably a polymer optical material for a contact lens or IOL, such material can be irradiated in either the first or second wavelength range described above to decrease or increase its polarization, thereby decreasing or increasing the refractive index of the artificial lens containing the polymer optical material. Such a polymer optical material makes the polarization of the artificial lens adjustable. Accordingly, the present invention further relates to a process for adjusting the polarization of an artificial lens (preferably at one or more specific positions on the lens) including a body formed of a polymer optical material, wherein the optical material of the artificial lens comprises a polymer matrix containing covalently bonded photoactive units, preferably carbon-carbon double bonds, which can be dimerized by forming a cyclobutane ring by [2π+2π] cyclic addition under the influence of a two-photon or multi-photon process, along with already dimerized photoactive units. In this embodiment, the photoactive units in the polymer optical material of the artificial lens used in the process according to the present invention may be the same or different, but are the only photoactive units in the polymer optical material, and are classified in that they contain non-aromatic double bonds, preferably carbon-carbon double bonds, which can be dimerized by forming a cyclobutane ring by [2π+2π] cyclic addition under the influence of a two-photon or multi-photon process, as described above or preferably below, or the photoactive units are dimerized photoactive units thereof.

[0087] The photoactive units in the polymer optical material of the artificial lens used in the process according to the present invention particularly preferably include a non-aromatic carbon-carbon double bond bonded to at least one aromatic ring system that can be dimerized by forming a cyclobutane ring by [2π+2π] cyclic addition 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 condensed ring system, preferably a bicyclic or tricyclic ring system, and particularly preferably a bicyclic ring system, as part of the photoactive unit, as described above.

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

[0089] [2π+2π] cyclic addition can be visualized by the following scheme 1. Figure 8 shows a specific [2π+2π] cyclic addition reaction of poly(M-14); the representative material is further described in Examples 1 and 2. Scheme 1 further visualizes retrocyclization. Figure 9 shows a specific cleavage of poly(M-14) dimer by retrocyclization, which is further described in Examples 3 and 5. Scheme 1: [ka] Rp refers to a polymer / copolymer skeleton covalently linked to a condensed ring system via a linker; X'-X' is independent of CH=CH, CR'=CH, CH=CR', or CR'=CR'; Y' is O, S, NR', CH2, CHR', C(R')2; If Y' is O, S, or NR', then m is 1; if Y' is independently selected from CH2, CHR', and C(R')2 in each case, then m is 1, 2, 3, or 4; Z' is either C=O or C=S; n is either 0 or 1; R' is an organic substituent.

[0090] Examples of silicon-containing polymers that can be used as optical materials for artificial lenses 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 polymerization 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, and is O, S, NR 0 , or X 1 ; 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;

[0093] R 0 It is a linear or branched alkyl group having 1 to 10 carbon atoms; R 1 , R 2 , R 3 , and R 4 These are selected from H, F, Cl, Br, I, linear or branched alkyl groups having 1 to 20 carbon atoms, partially or completely halogenated linear or branched alkyl groups having 1 to 20 carbon atoms, and aryl or heteroaryl groups having 5 to 40 ring atoms, and are independent of each other; R 5 , R 6 , R 7 , R 8 , and R 9 In each case, is independently selected from the group consisting of F, a linear 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 linear or branched, non-halogenated, partially or fully halogenated alkoxy group having 1 to 20 carbon atoms, and a linear or branched, non-halogenated, partially or fully halogenated thioalkyl group having 1 to 20 carbon atoms;

[0094] X 11 It 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 either 0 or 1; R 10 , R 11 , R 12 These are selected from H, F, linear or branched alkyl groups having 1 to 20 carbon atoms that can be partially or completely halogenated, and aryl groups having 6 to 14 carbon atoms, and are independent of each other; 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 carbon atoms, a partially or fully halogenated linear or branched alkyl group having 1 to 10 carbon atoms, a linear or branched alkoxy group having 1 to 10 carbon atoms, and a partially or fully halogenated linear or branched alkoxy group having 1 to 10 carbon atoms.

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

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

[0097] R 0 It is a linear or branched alkyl group having 1 to 10 carbon atoms; R 1 , R 2 , R 3 , and R 4 These are selected from H, F, Cl, Br, I, linear or branched alkyl groups having 1 to 20 carbon atoms, partially or completely halogenated linear or branched alkyl groups having 1 to 20 carbon atoms, and aryl or heteroaryl groups having 5 to 40 ring atoms, and are independent of each other; R 5 , R 6 , R 7 , R 8 , and R 9 In each case, F is independently selected from the group consisting of a linear 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 linear or branched, non-halogenated, partially or fully halogenated alkoxy group having 1 to 20 carbon atoms, and a linear or branched, non-halogenated, partially or fully halogenated thioalkyl group having 1 to 20 carbon atoms. R 5 , R 6 , R 7 , R 8 , or R 9 If any of these corresponds to equation (2-1), then * indicates a link to the rest of equation (2). [ka] R 10 , R 11 , R 12 These are selected from H, F, linear or branched alkyl groups having 1 to 20 carbon atoms that can be partially or completely halogenated, and aryl groups having 6 to 14 carbon atoms, and are independent of each other;

[0098] X 11 It 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 either 0 or 1; 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 carbon atoms, a partially or fully halogenated linear or branched alkyl group having 1 to 10 carbon atoms, a linear or branched alkoxy group having 1 to 10 carbon atoms, and a partially or fully halogenated linear or branched alkoxy group having 1 to 10 carbon atoms.

[0099] Halogenation preferably means fluorination, chlorination, or bromination, and particularly preferably fluorination. A linear or branched alkyl group having 1 to 10 carbon atoms means an alkyl group having 1, 2, 3, 4, 5, 6, 7, 8, 9, or 10 carbon atoms, such as methyl, ethyl, isopropyl, n-propyl, isobutyl, n-butyl, tert-butyl, n-pentyl, 1-, 2- or 3-methylbutyl, 1,1-, 1,2- or 2,2-dimethylpropyl, 1-ethylpropyl, n-hexyl, n-heptyl, n-octyl, ethylhexyl, n-nonyl, or n-decyl. Linear or branched alkyl groups having 1 to 20 carbon atoms include all examples of linear or branched alkyl groups having 1 to 10 carbon atoms, including any alkyl group having 11, 12, 13, 14, 15, 16, 17, 18, 19, and 20 carbon atoms, such as n-undecyl, n-dodecyl, n-tridecyl, n-tetradecyl, n-pentadecyl, n-hexadecyl, n-heptadecyl, n-octadecyl, n-nonadecyl, and n-eicosyl.

[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. In terminology, a fully halogenated alkyl group means that all the 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 the H atoms of the alkyl group are replaced by F. A preferred fully fluorinated alkyl group is trifluoromethyl. The terms halogenated, or preferably fluorinated, correspond to other groups such as halogenated cycloalkyl groups, halogenated alkoxy groups, or halogenated thioalkyl groups.

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

[0102] A linear or branched alkoxy group having 1 to 20 carbon atoms is 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 carbon atoms, such as methoxy, ethoxy, isopropoxy, n-propoxy, isobutoxy, n-butoxy, tert-butoxy, n-pentyloxy, 1-, 2- or 3-methylbutyloxy, 1,1-, 1,2- or 2,2-dimethylpropoxy, 1-ethylpropoxy, n- This refers to 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 completely halogenated, or preferably partially or completely fluorinated. A preferred fully fluorinated alkoxy group is trifluoromethoxy.

[0103] A linear or branched thioalkyl group having 1 to 20 carbon 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 carbon atoms, such as thiomethyl, 1-thioethyl, 1-thio-isopropyl, 1-thio-n-propoyl, 1-thio-isobutyl, 1-thio-n-butyl, 1-thio-tert-butyl, 1-thio-n-pentyl, 1-thio-1-,-2-, or-3-methylbutyl, 1-thio-1,1-,-1,2-, or-2,2-dimethylpropyl, 1-thio-1-ethylpropyl This refers to thioether groups such as 1-thio-n-hexyl, 1-thio-n-heptyl, 1-thio-n-octyl, 1-thio-ethylhexyl, 1-thio-n-nonyl, 1-thio-n-decyl, 1-thio-n-undecyl, 1-thio-n-dodecyl, 1-thio-n-tridecyl, 1-thio-n-tetradecyl, 1-thio-n-pentadecyl, 1-thio-n-hexadecyl, 1-thio-n-heptadecyl, 1-thio-n-octadecyl, 1-thio-n-nonadecyl, and 1-thio-n-eicosyl, which can be partially or completely halogenated, or preferably 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 carbon atoms.

[0105] In the context of the present invention, an aryl group contains 6 to 40 ring atoms, and a heteroaryl group in the context of the present invention contains 5 to 40 ring atoms, including at least one heteroatom. The heteroatom is preferably selected from N, O, and / or S. An aryl group or heteroaryl group is understood here to mean any of the following: a simple aromatic cycle, i.e., phenyl, or a simple heteroaromatic cycle, e.g., pyridinyl, pyrimidinyl, thiophenyl, etc., or a condensed (anelate) aryl or heteroaryl group, e.g., naphthyl, anthracenyl, phenantrenyl, quinolinyl, or isoquinolinyl.

[0106] The aryl group or heteroaryl group is preferably benzene, naphthalene, anthracene, phenanthrene, pyrene, benzanthracene, chrysene, perylene, fluorantene, naphthacene, pentacene, benzopyrene, biphenyl, biphenylene, terphenyl, triphenylene, fluorene, spirobifluorene, dihydrophenanthrene, dihydropyrene, tetrahydropyrene, cis or transindenofluorene, cis or transindenocarbazole, cis or transindenocarbazole, torcene, isotorcene, spi Rotulcen, Spiroisothorucene, Furan, Benzofuran, Isobenzofuran, Dibenzofuran, Thiofen, Benzothiophene, Isobenzothiophene, Dibenzothiophene, Pyrrole, Indole, Isoindole, Carbazole, Pyridine, Quinoline, Isoquinoline, Acridine, Phenanthidine, Benzo-5,6-Quinoline, Benzo-6,7-Quinoline, Benzo-7,8-Quinoline, Phenothiazine, Phenoxazine, Pyrazole, Indazole, Imidazole, Benzimidazole, Naphthimidazole, Phenanthrimidazole, Pyri Doimidazole, pyrazineimidazole, quinoxalineimidazole, oxazole, benzoxazole, naphthoxazole, anthroxazole, phenantroxazole, isoxazole, 1,2-thiazole, 1,3-thiazole, benzothiazole, pyridazine, hexazatriphenylene, 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-tetraaza Perylene, pyrazine, phenazine, phenoxazine, phenothiazine, fluorbin, naphthyridine, azacarbazole, benzocarbolin, 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,It is derived from 2,3-triazine, tetrazole, 1,2,4,5-tetrazine, 1,2,3,4-tetrazine, 1,2,3,5-tetrazine, purine, pteridine, indoridine, and benzothiadiazole. The aryl group having 6 to 14 carbon atoms is preferably an aryl group selected from the group consisting of phenyl, naphthyl, or anthryl, and particularly preferably phenyl.

[0107] In one particularly preferred embodiment of the present invention, a polymer optical material comprising a polymer matrix containing covalently bonded photoactive units of an artificial lens used in a process according to the present invention contains a polymer monomer according to formula (3), [ka] Here, X1, a, R 5 ~R 9 , and R 10 ~R 12 The above terms are used to indicate the meaning described above.

[0108] In one particularly preferred embodiment of the present invention, a polymer optical material comprising a polymer matrix containing covalently bonded photoactive units of an artificial lens used in a process according to the present invention contains a polymer monomer according to formula (4), [ka] Here, u is 0, Y is X 1 , X 11 c is selected from the group consisting of O-SO2, SO2-O, OC(=O), C(=O)O, S(C=O), and (C=O)S, where 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 , R9 , R 10 , R 11 , R 12 , and R have the meanings described above.

[0109] In one particularly preferred embodiment of the present invention, the polymeric optical material comprising a polymer matrix containing covalently bonded photoactive units of an artificial lens used in the process according to the present invention contains a polymerization monomer according to formula (5), [Chemical formula] / / 这里“

化

[0110] R 5 / / 这里保留原标签 , R 6 / / 这里保留原标签 , R 7 / / 这里保留原标签 , R 8 / / 这里保留原标签 and R 9 / / 这里保留原标签 are selected from H, F, Cl, Br, I, a linear or branched alkyl group having 1 - 20 C atoms, a linear or branched alkoxy group having 1 - 20 C atoms, a partially or fully halogenated linear or branched alkyl group having 1 - 20 C atoms, a partially or fully halogenated linear or branched alkoxy group having 1 - 20 C atoms, and an aryl or heteroaryl group having 5 - 40 ring atoms, preferably, independent of each other, R 5 / / 这里保留原标签 ~R9 At least one group selected from is a linear or branched alkyl or alkoxy group having 1 to 20 carbon atoms, which can be partially or completely halogenated to form a compound according to formula (1) or (3). R 5 , R 6 , R 7 , R 8 and R 9 These are selected from H, F, Cl, Br, I, linear or branched alkyl groups having 1 to 20 carbon atoms, linear or branched alkoxy groups having 1 to 20 carbon atoms, partially or fully halogenated linear or branched alkyl groups having 1 to 20 carbon atoms, partially or fully halogenated linear or branched alkoxy groups having 1 to 20 carbon atoms, and aryl or heteroaryl groups having 5 to 40 ring atoms for compounds according to formulas (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 It is preferably H. In the compounds of formula (1), (2), (3), (4), or (5), R 10 The nucleotide is preferably H or methyl. In the compound of formula (1) or (2), R 5 It is preferably H. In the compound of formula (1) or (2), R 6 It is preferably H. In the compound of formula (1) or (2), R 8 It is preferably H.

[0112] In the compound of formula (1) or (2), R 9 Preferably, X1, a, R is a linear or branched alkyl or alkoxy group having 1 to 6 C atoms that can be partially or completely fluorinated, and X1, a, R5 ~R 8 , and R 10 ~R 12 This has the meaning described above, or preferably as described above. In the compound of formula (1) or (2), R 7 Preferably, X1, a, R is a linear or branched alkyl group having 2 to 8 C atoms that can be partially or completely fluorinated, and X1, a, R 5 ~R 6 , R 9 , and R 10 ~R 12 This has the meaning described above, or preferably as described above. In the compounds of formula (2), (4), or (5), R 1 , R 2 , R 3 , and R 4 It is preferably H. In the compound of formula (2) or (4), R 5 , R 6 , R 7 , R 8 , and R 9 These are selected from H, F, a linear or branched alkyl group having 1 to 20 carbon atoms, a linear or branched alkoxy group having 1 to 20 carbon atoms, a partially or fully halogenated linear or branched alkyl group having 1 to 20 carbon atoms, and a partially or fully halogenated linear or branched alkoxy group having 1 to 20 carbon 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 All are preferably H or R 5 , R 6 , R 7 , R 8 , and R 9 One or two of these atoms are F, or an alkyl group having 1 to 8 C atoms that can be partially or completely fluorinated, and the other substituents are H. In the compound of formula (5), R 5 , R6 , R 7 , R 8 , and R 9 Besides the one substituent present in formula (2-1) as described above, or preferably as described above, all other atoms are preferably H.

[0113] In a further embodiment of the present invention, the polymer optical material comprising the polymer matrix of the artificial lens used in the process according to the present invention contains polymer monomers selected from compounds (M-1) to (M-68) and (A-01) to (A-16): [ka] [ka] [ka] [ka] [ka] [ka] [ka] [ka] [ka] [ka] [ka] [ka] [ka]

[0114] In a further embodiment of the present invention, the polymer optical material comprising a polymer matrix contains a polymer 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 more very preferred embodiment 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 comprising the aforementioned, or preferably, polymer monomers comprising the aforementioned photoactive units, or polymer compounds of formulas (1) to (5) above, or polymer compounds (M-1) to (M-68), and (A-01) to (A-16), and further polymer monomers known in the art.

[0116] Examples of monomers copolymerized with monomers containing the aforementioned, or preferably the aforementioned, photoactive units before constructing polymer optical materials for artificial lenses (e.g., contact lenses or IOLs) include styrene, ethoxyethyl methacrylate (EOEMA), methyl methacrylate (MMA), methyl acrylate, n-alkyl acrylate (n-alkyl group containing 2 to 20 carbon atoms), n-alkyl methacrylate (n-alkyl group containing 2 to 20 carbon atoms), i-alkyl acrylate (i-alkyl group containing 3 to 20 carbon atoms), i-alkyl methacrylate (i-alkyl group containing 3 to 20 carbon atoms), ethoxyethoxyethyl acrylate (EEEA), 2-hydroxyethyl methacrylate (HEMA), tetrahydrofuryl methacrylate (THFMA), glycidyl methacrylate (GMA), 16-hydroxyhexadecyl acrylate, 16-hydroxyhexadecyl methacrylate, 18-hydroxy hydroxy The following can be selected from the group consisting of tadecyl acrylate, 18-hydroxyoctadecyl methacrylate, 2-phenoxyethyl acrylate (EGPEA), heptafluorobutyl acrylate, heptafluorobutyl methacrylate, hexafluorobutyl acrylate, hexafluorobutyl methacrylate, hexafluoroisopropyl acrylate, hexafluoroisopropyl methacrylate, octafluoropentyl acrylate, octafluoropentyl methacrylate, betanfluoropropyl acrylate, pentafluoropropyl methacrylate, tetrafluoropropyl methacrylate, trifluoroethyl acrylate, trifluoroethyl methacrylate, bisphenol A diacrylate-1EO / phenol (BPADA), 2-[3'-2'H-benzotriazole-2'-yl)-4'-hydroxyphenyl]ethyl methacrylate (BTPEM), or ethylene glycol dimethacrylate.

[0117] Preferred examples of monomers copolymerized with monomers containing the aforementioned, or preferably the aforementioned, photoactive units before constructing polymer optical materials for artificial lenses (e.g., contact lenses or IOLs) are selected from methyl methacrylate, 2-hydroxyethyl methacrylate, 2-phenoxyethyl acrylate, ethoxyethoxyethyl acrylate, 8-methyl nonyl methacrylate, n-butyl methacrylate, 2-ethylhexyl methacrylate, or mixtures thereof.

[0118] Suitable UV absorbers: 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-benzo[d][1,2,3]triazol-2-yl)phenoxy)propyl methacrylate, 2-(2-hydroxy-5-vinylphenyl)-2H-benzotriazole, allyl-2-hydroxybenzophenone, 2-allyl-6-(2H-benzotriazol-2-yl)-p-cresol, 4-methacryloxy-2-hydroxybenzophenone, 2- (2'-hydroxy-3'-methallyl-5'-methylphenyl)benzotriazole, 2-hydroxy-4-methacryloyloxybenzophenone, 4-acryloylethoxy-2-hydroxybenzophenone, 2-[3-(2H-benzotriazole-2-yl)-4-hydroxyphenyl]ethyl methacrylate, 2-(2'-hydroxy-5'-methacrylamidephenyl)-5-methoxybenzotriazole, 2-(2'-hydroxy-5'-methacrylamidephenyl)-5-chlorobenzotriazole, 2-(2'-hydroxy-5'-methacryloxypropylphenyl)benzotriazole, 2-(2'-hydroxy-5'-methacryloylpropyl-3'-tert-butylphenyl)-5-methoxy-2H-benzotriazole, 2-(3-(tert-butyl)-4-hydroxy-5-(5-methoxy-2H-benzo[d][1,2,3] Triazole-2-yl)phenoxy)ethyl methacrylate, 2-[3'-tert-butyl-2'-hydroxy-5'-(3''-methacryloyloxypropyl)phenyl]-5-chlorbenzotriazole, 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]triazole-2-yl)-4-vinylphenol, 2-(2H-1,2,3-benzotriazole-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, and 3-(3-t-butyl-5-(5-chlorobenzotriazol-2-yl)-4-hydroxyphenyl)propyl methacrylate, which can be polymerized with monomers according to formulas (1), (2), (3), (4), or (5).

[0120] Suitable crosslinking agents for use in copolymers containing polymerization monomers of formula (1), (2), (3), (4), or (5) for constructing polymer optical materials of artificial lenses (contact lenses or IOLs) include 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, and 1,12-dodecyl The following are selected from the group: 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, and 1,18-octadecanediol dimethacrylate.

[0121] If it is necessary to increase the refractive index, a different wavelength range can be applied to an artificial lens (contact lens or IOL) made of one or more polymers that can change the polarization properties. 400-590 nm, preferably 500-580 nm, and most preferably 530-570 nm may be used.

[0122] In the following, the optical material of the artificial lens used in the process according to the present invention, preferably the polymer optical material of the contact lens or IOL, will be further and preferably described in the wavelength range 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 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) for the adjustment may optionally contain the aforementioned ultraviolet blocking agent or blue light absorbing agent. The polymer optical material of the artificial lens used in the process according to the present invention for the adjustment comprises a polymer matrix containing covalently bonded dimerized photoactive units in an amount preferably at least 2% to 100% by weight, preferably 5% to 90% by weight, and most preferably 7% to 80% by weight. The dimerized photoactive units within the polymer matrix may be the same or different. The polymer matrix of the artificial lens and / or IOL polymer optical material for the adjustment may be a homopolymer or copolymer, preferably a matrix made from a copolymer. The polymer matrix containing the dimerized photoactive units may be a matrix made from a silicon-containing polymer, an acrylic polymer, a methacrylic polymer, or a mixture thereof.

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

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

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

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

[0127] In a more very preferred embodiment 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 comprising the aforementioned, or preferably, polymer monomers comprising the aforementioned dimerized photoactive units, or derived from the polymer compounds of formulas (1) to (5) above, or derived from the polymer compounds (M-1) to (M-68) and (A-01) to (A-16), and further polymer monomers known in the art. Examples of monomers, UV absorbers, and crosslinking agents have been described above and can be appropriately applied to this polymer optical material comprising 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 comprising partially or completely dimerized photoactive units may be formed via one-photon, two-photon, or generally multi-photon absorption of photoactive units that can be dimerized by forming a cyclobutane ring by [2π+2π] cyclic addition, as described above, or preferably as described above. When the process according to the present invention is applied to the eye, two-photon (or, more commonly, multi-photon) absorption may be used. To manufacture artificial lenses comprising polymer optical materials including a polymer matrix containing partially or completely dimerized photoactive units used in the process according to the present invention, two-photon (or generally multi-photon) absorption or one-photon absorption may be used via any irradiation means such as a UV lamp with a special wavelength filter, a UV LED having one of the wavelengths specified above, or a laser having one of the wavelengths specified above. To produce an artificial lens comprising a polymer optical material including a polymer matrix containing partially or completely 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 UV LED having one of the wavelengths indicated above, or a laser having one of the wavelengths indicated above.

[0129] For the manufacture of an artificial lens comprising a polymer optical material including a polymer matrix containing partially or completely 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 may be used by doubling the frequency of the feed laser, or an optical power amplifier may be used, or a different irradiation source may be used. Preferably, a different irradiation source is used for the manufacture of the artificial lens.

[0130] The present invention further relates to a process for adjusting the polarization of an artificial lens, which includes a body formed of a polymer optical material, based on a two- or multiphoton absorption process, the process comprising the following steps: To provide the aforementioned artificial lens; and By using the aforementioned, or preferably the aforementioned system, the polarization of the lens is adjusted through irradiation of the lens. Herein, the provided artificial lens comprises a polymer matrix comprising a covalently bonded photoactive unit containing a non-aromatic double bond that can be dimerized by forming a cyclobutane ring by [2π+2π] cyclic addition, as described above, or preferably as described above. and, The provided artificial lens is irradiated with an irradiation beam of a first wavelength, the irradiation causing dimerization of the photoactive units, thereby reducing the polarization of the artificial lens, thereby modifying the provided artificial lens, the modified artificial lens comprising a polymer matrix containing partially or completely dimerized photoactive units derived from the [2π+2π] cyclic addition, and optionally irradiating the modified artificial lens with an irradiation beam of a second wavelength to locally increase the polarization of the modified artificial lens by partially cleaving the dimerized photoactive units.

[0131] The present invention further relates to a process for adjusting the polarization of an artificial lens, which includes a body formed of a polymer optical material, based on a two- or multiphoton absorption process, the process comprising the following steps: To provide the aforementioned artificial lens; and By using the aforementioned, or preferably the aforementioned system, the polarization of the lens is adjusted through irradiation of the lens. The artificial lens provided herein comprises a polymer matrix containing a covalently bonded dimerized photoactive unit as the sole photoactive unit that can be separated under the influence of the aforementioned, or preferably, the aforementioned two-photon or generally multi-photon process. The provided artificial lens is irradiated with an irradiation beam of a second wavelength, and said 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 containing 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 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 the lens by using the foregoing, or preferably the foregoing system, wherein the provided artificial lens includes a covalently bonded photoactive unit containing 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 a photoactive unit that has already been dimerized as described above, or preferably as described above, and, the provided artificial lens is irradiated with an irradiation beam of a first wavelength, and said 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 containing more dimerized photoactive units derived from said [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 containing a polymer matrix containing more photoactive units that can dimerize by forming a cyclobutane ring by [2π + 2π] cycloaddition.

[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, polymeric optical material, the method comprising: 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, polymeric optical material, the method comprising: 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, which is placed inside a patient's eye and which includes the aforementioned, or preferably, the aforementioned polymer optical material, wherein exposure of the intraocular lens includes scanning the irradiation beam across the intraocular lens based on input data relating to lens data of the intraocular lens, particularly relating to the polymer optical material, and / or treatment plan data relating to a treatment plan for the intraocular lens based on exposure of the intraocular lens to the irradiation beam.

[0136] The present invention further relates to a method for locally adjusting the polarization of an intraocular lens, which is placed inside a patient's eye and which contains the aforementioned, or preferably, the aforementioned polymer optical material. Lens data includes data relating to one or more dimensions of the intraocular lens (e.g., diameter, and / or thickness), material, in particular the aforementioned, or preferably, polymer optical material contained in the aforementioned intraocular lens, refractive index of the intraocular lens, and mapping of the refractive index to a specific location / coordinate of the intraocular lens.

[0137] The present invention further relates to a method for locally adjusting the polarization of an intraocular lens, which is placed inside a patient's eye and which contains the aforementioned, or preferably, the aforementioned polymer optical material, wherein the treatment plan data includes one or more of the following: Scanning procedure control command data for scanning 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 pulses of the irradiation beam at first and / or second wavelengths, 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 exposure. The refractive index of the intraocular lens obtained based on the exposure, and the refractive index data obtained in particular with respect to the mapping of the refractive index obtained for a specific position / coordinate of the intraocular lens, Incision dimensions data, 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 relative to the eye, and Registered data regarding the identification of the patient and / or a specific eye of the patient.

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

[0139] The present invention further relates to a method for locally adjusting the polarization of an intraocular lens, which is placed inside a patient's eye and which comprises the aforementioned, or preferably, the aforementioned polymer optical material, wherein the (first) wavelength is between 650 nm and 750 nm, preferably between 670 nm and 720 nm, and more preferably between 680 nm and 710 nm. The present invention further relates to a method for locally adjusting the polarization of an intraocular lens, which is placed inside a patient's eye and which comprises the aforementioned, or preferably, the aforementioned polymer 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 may be to provide the intraocular lens.

[0140] In the embodiment, exposure of the intraocular lens to the irradiation beam includes exposure of a first volume and / or plane and / or position of the intraocular lens before exposure of a second volume and / or plane and / or position of the intraocular lens, wherein the first volume and / or plane and / or position is further 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 time in the irradiation sequence may be closer to the cornea than the volume and / or plane and / or position irradiated at an earlier time. The volume may thus relate to one or more planes of the intraocular lens.

[0141] The lens data and treatment plan data are preferably part of a system preferred for locally adjusting the polarization of an intraocular lens, which is preferably the aforementioned or the aforementioned polymer optical material, and is placed in the patient's eye as described above.

[0142] The present invention also relates to a method for correcting a patient's vision by modifying the refractive index of an intraocular lens in the patient's eye, which comprises the aforementioned, or preferably, the aforementioned polymer optical material. To identify and measure the degree of vision correction required by a patient; Determining the position and type of refractive structure to be inscribed on 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, the intraocular lens is subsequently exposed 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, and / or The procedure then includes 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, when the polarization changes, the refractive index changes as will be explained in more detail below. The speed of light c0 in vacuum is a fundamental constant and describes the speed of electromagnetic waves in vacuum. From the solution of Maxwell's equations, the speed of light in vacuum can be related to the electric constant ε0 and the magnetic constant μ0. These are also fundamental constants.

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[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 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.

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Number

[0145] Relative permittivity, also known as dielectric material, describes how the electric field strength decreases when a material is placed in an electric field. Relative permittivity is determined by the material's ability to polarize in response to an electric field, thereby reducing the total electric field within the material. While the relative permittivity of most materials is between 1 and 100, it can range up to 10000. r Dielectrics with relative permittivity are known. Some examples include the relative permittivity of polystyrene, cellulose, and water, which are 2.5, 4.5, and 81, respectively. The relative permittivity of air can be considered to be 1, which corresponds to a suitable approximation. Generally, relative permittivity is not constant, as it can vary depending on the frequency, humidity, temperature, and other parameters of the field in which it is applied. In nonlinear media, the permittivity may depend on the strength of the electric field. Therefore, ε r The old term "dielectric constant" is unclear and should no longer be used.

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

number

number

[0147] The refractive index n is a material constant that characterizes the refractive properties of a medium. As previously mentioned, 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, 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. The refractive index of most organic polymers is between 1.4 and 1.6, and specially modified high-refractive-index polymers have refractive indices greater than 1.7. The refractive index generally depends on the frequency of light, a phenomenon called scattering. The refractive index of dry air (n air Since ≈1.0003) differs only slightly from 1, it is possible to perform measurements that correspond to an appropriate approximation for air. In technical optics, the refractive index n 0 This is used. This is defined below.

number

[0148] The following relationship can be obtained.

number

number

[0149] This is because the refractive index of the polymer / copolymer is determined by its relative permittivity ε r This means that it changes when it fluctuates. To understand the relative permittivity and how it can thereby modify the refractive index of polymers / copolymers, we need to examine in detail what happens when light waves interact with matter. The electric field, in this case the electrical component of the light wave,

number

number

number

number

number

number

[0150] Polarity vector

number

number

number

number

number

number

[0151] Electric susceptibility was previously defined. It is necessary to distinguish between two types of polarity: displacement polarity and orientation polarity. Displacement polarity arises from the displacement of charges in neutral atoms or molecules relative to one another. The distortion from its normal shape by an external electric field, i.e., the induction of an electric dipole moment by the electric field, is a relative tendency of charge distribution, like the electron cloud of an atom or molecule. Orientation polarity arises from the orientation of permanent dipoles along the electric field lines. These dipoles were present in the medium before the electric field was applied. In the visible spectral range, only the orientation polarity of electrons is considered. The frequency of visible light is approximately 10 14 Hz~10 15 In the Hz range, it is relatively high. Therefore, the factors contributing to the overall polarity caused by atomic displacement and the orientation of permanent dipoles are so small that they can be ignored. Only electrons can "follow" a rapidly oscillating electric field. For displacement polarity, the equation is

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number

number

[0152] In comparison, α is ε r It is easy to see that it must be proportional to this.

number

[0153] It should be noted that variations of the embodiments described herein fall within the scope of the invention. Any feature disclosed herein may be substituted for alternative features serving the same, equivalent, or similar purposes unless expressly excluded. Therefore, any feature disclosed herein 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 no particular features and / or steps are mutually exclusive. This is particularly consistent with the preferred features of the present invention. Similarly, non-essential combination features can be used individually (but not in combination). It should also be noted that many of the features, particularly those of preferred embodiments of the present invention, constitute an invention in themselves and should not be considered merely some of the embodiments of the present invention. These features may be subject to independent protection, either in addition to or as a substitute for any of the present inventions.

[0154] The technical teachings disclosed in this invention may be abstracted and combined with other examples. Undoubtedly, many other effective alternatives will come to mind for those skilled in the art. It will be understood that the present invention is not limited to the embodiments described and includes modifications that are apparent to those skilled in the art and fall within the scope of the claims appended herein. [Brief explanation of the drawing]

[0155] [Figure 1]Figure 1 is a schematic diagram of a system for irradiating artificial lenses, such as contact lenses or intraocular lenses, that are not placed inside the patient's eye. [Figure 2] Figure 2 is a schematic diagram of the system for irradiating the intraocular lens placed inside the patient's eye. [Figure 3] Figure 3 shows a schematic diagram of the scanning procedure (1500). [Figure 4] Figure 4 shows a schematic diagram (1600) of the variables used in the scanning program, taking into account the illumination of the lens inside the patient's eye. [Figure 5] Figure 5 shows a further schematic diagram of the system for illuminating the intraocular lens placed inside the patient's eye. [Figure 6] Figure 6 shows a schematic diagram of the elements of the system for illuminating the intraocular lens placed inside the patient's eye. [Figure 7] Figure 7 shows a schematic diagram of the elements of the system for illuminating the intraocular lens placed inside the patient's eye. [Figure 8] Figure 8 shows a specific [2π+2π] cyclic addition reaction of poly(M-14). [Figure 9] Figure 9 shows specific cleavage of the poly(M-14) dimer by retrocyclization. [Figure 10] Figure 10 shows the irradiation settings used in Example 5. [Figure 11] Figure 11 shows, for example, the irradiation settings for Example 14.

[0156] [Figure 12] Figure 12 shows the absorption as a function of wavelength for the single-photon process, which is further described in the Experimental section as Example 2. [Figure 13] Figure 13 shows the absorption as a function of wavelength for the single-photon process described in Example 3. [Figure 14] Figure 14 shows the change in refractive index of the single-photon process as a function of the applied energy, as described in Example 5. [Figure 15]Figure 15 shows the change in refractive index of the single-photon process as a function of the applied energy, as described in Example 5. [Figure 16] Figure 16 shows the absorption of the single-photon process as a function of wavelength, as further described in Example 7. [Figure 17] Figure 17 shows the absorption as a function of wavelength of the single-photon process described in Example 8, using the solution from Example 7. [Figure 18] Figure 18 shows the change in refractive index as a function of the applied energy for the bulk polymer of Example 9, which contains polymerized M18, as described in Example 10, using the single-photon process. [Figure 19] Figure 19 shows the change in refractive index as a function of added energy for the crosslinked dimer of the bulk polymer of Example 9 containing polymerized M18, as described in Example 10, using the single-photon process. [Figure 20] Figure 20 shows the fluorescence spectra as the irradiation time increases according to Example 15. [Figure 21] Figure 21 shows the peak of the fluorescence spectrum at 420-430 nm as a function of irradiation wavelength, as described in Example 17. [Figure 22] Figure 22 shows the change in refractive index (Δn) as a function of the radiation exposure amount according to Example 19. [Figure 23] Figure 23 shows the change in refractive index (Δn) as a function of the radiation exposure amount in Example 20. [Figure 24] Figure 24 shows an example selected from the refractive index profiles written to the optical material during the experiment of Example 20. [Modes for carrying out the invention]

[0157] The present invention will be illustrated in detail by the following examples, without any intention to limit it. The following embodiments are also included in this disclosure and may be incorporated in whole or in part into aspects of the invention and the general disclosure. Manipulation of UV / Vis spectra in single-photon experiments is performed by placing a cuvette containing the dissolved sample in a sample holder and then irradiating the cuvette. Changes in the UV / Vis spectrum are monitored over time by UV / Vis measurements, for example, using a UV / Vis spectrometer Lambda900 (PerkinElmer). As described below, the refractive index in single-photon experiments is manipulated by placing the sample in a sample holder and irradiating it for preferably 30 seconds. The resulting change in refractive index is monitored over time by refractive index measurement. The change in refractive index is measured using a multi-wavelength refractometer (Schmidt & Haensch ATR-L). Single-photon experiments demonstrate that the described polymer optical material for artificial lenses used in the process according to the present invention can locally alter its initial polarization properties through irradiation with specific first and second wavelengths, thereby enabling, for example, [2π+2π] cyclic addition or retrocyclic addition as described above or below. Alternatively, the artificial lens may be treated based on a multiphoton (e.g., two-photon) process, as further described below in Examples 14-19. Examples Example 1

[0158] Creating Poly(M-14): First, dissolve 1 g of M-14 in 10 mL of chloroform. Next, degas the solution and add 1.33 mg of AIBN. Then, stir the mixture at 60°C for 14 hours. After that, precipitate the polymer in 250 mL of methanol. Next, dry the resulting polymer, poly(M-14). Example 2

[0159] In the second example, a solution of 75.4 mg of poly(M-14) in 10 mL of THF is prepared. This is diluted 500-fold. The diluted solution is packed into a quartz glass cuvette (32 / GL14 / S / Q / 10, STARNA, 10 mm path length). The UV / Vis spectrum is acquired using a PerkinElmer Lambda900 UV / Vis spectrometer. The sample is irradiated alternately at 340 nm and the UV / Vis spectrum is acquired. The results are shown in Figure 12, showing the absorption as a function of wavelength of the single-photon process. Figure 12 shows three isosbestic points, indicating a controlled conversion. The photochemical reaction represented by this conversion is a [2π+2π] cyclic addition, resulting in a crosslinked polymer as shown in Figure 8. Dimerization of the photoactive unit is indicated by a descending 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(500MHz,CDCl3)δ7.45,7.17,7.08~7.03,7.01~6.96,6.84,6.75,6.61,6.52,4.96,4.72,4. 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 aforementioned 1 The singlet signals at 4.72 and 4.96 ppm in the 1H NMR spectrum are attributed to the cyclobutane ring formed via the aforementioned photochemical [2π+2π] cyclic addition reaction. These two signals are attributed to the formation of a mixture of photodimers consisting of syn and anti, head-head and head-tail configurations, respectively. The NMR signals and conclusions are consistent with the literature [Raoetal., Chem. Ber., 1973, 106(2), 388]. Example 3

[0161] In the third embodiment, the irradiated poly(M-14) prepared in Example 2 is used. UV / Vis spectra are acquired. The sample is irradiated at 275 nm, and UV / Vis spectra are acquired alternately. The results are shown in Figure 13, illustrating the absorption as a function of wavelength of the single-photon process. The aforementioned experiment demonstrates that typical polymer optical materials can cleave dimerized photoactive units. The amount of cyclobutane in the cross-linked poly(M-14) decreases. The mechanism of this cleavage is shown in Figure 9. Back conversion is indicated by an increasing signal at 332 nm.

[0162] The reaction mixture is dried and analyzed by NMR. 1 HNMR(500MHz,CDCl3)δ7.67,7.40,7.20~7.14,6.86,4.11~4.00,2.69~2.62,2.36,1.87~1.78,1.65,1.53~1.41,1.40~1.26,1.14,0.91 As can be seen further, the cyclobutane ring previously assigned to Example 2 was formed via a photo-induced photochemical [2π+2π] cyclic addition reaction. 1 The singlet phase disappears at 4.74 and 4.98 ppm, as demonstrated by the HNMR spectrum, confirming the cleavage as shown in Figure 9. Example 4

[0163] In the fourth embodiment, a polymer optical material having a copolymer matrix is ​​prepared.

[0164] First, a molten mixture of 2.00 g of M-14,10.36 mg of 2-[3-(2H-benzotriazole-2-yl)-4-hydroxyphenyl]ethyl methacrylate, 220.00 mg of poly(ethylene glycol) diacrylate (average Mn250), and 247.60 mg of n-butyl methacrylate is 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 in a 1 mm thick sheet mold. Polymerization is thermally carried out under conditions that a person skilled in the art would consider appropriate. After the polymerization process is complete, the polymer is demolded to obtain a 1 mm thick polymer sheet. Example 5

[0165] In the fifth embodiment, a cylindrical blank of the polymer optical material prepared in Example 4 is punched out from a sheet. A multi-wavelength refractometer with a heating stage is used to determine the refractive index. Before measurement, the blank is heated to 80°C in the device to release stress from the material. In this embodiment, the refractive index is measured at 546 nm and 35°C. Outside the refractometer, the blank is irradiated at 340 nm in the apparatus shown in Figure 10. The sample is returned to the refractometer, heated to 80°C, and the refractive index is measured at 546 nm and 35°C. Figure 14 shows the change in 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 crosslinking reaction shown in Figure 8. The cyclic addition reaction shown in Figure 8 yields a low-polarization photoactive unit (cyclobutane ring), which reduces the refractive index. Samples irradiated at 340 nm are used further in the procedures described herein, but with an irradiation wavelength of 275 nm.

[0166] The effect shown in Figure 15 is due to the cleavage or backconversion of the cyclobutane moiety (see Figure 9). This increases polarization and the refractive index. Figure 15 shows the change in refractive index of the single-photon process as a function of the applied energy.

[0167] Figure 10 shows the 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 the sample (406). In this Example 5, the irradiation source (402) is Thorlabs' MountedLEDM340L4-340nm, 53mW.

[0168] Examples 6 to 10 are carried out in the same manner as Examples 1 to 5 outlined above. Example 6 Creating 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 in 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) is prepared in 25 mL of THF. This is then diluted 20-fold. The diluted solution is packed into a quartz glass cuvette. A UV / Vis spectrum is obtained. The sample is alternately irradiated at 340 nm, and a UV / Vis spectrum is obtained. 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 embodiment, the irradiated poly(M-18) sample from Example 7 is used. The UV / Vis spectrum is acquired. The sample is further irradiated at 275 nm, and the UV / Vis spectra are acquired alternately. 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 embodiment, a second polymer optical material having a copolymer matrix is ​​prepared. 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 2-octadecyl methacrylate is degassed. Then, 26.42 mg of 1,1'-(3,3,5-trimethylcyclohexylidene)bis[2-(1,1-dimethylethyl) peroxide is added. The mixture is filtered and placed in a 1 mm thick sheet mold. Polymerization is thermally carried out under conditions that a person skilled in the art would consider appropriate. After the polymerization process is complete, the polymer is demolded to obtain a 1 mm thick polymer sheet. Example 10

[0172] In the tenth embodiment, a cylindrical blank of ophthalmic material prepared in Example 9 is punched out from a sheet. A multi-wavelength refractometer with a heating stage is used to determine the refractive index. Before measurement, the sample is heated to 80°C in the device to release stress from the material. The refractive index is measured at 546 nm and 35°C. Alternating between irradiating the sample with 340 nm, returning the sample to the refractometer, heating it to 80°C, and measuring the refractive index at 546 nm and 35°C. The results are shown in Figure 18. Thus, Figure 18 shows the change in refractive index of the single-photon process as a function of the applied energy. The sample irradiated at 340 nm is used further in the procedure described herein, but with an irradiation wavelength of 275 nm. The effect shown in Figure 19 is due to cleavage or backconversion of the cyclobutane moiety (see Figure 9). Figure 19 shows the change in refractive index of the single-photon process as a function of the applied energy. Examples 11-13

[0173] Examples 11-13 below have copolymer matrices containing the amounts of polymerization monomers M-58, M-56, or M-15 shown in the table below, and demonstrate the refractive index change during irradiation in a single-photon process for polymer optical materials based on the formulation described in Example 9: [Table 1]

[0174] Examples of irradiation involving two-photon / multiphoton absorption: Example 14 The experimental device used in Example 14 is shown in Figure 11. The two-photon experimental system (410) in Figure 11 incorporates a tunable laser (412) (Ti:Sapphirelaser (ChameleonUltraII by Coherent, Santa Clara, CA, USA)) 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 the microscope objective lens (416) (LUCPLFLN in Olympus) to become the output of the focused laser radiation. A region of a polymer optical material (sample 418) with a changing refractive index is directed towards a target via a voice coil-driven linear stage (422) (PIMag®) used to position a sample holder (420).

[0175] The polymer sample (418) described herein is a 6.0 mm diameter flat button of the polymer optical material described below. All polymers in the aforementioned polymer samples are copolymers containing at least a crosslinking agent. The main monomers used in the manufacture of polymer optical materials containing copolymer matrices are summarized in the following table for each button material. [ka]

[0176] During the irradiation process, the flat button of the polymer material described above, as the polymer sample (418), is placed in a fixed position within the sample holder (420). Coupling gel (Vidisic [Bausch & Lomb]) is applied to the button. The sample holder (420) is mounted horizontally, and laser pulses are focused onto the material using a high numerical aperture microscope objective lens. The refractive index molded body is created near the surface. This is similar to the "bottom-up" and "spot-to-spot" procedures. As mentioned earlier, the sample holder (420) is driven by the voice coil linear stage (422). 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 variable parameters are the scanning speed and the spacing x between layers. By adjusting these three parameters, a uniform solid refractive index molded body is created. The change in refractive index is measured using a multi-wavelength refractometer (Schmidt & Haensch ATR-L).

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

[0178] In the 15th example, a solution of 288 mg of poly(M-14) (Example 1) was prepared in 4 mL of acetonitrile. The solution was packed into a quartz glass cuvette (32 / GL14 / S / Q / 10, STARNA, path length 10 mm). The cuvette containing the liquid solution of poly(M-14) was irradiated with a 1 μJ pulse at a wavelength of 680 nm at a repetition rate of 100 kHz using an NA0.1 microscope objective lens. The two-photon generation fluorescence of the solution was measured as a function of irradiation time using a pulsed irradiation source as described above. The fluorescence was measured with sensitivity from 350 to 1050 nm using fiber-coupled and diffraction grating-based spectrometers, geometrically positioned at 90 degrees relative to the irradiation beam. The fluorescence spectra with increasing irradiation time are summarized in Figure 20. The two-photon-induced [2π+2π] cyclic dimerization reaction of the photoactive unit is indicated by a falling signal between 400 and 500 nm. Conversion to a non-fluorescent dimer in poly(M-14) reduces the emission peak. The reaction mixture is dried and analyzed by NMR with chloroform-d. Singlets at 4.74 and 4.98 ppm are attributed to the cyclobutane ring formed via the two-photon-induced photochemical [2π+2π] cyclic addition reaction. The NMR spectra correlate with those of Example 2. Both single-photon and two-photon-induced photochemical [2π+2π] cyclic addition reactions yield 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, STARNA, 10 mm path length). The solution is irradiated with a 1 μJ pulse at a wavelength of 532 nm and a repetition rate of 100 kHz using an NA0.1 microscope objective lens. The amount of cyclobutane moiety in the substrate decreases over time during laser irradiation due to a two-photon-induced photochemical [2π+2π] retrocyclization reaction. The reaction mixture was dried and analyzed by chloroform-d NMR. The singlets at 4.74 and 4.98 ppm, previously assigned to the cyclobutane ring formed via the two-photon-induced photochemical [2π+2π] cyclic addition reaction in Experiment 14, disappeared. The results of the two-photon-induced photochemical [2π+2π] retrocyclization correlated with the single-photon-induced photochemical [2π+2π] retrocyclization experiment in Example 3. Example 17

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

[0181] In the 18th example, a polymer optical material having a copolymer matrix is ​​prepared. First, 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 degassed. Then, 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 1 mm thick sheet mold. Polymerization is thermally induced under conditions known in the art. After the polymerization process is complete, the polymer is demolded to obtain a 1 mm thick polymer sheet. A cylindrical blank of the optical material is punched out from the sheet. Example 19

[0182] In the 19th embodiment, a cylindrical blank of optical material prepared in Example 18 is used. The two-photon-induced photochemical crosslinking reaction of the optical material is demonstrated using two different irradiation sources as described above, in the setting shown in Figure 11. One irradiation source, classified as "kHz" in Figure 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 Figure 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, the optical path length difference of the entire sample is measured for each measurement using an optical phase-sensitive camera. The refractive index of the material in the irradiated area is estimated from the optical path length difference and the thickness of the sample. The refractive index change (Δn) shown in Figure 22 is obtained by comparing the irradiated and unirradiated areas. The successive data points from low to high radiation exposure doses (applied energy) indicate the cumulative effect of the irradiation treatment because the duration of irradiation increases. This cumulative effect allows for a more accurate translation of physician requirements into corresponding treatment plans.

[0183] Figure 22 also shows the difference in overall system efficiency between kHz and MHz irradiation sources. With all system settings identical, the kHz system exhibits a significantly increased write speed and, therefore, a shorter and more desirable treatment time. This result indicates that the two-photon-induced photochemical [2π+2π] cyclic dimerization reaction is more efficient for the kHz system, which is consistent with the conclusions drawn from the excited state lifetimes described above. Example 20

[0184] In this embodiment, a cylindrical blank of the optical material prepared in Example 18 is used. The two-photon-induced photochemical crosslinking reaction of the optical material is demonstrated using different irradiation wavelengths. The radiation source used is a femtosecond laser tuned between 666 and 722 nm, emitting μJ pulses at a repetition rate of 100 kHz. The setup shown in Figure 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 with the same overall radiation exposure. The refractive index of the material in the irradiated area is estimated from the optical path length difference and the thickness of the sample. The refractive index change (Δn) shown in Figure 23 is obtained by comparing the irradiated and unirradiated areas. The data shown in Figure 23 demonstrates that a modification of the refractive index can be created within the optical material by efficiently using the range of 680-720 nm.

[0185] Figure 24 shows a selected example of the refractive index profile written to the optical material during this experiment. In this embodiment, 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. Data is collected at 10x magnification using a phase-sensitive camera system mounted on a microscope. 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. Figure 24 shows that the refractive index of the irradiated area is reduced by approximately 0.011 compared to the surrounding unirradiated material.

Claims

1. A system for irradiating artificial lenses, the system is One or more irradiation sources (1) for two-photon or multi-photon irradiation are provided on the artificial lens (3), which are focused by an optical section (16) and irradiate the lens (3) with an irradiation beam (2) having a first wavelength and / or a second wavelength different from the first wavelength. A scanner (4) connected to one or more light sources (1) and configured to scan the light beam (2) across the artificial lens (3), and The system includes one or more irradiation sources (1) and an input unit (6) connected to a 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 is between 600 nm and 800 nm in order to locally reduce the polarization of the artificial lens based on the treatment of the artificial lens. The second wavelength is between 400 nm and 590 nm in order to locally increase the polarization of the artificial lens (3) based on the treatment of the artificial lens. The aforementioned system.

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

3. The system according to claim 1 or 2, wherein an artificial lens (3) is placed inside the patient's eye.

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) relating to a treatment plan for the treatment of the artificial lens (3).

5. The system according to claim 4, wherein the lens data (10) includes data relating to the radiant absorption characteristics of the artificial lens (3), and the system is configured to adjust a first wavelength and / or a second wavelength based on a two-photon or multi-photon absorption process so that the artificial lens locally changes its polarization.

6. The system further includes a positioning system (20) for determining the focal position of the irradiation beam (2) within the eye of the patient, The positioning system (20) is connected to a scanner (4), and the scanning of the irradiation beam (2) across the artificial lens (3) by the scanner is based on the position of the focal point of the irradiation beam in the eye, according to any one of claims 2 to 5.

7. The system is configured to determine the position and / or orientation of the artificial lens (3) relative to the eye and the exit of the irradiation beam. The scanning of the illumination 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, according to any one of claims 2 to 6.

8. A system according to any one of claims 1 to 7, (i) one or more light 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 portion of the artificial lens (3) during the scanning treatment of the artificial lens (3) 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 (i) one or more irradiation sources (1) and (ii) one or both of the scanner (4) based on the temperature determination. The aforementioned system.

9. The system according to claim 8, wherein a temperature control unit (14) is configured to predict the temperature of the artificial lens (3) during the treatment, 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 patient's eye in a fixed position.

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

12. The method according to claim 11, wherein the adjustment of the polarization of the artificial lens comprises the system according to any one of claims 1 to 10 reducing the polarization by irradiating the artificial lens with an irradiation beam having a wavelength between 600 nm and 800 nm, thereby changing the polymer optical material with respect to the non-irradiated polymer optical material of the artificial lens, i.e., a loss of peak absorption in the range of 300 nm to 400 nm.

13. The method according to claim 11, wherein the adjustment of the polarization of the artificial lens comprises increasing the polarization by irradiating the artificial lens with an irradiation beam having a wavelength between 400 nm and 590 nm, thereby changing the polymer optical material with respect to the unirradiated polymer optical material of the artificial lens, i.e., an increase in peak absorption in the range of 300 nm to 400 nm.

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 containing a non-aromatic double bond that can be dimerized by forming a cyclobutane ring by [2π + 2π] cyclic addition 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 covalently bonded photoactive units that can be dimerized together with already dimerized photoactive units by forming a cyclobutane ring by [2π + 2π] cyclic addition under the influence of a two-photon or multi-photon process, together with the photoactive units, by forming a cyclobutane ring by a non-aromatic double bond.

16. The method according to claim 11 or 13, wherein the polymer optical material of the artificial lens comprises a polymer matrix containing dimerized photoactive units covalently bonded as a single photoactive unit that can be separated under the influence of a two-photon or generally multi-photon process.

17. A method according to any one of claims 11 to 14, The system according to any one of claims 1 to 10 irradiates an artificial lens comprising a polymer matrix containing a covalently bonded photoactive unit having a non-aromatic double bond that can be dimerized by forming a cyclobutane ring by [2π+2π] cyclic addition with an irradiation beam of a first wavelength, wherein the irradiation causes dimerization of the photoactive unit, thereby reducing the polarization of the artificial lens, thereby modifying the provided artificial lens, the modified artificial lens comprising a polymer matrix containing a partially or completely dimerized photoactive unit derived from the [2π+2π] cyclic addition Optionally, in order to locally increase the polarization of the modified artificial lens by partially cutting 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 comprises a polymer matrix containing photoactive units that can be re-dimerized, wherein the irradiation irradiates an artificial lens 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, the modified artificial lens comprising photoactive units that can be re-dimerized, The method according to claim 16, wherein the system according to any one of claims 1 to 10 irradiates the modified artificial lens with an irradiation beam of a first wavelength in order to optionally reduce the polarization of the modified artificial lens by partially dimerizing the photoactive unit.

19. A system according to any one of claims 1 to 10, wherein the artificial lens is irradiated with an irradiation beam of a first wavelength, the irradiation causing dimerization of the photoactive units, thereby reducing the polarization of the artificial lens, thereby modifying the provided artificial lens, the modified artificial lens comprising a polymer matrix containing more dimerized photoactive units derived from the [2π + 2π] cyclic addition, 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, the irradiation causing separation of the dimerized photoactive units, thereby increasing the polarity of the artificial lens, thereby modifying the provided artificial lens, the modified artificial lens comprising a polymer matrix containing more photoactive units that can be dimerized by forming a cyclobutane ring by [2π + 2π] cyclic addition.

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

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