WO2025085626A1 - Procédé de changement d'indice de réfraction induit par laser et produit ophtalmique traité par ledit procédé - Google Patents

Procédé de changement d'indice de réfraction induit par laser et produit ophtalmique traité par ledit procédé Download PDF

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WO2025085626A1
WO2025085626A1 PCT/US2024/051757 US2024051757W WO2025085626A1 WO 2025085626 A1 WO2025085626 A1 WO 2025085626A1 US 2024051757 W US2024051757 W US 2024051757W WO 2025085626 A1 WO2025085626 A1 WO 2025085626A1
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laser
silk fibroin
ophthalmic
refractive index
optical device
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Wayne H. Knox
Quazi Rushnan ISLAM
Susana Marcos Celestino
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University of Rochester
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University of Rochester
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/14—Eye parts, e.g. lenses or corneal implants; Artificial eyes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/14—Macromolecular materials
    • A61L27/22—Polypeptides or derivatives thereof, e.g. degradation products
    • A61L27/227—Other specific proteins or polypeptides not covered by A61L27/222, A61L27/225 or A61L27/24
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/52—Hydrogels or hydrocolloids
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B1/00—Optical elements characterised by the material of which they are made; Optical coatings for optical elements
    • G02B1/04—Optical elements characterised by the material of which they are made; Optical coatings for optical elements made of organic materials, e.g. plastics
    • G02B1/041—Lenses
    • G02B1/043—Contact lenses
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/14—Eye parts, e.g. lenses or corneal implants; Artificial eyes
    • A61F2/16—Intraocular lenses
    • A61F2/1613—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • A61F2/1624—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside
    • A61F2/1627—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus having adjustable focus; power activated variable focus means, e.g. mechanically or electrically by the ciliary muscle or from the outside for changing index of refraction, e.g. by external means or by tilting
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F9/00—Methods or devices for treatment of the eyes; Devices for putting in contact-lenses; Devices to correct squinting; Apparatus to guide the blind; Protective devices for the eyes, carried on the body or in the hand
    • A61F9/007—Methods or devices for eye surgery
    • A61F9/008—Methods or devices for eye surgery using laser
    • A61F2009/00842—Permanent Structural Change [PSC] in index of refraction; Limit between ablation and plasma ignition
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2430/00—Materials or treatment for tissue regeneration
    • A61L2430/16—Materials or treatment for tissue regeneration for reconstruction of eye parts, e.g. intraocular lens, cornea

Definitions

  • Femtosecond micromachining is a process that uses femtosecond lasers to deliver a large amount of energy to a small area, creating localized changes in a material’s properties.
  • femtosecond lasers By scanning a tightly focused pulse in the material, a wide range of nano- and microstructures can be inscribed in metals, plastics, ceramics, and biological tissues. This technique is often used in the production of microfluidic devices, and other microscale components for various purposes, including data storage, drug delivery, and environmental monitoring.
  • femtosecond lasers can be used to create localized refractive index changes in transparent materials without the damage or removal of the material.
  • LIRIC Laser Induced Refractive Index Change
  • 2008/0001320 the disclosure of which is incorporated herein by reference in its entirety, more particularly describes methods for modifying the refractive index of optical polymeric materials, such as intraocular lenses, corneal inlays, or contact lenses, using very short pulses from a visible or near-IR laser having a pulse energy from, e.g., 0.5 nJ to 1000 nJ, where the intensity of light is sufficient to change the refractive index of the material within the focal volume, whereas portions just outside the focal volume are minimally affected by the laser light.
  • Irradiation within the focal volume results in refractive optical structures characterized by a change in refractive index of 0.005 or more relative to the index of refraction of the bulk (non-irradiated) polymeric material. Under certain irradiation conditions and in certain optical materials, a change in refractive index of 0.06 was measured.
  • the change in refractive index can be used to form patterned desired refractive structures in the optical polymeric material.
  • U.S. Publication No. 2012/0310340 further describes a method for providing changes in refractive power of an optical device made of an optical, polymeric material by forming at least one laser-modified, gradient index (GRIN) layer disposed between an anterior surface and a posterior surface of the device by scanning with light pulses from a visible or near-IR laser along regions of the optical, polymeric material.
  • GRIN gradient index
  • the at least one laser-modified GRIN layer comprises a plurality of adjacent refractive segments, and is further characterized by a variation in index of refraction of at least one of: (i) a portion of the adjacent refractive segments transverse to the direction scanned; and (ii) a portion of refractive segments along the direction scanned.
  • a method of forming a silk fibroin containing optical device with a modified refractive index pattern provided therein comprises: providing an optical device comprising an ophthalmic material made primarily of silk fibroin; and forming at least one laser-modified pattern within the optical device by exposing regions of the ophthalmic material to light pulses from a laser to cause changes in the ophthalmic material in the exposed regions sufficient to cause a change in refractive index of the exposed regions relative to the refractive index of the ophthalmic material in non-exposed regions.
  • the laser exposure may be performed by scanning focused pulses from the laser along regions of the ophthalmic material;
  • the ophthalmic material may comprise a silk fibroin hydrogel material;
  • the silk fibroin hydrogel material may be obtainable by polymerizing one or more hydrophilic monomers and silk fibroin in the presence of a copolymerization initiator; and/or the silk fibroin hydrogel material may be more particularly obtainable by polymerizing hydroxy ethyl methacrylate (HEMA), ethylene glycol dimethacrylate (EGDMA), and silk fibroin in the presence of a copolymerization initiator.
  • HEMA hydroxy ethyl methacrylate
  • EGDMA ethylene glycol dimethacrylate
  • FIG. 1A is an illustration of a corneal inlay inserted into a cornea to produce a “bump” in the cornea surface to add power.
  • Fig. IB is an illustration of a nominally flat corneal inlay with add power written in the inlay by LIRIC inserted into a cornea to add power without producing a “bump” in the cornea surface.
  • Figs. 2A-2C illustrate placement of a silk material on exposed cornea stroma bed without performing LASIK ablation, and subsequent LIRIC laser writing of a correction pattern in the silk layer.
  • Figs. 3A-3C illustrate placement of a silk material on exposed cornea stroma bed after performing LASIK ablation, and subsequent LIRIC laser writing of a correction pattern in the silk layer.
  • Fig. 4 is a schematic illustrating a laser writing system employed in one embodiment of the disclosure.
  • Figs. 5A and 5B illustrate an interference pattern and corresponding retrieved phase shift obtained for a phase bar written in a silk -hydrogel composite material in one embodiment of the disclosure.
  • Fig. 6 is a bright field image of phase bars written in a silk-hydrogel material at varying scan speeds in an embodiment of the disclosure.
  • Fig. 7 is a schematic illustrating a second laser writing system employed in an embodiment of the disclosure.
  • Figs. 8 A and 8B illustrate differential interference contrast in transmision mode (TDIC) and bright field microscopy in transmision mode (TBF) images for phase bars written in wet silk fibroin material material at varying average power in an embodiment of the disclosure.
  • Fig. 9A is a plot of the magnitude of phase shift induced versus the average writing power obtained in an embodiment of the disclosure.
  • Fig. 9B is a differential interference contrast in reflection mode (RDIC) image for phase bars written in a silk-hydrogel composite material at varying average power in an embodiment of the disclosure.
  • RDIC differential interference contrast in reflection mode
  • Figs. 10A and 10B illustrate bright field microscopy in reflection mode (TBF) and differential interference contrast in reflection mode (RDIC) and images for phase bars written in wet silk fibroin material material at varying scan speeds in an embodiment of the disclosure.
  • Figs. 10C and 10D illustrate an interference pattern and corresponding retrieved phase shift obtained for a phase bar written in hydrated silk material autoclaved in saline solution in one embodiment of the disclosure.
  • the present disclosure is directed towards forming at least one laser-modified refractive index pattern within an optical device comprising an ophthalmic material made primarily of silk fibroin.
  • Silk fibroin a protein produced by the silkworm, is a natural compound and has been found to enhance the properties of synthetic polymers for eye implantation. It is transparent, biocompatible, and affordable.
  • Silk fibroin is an FDA-approved biomaterial. By being made primarily of silk fibroin, it is meant that the ophthalmic material comprises at least 50 wt% silk fibroin.
  • the present disclosure more specifically may be directed towards writing of laser- modified refractive index patterns in implantable optical devices comprising an ophthalmic material made primarily of silk fibroin, and in even more particular embodiments in such implantable optical devices which are designed for correcting presbyopia.
  • presbyopia affects everyone over the age of 50, reducing the eye’s ability to accommodate to near objects.
  • Many potential solutions to the problem have been developed such as multifocal contact and intra-ocular lenses, artificial iris implants, progressive eyeglasses, adjustable glasses, presbyopic LASIK surgery, comeal inlays that increase curvature in the corneal center, or accommodating IOLS.
  • the elements incorporate a vision corrector written with laser- induced refractive index change (LIRIC).
  • LIRIC laser- induced refractive index change
  • Multifocal corrections can come in the form of a contact lens, where the refractive power of a contact lens can be varied over the diameter of the lens by controlling the shape of the surface. This results in an increased range of well-focused vision.
  • multifocal designs have been developed in the form of intraocular lenses. These can be implanted when a patient is having their crystalline lenses removed due to the fomiation of cataracts that are degrading their quality of vision. More recently, refractive lens exchange procedures may be performed even in presbyopic patients with clear crystalline lenses, where the lens is being replaced by an artificial implant that provides distance correction as well as visual functionality at near focus, generally using multifocal or extended-depth-of-focus IOL designs.
  • presbyopia treatments that preserve the transparent crystalline lens (along with some potential -albeit diminished- accommodation functionality) have been preferred in relatively young presbyopes.
  • the treatments include Presbyopic LASIK where the cornea is sculpted to produce an increased power (near add) in the central cornea.
  • non-tissue subtraction refractive procedures are gaining traction. Unlike LASIK or Small Incision Lenticular Extraction (SMILE) procedures that eliminate corneal tissue, those would aim at inserting additional material to the cornea, or anterior segment in general (additive procedures). Procedures such as those aiming at changing the refractive properties of the tissue (such as LIRIC) will also fall into the category of non-tissue subtraction refractive procedures.
  • SMILE Small Incision Lenticular Extraction
  • a further alternative to induce multifocality or EDOF without removing ocular tissue are comeal inlays.
  • Those are lenticules with a prolate-shape inserted into a corneal incision to produce a “bump” in the cornea surface which can produce enhanced “add” power in the center of the cornea, such as the device called RAINDROPTM.
  • RAINDROPTM enhanced “add” power in the center of the cornea
  • phakic IOLS Another alternative of “tissue adding” procedure without removing the crystalline lens is phakic IOLS. Those are implanted generally between the iris and the crystalline lens. They have been typically used to correct myopia in young high myopes, where a LASIK procedure would require large reductions in corneal thickness. Since the phakic IOL is implanted without removing the natural crystalline lens the accommodation functioning is intact. Recently phakic IOLs have been expanded to include EDOF designs catering the relatively young presbyopes. It is recognized that biocompatibility of these lenses poses more challenges, given the higher proximity to ocular structures. To address this challenge, a copolymer of collagen and Hema has been proposed.
  • the market standard for phakic lens (ICLs, by Staar Surgical Optics) are made of collamer material, with 60% of polyhydroxy ethyl methacrylate (pHEMA), water (36%), benzophenone (3.8%), and 0.2% porcine collagen.
  • pHEMA polyhydroxy ethyl methacrylate
  • water 36%
  • benzophenone 3.8%
  • 0.2% porcine collagen The presence of collagen is claimed to have a positive effect in the hydrophilicity and exchange of gas and nutrients in the anterior chamber.
  • the present disclosure addresses the combined problems of complex biomechanical issues and biocompatibility by use of ophthalmic material comprising primarily silk fibroin and use of LIRIC femtosecond processing.
  • such solution may more particularly be used to advantageously addresses existing problems in presbyopia correcting procedures.
  • the disclosure relates to writing of refractive index change patterns in an ophthalmic material comprising primarily silk fibroin.
  • Silk fibroin is typically obtained from silk-cocoon in a known fashion, and may be solution cast to form a membrane.
  • the ophthalmic material comprising primarily silk fibroin may comprise a silk fibroin hydrogel material, and may be obtainable by polymerizing one or more hydrophilic monomers and silk fibroin in the presence of a copolymerization initiator.
  • the resulting silk hydrogel materials can be machined, molded or machined into, e.g., a contact lens, a corneal inlay, a phakic or a non-phakic IOL.
  • An ophthalmic material as described herein is understood as material that is suitable for ophthalmic applications, such as a hydrogel.
  • An ophthalmic material as described herein may initially be substantially free of water upon formation, e.g., has less than 0.5 wt.% of water.
  • the ophthalmic material e.g., when comprising hydrophilic monomers, may be hydrated upon addition of water to form a hydrated hydrogel. Accordingly, in various states the ophthalmic material may also be referred herein as to a dry ophthalmic material or dry hydrogel, and the hydrated hydrogel obtained may also be referred to as the hydrated ophthalmic material.
  • the ophthalmic material comprising primarily silk fibroin may be obtainable by polymerizing a first monomer and a second monomer in the presence of silk fibroin, as described in EP Appl. No. 23383047.0, filed October 11, 2023, wherein such materials are demonstrated to be bio-compatible and stable, well suited for ophthalmic applications such as ophthalmic lenses and/or implants and in particular for comeal inlay application.
  • the first and second monomers are monomers suitable for polymerization and may be selected from monomers typically used in ophthalmic applications. More particularly, in such embodiments the first monomer and the second monomer are different from each other.
  • the first and second monomer may be independently selected from a methacrylate, an acrylate, an acrylamide, a siloxane, a carbamate, a glycol, a dialdehyde, a vinyl and an allyl.
  • the methacrylate may be selected from hydroxy ethyl methacrylate (HEMA), ethylene glycol dimethacrylate (EGDMA), methacrylic acid (MAA), methyl methacrylate (MMA), oligo (ethylene glycol) methyl ether methacrylate (OEGMA), glycerol methacrylate (GMA), isobutyl methacrylate (IB MA), allyl methacrylate (AMA), 3- [tris(trimethylsiloxy)silyl] propyl methacrylate (TRIS), polypropylene glycol dimethylacrylate (PPGDMA) and methacryloyl oxyethyl phosphorylcholine (MPC); more preferably may be selected from HEMA and EGDMA; and yet more preferably the first monomer may be HEMA and/or the second monomer may be EGDMA.
  • HEMA hydroxy ethyl methacrylate
  • EGDMA ethylene glycol dimethacrylate
  • MAA methacrylic
  • an acrylate may be ethylene glycol phenyl ether acrylate (EGPEA); an acrylamide may be selected from N,N-dimethylacrylamide (DMA), diacetone acrylamide (DAA) and methylene -bis-acrylamide (MBA); a siloxane may be dimethylsiloxane (DMS), a carbamate may be tris(trimethylsioxy)silyl) propyl vinyl carbamate (TPVC), a glycol may be selected from diethylene glycol (DEG) and polyethylene glycol dialdehyde (PEG-DA), a vinyl may be N-vinyl pyrrolidone (N-VP) and an allyl may be diallyl maleate (DA).
  • EPG ethylene glycol phenyl ether acrylate
  • an acrylamide may be selected from N,N-dimethylacrylamide (DMA), diacetone acrylamide (DAA) and methylene -bis-acrylamide (MBA)
  • the first monomer may be preferably selected from a methacrylate such as HEMA, EGDMA, MAA, MMA, OEGMA, GMA, IBM A, AMA, TRIS; an acrylate such EGPEA; a methacrylamide DMA and DAA; a siloxane such as DMS; a carbamate such as TPVC; and a glycol such as DEG.
  • the first monomer may be HEMA.
  • the second monomer may be preferably selected from a methacrylate such as EGDMA and PPGDMA; an acrylamide such as MBA; a glycol such as PEG-DA; a vinyl such as N-VP; and an allyl such as DA.
  • the second monomer may be EGDMA.
  • the first and second monomer may be selected from hydrophilic monomers, in particular they may be selected from HEMA, EGDMA, EGPEA, DEG, and MPC, and more in particular from HEMA and EGDMA.
  • the first monomer is HEMA and/or the second monomer is EGDMA.
  • the first monomer is HEMA and the second monomer is EGDMA.
  • the use of such monomers may advantageously provide an ophthalmic material suitable for forming a hydrogel.
  • An ophthalmic material comprising primarily silk fibroin as described herein may typically have a weight proportion of the combination of the first and second monomers of 10-40 wt.% and more in particular, 20-25 wt.%, and silk fibroin weight proportion of 60-90 wt.% and more particularly 75-80 wt.%, based on the total weight of first monomer, second monomer and SILK FIBROIN. Thus, such materials continue to comprise primarily silk fibroin.
  • An ophthalmic material as described for use herein obtainable from such reaction mixtures may typically have a weight ratio of the first monomer to the second monomer of greater than 1:1, e.g., from 2:1 to 40:1, in particular from 3:1 to 35:1, more in particular from 5:1 to 30 : 1 , yet more in particular from 7:1 to 25 : 1.
  • Useful polymerization initiators may be selected, e.g., from azobisisobutyronitrile (AIBN), ammonium persulfate (APS), tetramethyl ethylenediamine (TEMED), and benzoyl peroxide (BP), and more preferably the polymerization initiator is AIBN.
  • AIBN azobisisobutyronitrile
  • APS ammonium persulfate
  • TEMED tetramethyl ethylenediamine
  • BP benzoyl peroxide
  • Such initiators are known in the art and may initiate the polymerization reaction by, e.g., application of heat.
  • the ophthalmic material upon addition of water the ophthalmic material may form a hydrogel.
  • the hydrogel in hydrated form may comprise, e.g., 10 to 40 wt.% of water, in particular from 12 to 30 wt.% of water, based on the total weight of the hydrogel.
  • the silk hydrogel materials can be machined, molded or machined into, e.g., a contact lens, a corneal inlay, a phakic or a non-phakic IOL.
  • the ophthalmic material comprising primarily silk fibroin is well suited for ophthalmic lenses and/or implants.
  • the ophthalmic material as such may be used in dry forms for the formation of said ophthalmic lenses and/or implants, or may be hydrated to form a hydrated hydrogel to form said ophthalmic lenses and/or implants.
  • desired refractive index change patterns may be formed in an ophthalmic material comprising primarily silk fibroin as described herein by irradiating the ophthalmic material with very short laser pulses of light as described in U.S. Publication Nos. 2008/0001320, 2009/0287306, 2012/0310340 and 2012/0310223.
  • the femtosecond laser pulse sequence pertaining to an illustrative embodiment e.g., operates at a high repetition-rate, e.g., 80 MHz, and consequently the thermal diffusion time (>0.1 ps) is much longer than the time interval between adjacent laser pulses ( ⁇ 11 ns). Under such conditions, absorbed laser energy can accumulate within the focal volume and increase the local temperature.
  • Femtosecond laser pulse writing methods may be more advantageously carried out if the ophthalmic material further includes a photosensitizer, as more particularly taught in U.S. Publication Nos. 2009/0287306 and 2012/0310340.
  • the presence of the photosensitizer permits one to set a scan rate to a value that is at least fifty times greater, or at least 100 times greater, than a scan rate without a photosensitizer present in the material, and yet provide similar amount of non-linear absorption in the focal volume.
  • a photosensitizer may permit one to set an average laser power to a value that is at least two times less, more particularly up to four times less, than an average laser power without a photosensitizer in the material, yet provide similar results.
  • a photosensitizer having a chromophore with a relatively large multi-photon absorption cross section is believed to capture the light radiation (photons) with greater efficiency and then transfer that energy to the material within the focal volume.
  • the photosensitizer may include, e.g., a chromophore having a two-photon, absorption cross-section of at least 10 GM between a laser wavelength range of 750 nm to 1100 nm.
  • solutions containing a photosensitizer may be prepared and the ophthalmic materials may be allowed to come in contact with such solutions to allow up-take of the photosensitizer into the matrix of the material.
  • monomers containing a chromophore e.g., a fluorescein-based monomer, may be used in a monomer mixture used to form the ophthalmic material such that the chromophore becomes part of the resulting polymeric matrix.
  • chromophoric entities could be the same or different in each respective photosensitizer.
  • the concentration of a polymerizable, monomeric photosensitizer having a two-photon, chromophore in an ophthalmic material can be as low as 0.05 wt.% and as high as 10 wt.%.
  • Exemplary concentration ranges of polymerizable monomer having a two-photon, chromophore in a hydrogel material is from 0.1 wt.% to 6 wt.%, 0.1 wt.% to 4 wt.%, and 0.2 wt.% to 3 wt.%.
  • the concentration range of polymerizable monomer photosensitizer having a two-photon, chromophore in a hydrogel material is from 0.4 wt.% to 2.5 wt.%.
  • the accumulated focal temperature increase can be much larger than the temperature increase induced by a single laser pulse.
  • the accumulated temperature increases until the absorbed power and the dissipated power are in dynamic balance.
  • thermal-induced depolymerization can produce a change in the refractive index as the local temperature exceeds a transition temperature. If the temperature increase exceeds a second threshold, a somewhat higher temperature than the transition temperature, the polymer is pyrolytically degraded and carbonized residue and water bubbles are observed. In other words, the material exhibits visible optical damage (scorching).
  • Each of the following experimental parameters such as laser repetition rate, laser wavelength and pulse energy, TPA coefficient, and water concentration of the materials should be considered so that a desired change can be induced in the hydrogel polymers without optical damage.
  • the pulse energy and the average power of the laser, and the rate at which the irradiated regions are scanned, will in-part depend on the specific composition of the material that is being irradiated, how much energy absorption is required to create a desired refractive index change in the material.
  • the selected pulse energy will also depend upon the scan rate and the average power of the laser at which the refractive index change features are written into the material. Typically, greater pulse energies will be needed for greater scan rates and lower laser power. For example, some materials will call for a pulse energy from 0.05 nJ to 100 nJ or from 0.2 nJ to 10 nJ.
  • a Fresnel-type phase wrapped refractive index profde may be written into the silk-optical material, in any of the above-mentioned platforms.
  • an advantage of the use of ophthalmic materials comprising primarily silk fibroin is the use of a naturally based material, produced by green chemistry, more biodegradable and alleviating the impact of microplastics on health and environment.
  • accurate and custom refractive index change pattern corrections can be advantageously written in this type of ophthalmic material.
  • FIG. 1 A shows a current approach using a prolate-shaped inserted object 101 in the cornea 102 causing a “bump” 103 in the corneal surface, thereby providing increased refractive optical power in the central zone.
  • a “pocket” 104 is cut into the corneal tissue using conventional cornea cutting laser techniques.
  • a nominally flat or slightly curved piece of a silk bio-compatible material such as a silk-hydrogel composite material 105 in one embodiment, is first treated by laser scanning to produce the desired refractive correction using a LIRIC technique as described herein (see also Wayne H. Knox, “Inventing a new way to see clearly,” Technology & Innovation, Volume 20, Number 4, August 2019, pp. 385-398(14), Publisher: National Academy of Inventors; Gustavo A. Gandara-Montano, L. Zheleznyak, and Wayne H. Knox, “Optical quality of hydrogel ophthalmic devices created with femtosecond laser induced refractive index modification,” Optical Materials Express, Vol. 8, No.
  • FIGs 2A-2C (wherein a cornea flap 211 is cut in cornea 202 in Figure 2 A, as in a first step of conventional LASIK; Silk optics layer 205 is placed over exposed stroma bed and the flap is reset in Figure 2B; and LIRIC custom vision correction pattern is written into the Silk layer at a later time by exposure to laser 213 in Figure 2C) further show that the layer of silk material could be placed on top of an exposed stroma in a normal LASIK procedure, and then covered for later use in vision correction, without performing any LASIK ablation.
  • the silk optics layer could provide a refractive index change profile that is more stable over time than when writing LIRIC directly into the cornea stroma (Len Zheleznyak et al, “First-in-human laser-induced refractive index change (LIRIC) treatment of the cornea,” Investigative Ophthalmology & Visual Science July 2019, Vol.60, 5079).
  • LIRIC First-in-human laser-induced refractive index change
  • Figures 3A-3C (wherein a cornea flap 311 is cut in cornea 302 in Figure 3A, as in a first step of conventional LASIK, and normal LASIK ablation procedure is performed on the exposed stroma bed to form a modified surface 314;
  • Silk optics layer 305 is placed over the exposed stroma bed modified surface 314 and the flap is re-set in Figure 3B; and LIRIC custom vision correction pattern is written into the Silk layer at a later time by exposure to laser 313 in Figure 3C) show that the silk optics layer could be incorporated into a full LASIK procedure.
  • the silk optics layer can be placed over the exposed LASIK modified cornea stroma and then the flap closed. Then, at any later date as desired, the LASIK treatment could be adjusted without having to relift the flap (which is not recommended) by simply writing the LIRIC refractive correction directly into the silk layer.
  • a similar approach can be applied on phakic or non-phakic IOLS where the lenses can be manufactured in a biocompatible material comprising primarily silk fibroin, and refractive index profiles can be written using the LIRIC procedure (either pre- or post- implantation).
  • LIRIC results have been obtained in a silk-hydrogel composite material comprising primarily silk fibroin.
  • the silk hydrogel composite material was obtained by polymerizing 25 wt.% of HEM A and EGDMA monomers (in a proportion HEMA to EGDMA of 17:1) and 75wt.% of Silk fibroin, based on the total weight of monomers and silk fibroin as described in the examples of EP AppL No. 23383047.0 filed October 11, 2023.
  • the monomer mixture was prepared by stirring the monomers in liquid form, and adding a 0.6 wt.% of AIBN as polymerization initiator with respect to the total weight of HEMA and EGDMA.
  • the AIBN is dissolved into the monomer mixture by using ultrasound to provide a polymerization mixture.
  • a 3% silk fibroin solution in water was prepared.
  • An appropriate weight of polymerization mixture including AIBN was added to the silk fibroin solution in order to have a 25% in weight of monomers with respect to the total weight of monomers and silk fibroin.
  • the silk fibroin solution was stirred with the polymerization mixture at 700 RPM for 2 minutes.
  • the obtained reaction mixture was cast in a petri dish, covered with a lid and polymerized at 60°C overnight.
  • FIG. 4 shows the laser writing system that was used.
  • a mode locked Ti:Sapphire laser 421 (Vitesse; Coherent Corporation, Santa Clara, CA, USA) emitting 800nm, ⁇ 100fs pulses at 80MHz was employed, where the 800nm beam was first frequency doubled to 400nm with a second harmonic generator 422.
  • a variable neutral density filter 423 is introduced into the beam path to vary the writing power of the system.
  • Using a 400 nm laser at 80 MHz repetition rate we wrote a series of phase bars in a piece of silk-hydrogel composite 405 that was 100 microns thick, focusing the laser beam with objective 424 and scanning at a range of scan speeds and with a system effective NA of 0.4.
  • FIG. 5A and 5B shows a result obtained when writing phase bars of 50 microns width in the silk-hydrogel composite material at a scan speed of 15 mm/sec and average power of 39 mW.
  • Figure 5 A shows a Mach-Zehnder interference pattern caused by transmission through a phase bar
  • Figure 5B shows the retrieved phase shift measured at 633 nm, corresponding to a phase shift of -0.89 waves, indicating that phase shifts of almost one wave are obtainable at relatively low average powers and reasonable scan speeds.
  • Figure 6 shows a further bright field photo of three phase bars 631, 631, 633 written in the silk-hydrogel material at 5, 10 and 15 mm/sec scan speeds, respectively, with a system effective NA of 0.4.
  • the phase bars are clear and transparent, indicating pure phase shift has been written in the material.
  • a second femtosecond micromachining system was used to demonstrate the application of silk fibroin as a contact lens material for large scale production of refractive correctors (setup shown in Fig. 7).
  • the system includes a KM Labs Y-Fi (Ytterbium fiber) laser 721, which delivers 1035nm, 120fs pulses at 8.3MHz.
  • the Y-fi laser contains an internal second harmonic generator that frequency doubles the pulses to produce 517 nm laser beam.
  • a combination of low GDD mirrors and a silver mirror is used to steer the 517 nm beam from the source through a microscope objective 724 (Olympus UPLFLN 40X 0.75NA) that is connected to a vertical stage 726 (Newport GTS30V) to adjust Z-height determined by a back reflection monitor 728.
  • the silk fibroin sample is mounted to a 2D translation stage 727 (Aerotech PRO115LM) and scan speeds of 20 to 200mm/s was used at an average power of 507mW. Multiple phase bars were also written with a set scan speed of 50mm/s and average power varying from 370-980mW in four identically produced wet silk fibroin samples to determine LIRIC scalability with writing power.
  • the samples were then autoclaved in saline solution at 121°C to allow the written regions to attain maximum phase shift.
  • Figs. 8 A and 8B illustrate differential interference contrast in transmision mode (TDIC) and bright field microscopy in transmision mode (TBF) images for pairs of 30um wide phase bars written with 517nm 8.3MHz 50mm/s effective NA 0.6 at different average powers of 451mW and 502mW in wet silk fibroin material with 50um scale bars.
  • TDIC transmision mode
  • TBF transmision mode
  • Fig. 8B transparent phase bars are observed while the corresponding TDIC images (Fig. 8A) showed relief at the edges of the phase bars indicating the presence of phase objects without damage.
  • phase bars 9B is a differential interference contrast in reflection mode (RDIC) image for phase bars written at average powers of 449 mW, 502 mW, 546 mW, and 608 mW, illustrating the onset of damage at an average power of 608mW.
  • Phase bars written with powers equal to and above 608 mW showed dark regions and portions missing, indicating the onset of damage. Also, regions written above 608mW, which exhibited smooth phase bars under differential interference contrast in reflection mode (RDIC), appeared with distorted edges under the interferometer making it difficult to construct phase maps.
  • RDIC differential interference contrast in reflection mode
  • Figs 10A-B show bright field microscopy in reflection mode (RBF) 300x (Fig. 10A) and RDIC 300x (Fig. 10B) images of phase bars written at 80, 60, 40, and 20mm/s (left to right) at an average power of 507mW.
  • phase bars written at speeds above 80mm/s were very faint while Figs 10A-10D demonstrate that phase bars written with scan speeds below 80mm/s were prominent under the RBF and RDIC microscope.
  • the onset of damage was noticed at 20mm/s.
  • An average phase shift of -0.4+0.03 waves is observed at writing wavelength of 517nm, scan speed 40mnv's and average power 507mW.
  • hydrogel refers to an optical, polymeric material that can absorb greater than 10% by weight water based on the total hydrated weight.
  • many optical, hydrogel polymeric materials will be able to absorb a water content greater than 15% or greater than 20%.
  • hydrogel polymeric materials may have a water content from 10% to 80%, or from 15% to 80%, or from 15% to 60%, or from 15% to 40% in their fully hydrated states.
  • the polymeric hydrogel materials should be of sufficient optical clarity, and may have a relatively high refractive index of approximately 1.40 or greater, particularly 1.48 or greater.
  • any ophthalmic materials or material modifications e.g., the inclusion of a photosensitizer, or laser parameters described herein
  • the foregoing disclosed techniques and apparatus can be used to modify the refractive properties, and thus, the dioptric power, of an ophthalmic material comprising primarily silk firoin as described herein, by creating (or machining) a refractive structure with a gradient index in one, two or three dimensions of the optical material, as more fully described in U.S. Publication Nos. 2012/0310340 and 2012/0310223, incorporated by reference herein.
  • the gradient refractive structure can be formed by continuously scanning a continuous stream of femtosecond laser pulses having a controlled focal volume in and along at least one continuous segment (scan line) in the ophthalmic material while varying the scan speed and/or the average laser power, which creates a gradient refractive index in the ophthalmic material along the segment. Accordingly, rather than creating discrete, individual, or even grouped or clustered, adjoining segments of refractive structures with a constant change in the index of refraction in the material, a gradient refractive index may be created within the refractive structure, and thereby in the optical material, by continuously scanning a continuous stream of pulses. As described in greater detail in U.S. Publication No.
  • the amount of two-photon absorption can be adjusted by doping or otherwise including in the irradiated material with selected chromophores that exhibit large two-photon absorption cross-section at the proper wavelength (e.g., between 750 nni and 1100 nm), which can significantly increase the scanning speed as already described.
  • multiple segments can be written into the material in a layer using different scan speeds and/or different average laser power levels for various segments to create a gradient index profile across the layer, i.e., transverse to the scan direction.
  • GRIN refractive structures can be written into the material along the z-direction (i.e., generally the light propagation direction through the material) to provide a desired refractive change in the material that provides a significant added dioptric power or that otherwise corrects for some, most, or all higher order aberrations of a patient’s eye.
  • Such abilities to write continuously varying gradient index layers are particularly advantageous in forming refractive correctors having wavefront cross-section profiles.
  • GRIN refractive structures are low scattering (as discussed above) and are of high optical quality.
  • GRIN refractive structures in the form of Fresnel lens patterns may be LIRIC written in ophthalmic material comprising primarily silk fibroin.
  • the laser may generate light with a wavelength in the range from violet to near-infrared.
  • the wavelength of the laser may be in the range, e.g., from 340 nm to 1500 nm, from 400 nm to 1200 nm, from 400 to 600, or from 650 nm to 1100 nm, including more specifically wavelengths near 400 nm, 517 nm, 800 nm, and 1035 nm.
  • Example pulsewidths include femtosecond scale pulsewidths, and, in some examples, pulsewidths less than 350 fs.
  • Example repetition rates include repetition rates in the range of 1-80 MHz.
  • Example lens NA include NA’s between 0.19 and 1.0.
  • any suitable scanning system may be utilized, including, without limitation, high speed XYZ translation stages, high speed galvanometer scanning systems, and shaker scanners (such as described in U.S. Patent Application Publication No. 2016/0144580 published May 26, 2016 to Wayne H,. Knox et al.).
  • the scanning speed may be in the range of 1 mm/sec to 10 meters/sec or even higher.
  • the laser scanning system may deliver short laser pulses of sufficient energy (e.g. above a minimal threshold but below a damage threshold) and at sufficient scan speeds (e.g. above a damage threshold but below an upper speed threshold) to cause a nonlinear absorption of photons (typically multi-photon absorption), leading to a change in the refractive index of the material at the focus point.
  • the damage threshold may reflect a threshold in which a degradation in optical quality of the device is detectable.
  • the region of the material just outside the focal region is minimally affected by the laser light. Accordingly, select regions of an ophthalmic material comprising primarily silk fibroin material can be modified with a laser resulting in a change in the refractive index in the exposed regions.
  • the irradiated regions may exhibit no significant differences in the Raman spectrum with respect to the non-irradiated regions. Also, the irradiated regions may exhibit little or no scattering loss, which means that the structures fomied in the irradiated regions are not clearly visible under appropriate magnification without contrast enhancement.
  • the described writing systems may be utilized to create lenses or other optical constructs in the interior of the material to change their optical properties. Depending on the phase shift required, the lens or other optical construct can be written into the material in a single layer or in multiple layers.
  • U.S. Patent 8,932,352, issued January 13, 2015 to Wayne H. Knox et al. for an “Optical Material and Method for Modifying the Refractive Index” and U.S. Patent 9,144,491, issued September 29, 2015 to Wayne H. Knox et al. for a “Method for Modifying the Refractive Index of an Optical Material,” describe additional examples of gratings and other optical constructs that may be written into materials.
  • a first step to determining material characteristics for planning desired writing parameters in an ophthalmic material comprising primarily silk fibroin in accordance with the present disclosure may be to measure written phase shifts obtainable in the material of interest as a function of, for example, average power and scan speed.
  • Phase vs. power can be plotted on log-log scales to determine slope of nonlinear processes in small signal regime (below saturation).
  • the determined slope may be indicative of the applicable photochemical model for the material of interest (e.g. a slope close to 2 may be indicative of a two photon model, a slope close to 4 may be indicative of a four photon model, etc.).
  • the applicable photochemical models e.g.
  • the two and/or four photon regime models may be fit to the data, and a maximum phase shift just below the damage threshold may be identified.
  • This information may be subsequently used to establish a range of writing powers at desired scan speeds, to enable controlling a laser power and scan rate for maintaining an energy profile in the ophthalmic material within the focus volume above a nonlinear absorption threshold of the ophthalmic material, and below a material damage breakdown threshold of the ophthalmic material which would result in ablation or observable burning or carbonization of the ophthalmic material. It is noted that, while the best results for at least some systems and methods are obtained when the one-photon absorption is minimized, a small amount of one-photon absorption may be tolerable even in those instances.

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Abstract

Un procédé de formation d'un dispositif optique contenant de la fibroïne de soie ayant un motif d'indice de réfraction modifié selon la présente invention comprend : la fourniture d'un dispositif optique comprenant un matériau ophtalmique constitué principalement de fibroïne de soie ; et la formation d'au moins un motif modifié par laser à l'intérieur du dispositif optique par exposition de régions du matériau ophtalmique à des impulsions lumineuses provenant d'un laser afin de provoquer des changements dans le matériau ophtalmique dans les régions exposées suffisants pour induire un changement d'indice de réfraction des régions exposées par rapport à l'indice de réfraction du matériau ophtalmique dans des régions non exposées. L'exposition au laser peut être effectuée par balayage d'impulsions focalisées à partir du laser le long de régions du matériau ophtalmique. Le matériau ophtalmique peut comprendre un matériau d'hydrogel de fibroïne de soie. Le matériau d'hydrogel de fibroïne de soie peut être obtenu par polymérisation d'un ou de plusieurs monomères hydrophiles et de fibroïne de soie en présence d'un initiateur de copolymérisation.
PCT/US2024/051757 2023-10-20 2024-10-17 Procédé de changement d'indice de réfraction induit par laser et produit ophtalmique traité par ledit procédé Pending WO2025085626A1 (fr)

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