A surgical mesh coated with light-activated adhesive

Abstract

A surgical mesh comprising a photocurable adhesive coating for repairing tissue damage is disclosed After applying the surgical mesh to a patient, the photocurable adhesive is activated under a light source which provides enhanced fixation between the surgical mesh and the damaged tissue. The surgical mesh may be removed and repositioned without substantially losing its adhesive properties and is suitable for treatment of hernia.

Description

A SURGICAL MESH COATED WITH LIGHT- ACTIVATED ADHESIVEFIELD

[0001] The present disclosure generally relates to medical devices for the treatment of tissue disorders, and more particularly to a surgical mesh coated with photocurable adhesive material that may further facilitate positioning and fixation of the implant to the tissue.BACKGROUND

[0002] The abdominal wall in humans is composed of fat and muscles interconnected by fascias. When the abdominal wall becomes damaged, break in continuity occurs in the fascias, allowing part of the peritoneum to slip through and form a sac, or a hernia, containing either fat or part of the intestines. Hernias or incisional hernias (a hernia occurring through a parietal surgical scar), which manifests in the form of a bulge at the surface of the skin imparts pain to the patient and may lead to further complications such as a bowel obstruction leading to more serious injuries including intestine rupture and sepsis. In order to repair or treat the injured area, surgeons may fit a prosthesis in place to prevent additional bulges from forming and initiate skin growth around the weakened anatomical the tissue and close the incision.

[0003] These prothesis are often made of polymeric materials and are provided as a knitted textile or a mesh structure. Knitting methods allow obtaining a knitted structure having open-worked faces or pores that promote issue ingrowth after implantation while maintaining structural integrity of the prosthesis. Once implanted, the mesh must be positioned in the desired location and fixed to the surrounding biological tissues, such as for example the abdominal wall. Many fixing means are available for fixing the mesh to the abdominal wall, such as tacks, staples or sutures. However, these modes of fixation may introduce the potential for human error, may not be repositioned, and may require additional procedures to remove the fixing means post operation.

[0004] Accordingly, there is a continuous need for devices and methods to provide an adhesive surgical mesh on the damaged tissue areas that are less difficult to implement, repositionable in tight tissue space, most preferably without substantially losing adhesive properties, provide enhanced adhesion to the tissue, promote tissue ingrowth, and arepreferably bioabsorbable / biocompatible such that post-operational procedures to remove the adhesive / connective means are not required. Therefore, there exists a need to provide a solution in which a surgical mesh is coupled with a biologically compatible adhesive that can positioned (or repositioned) in the desired place.SUMMARY

[0005] In one aspect, the disclosed technology relates to a surgical mesh comprising: a reinforcement part; and a photocurable adhesive deposited on surface of the reinforcement part; wherein the photocurable adhesive is configured to bond to tissue when exposed to an optical energy source while the surgical mesh is in contact with the tissue. In some embodiments, the reinforcement part comprises biocompatible material, bioabsorbable materials, non-bioabsorbable materials, or combinations thereof. In some embodiments, the photocurable adhesive comprises: about 0.2 %w / w to about 20 %w / w photopolymer, based on the total weight of the photocurable adhesive; about 0.005 %w / w to about 1.0% w / w photo initiator, based on the total weight of the photocurable adhesive. In some embodiments, the surgical mesh further comprises about 0.01 %w / w to about 5.0 %w / w co-initiator, based on the total weight of the photocurable adhesive.

[0006] In some embodiments, the photopolymer is selected from the group consisting of pepsin soluble collagen, denatured collagen, collagen acrylamide, gelatin tyramine, gelatin methacrylamide, sodium hyaluronate tyramine, and combinations thereof. In some embodiments, the photo initiator is selected from the group consisting of Tris(2,2'-bipyridyl)dichlororuthenium(II) hexahydrate (Ru(BPY)3), Riboflavin, Eosin Y, Rose Bengal, and combinations thereof. In some embodiments, the co-initiator is selected from the group consisting of sodium persulfate, ammonium persulfate and combinations thereof.

[0007] In some embodiments, the photocurable adhesive is a powder coating, a film coating, a foam coating, or combinations thereof. In some embodiments, the photocurable adhesive is deposited on a top surface, a bottom surface, or both the top surface and the bottom surface of the reinforcement part. In some embodiments, wherein the optical energy source comprises a light having a wavelength from 240 nm to 780 nm. In some embodiments, the photocurable adhesive comprises: about 1.0 %w / w to about 3.0 %w / w denatured collagen, based on the total weight of the photocurable adhesive; about 0.5%w / w to about 1.5 %w / w pepsin soluble collagen, based on the total weight of the photocurable adhesive; about 0.005 %w / w to about 0.025 %w / w of Ru(BPY)3, based on the total weight of the photocurable adhesive; and about 0.025 %w / w to about 0.5 %w / w of sodium persulfate, based on the total weight of the photocurable adhesive.

[0008] In another aspect, the disclosed technology relates to a method of producing a photocurable adhesive, the method comprising: (a) solubilizing a photopolymer in an aqueous solution to produce a photopolymer solution having a concentration of about 0.2 %w / w to about 20.0 %w / w photopolymer, based on the total weight of the photocurable adhesive; (b) adding a photo initiator to the photopolymer solution to produce a photopolymer-photo initiator solution having concentration of about 0.005 %w / w to about 1.0 %w / w a photo initiator, based on the total weight of the photocurable adhesive; and (c) homogenizing the combined solution. In some embodiments, the method further comprises further comprising after step (b) and before step (c), adding a co-initiator to the photopolymer-photo initiator solution to produce a combined solution having concentration of about 0.01 %w / w to about 5 %w / w a co-initiator, based on the total weight of the photocurable adhesive.

[0009] In some embodiments, step (a) is carried out at a temperature range from about 20 °C to about 50 °C for about 30 minutes to 24 hours. In some embodiments, step (b) is carried out at a temperature range from about 20 °C to about 50 °C for about 5 minutes to about 30 minutes. In some embodiments, adding a co-initiator is carried out at a temperature range from about 20 °C to about 50 °C for about 5 minutes to about 30 minutes. In some embodiments, after step (a) and before step (b), the photopolymer is a first photopolymer, and further comprising adding a second photopolymer, wherein the second photopolymer is present at a concentration about 0.2 %w / w to about 20% w / w, based on the total weight of the photocurable adhesive. In some embodiments, further comprising after step (c): aerating the combined solution from about 1 minute to about 30 minutes to produce a wet foam; depositing the wet foam on a reinforcement part of a surgical mesh; and air drying the wet foam to produce a dry foam coating.

[0010] In another aspect, the disclosed technology relates to a method of producing a photocurable adhesive foam, the method comprising: (a) solubilizing pepsin soluble collagen in an aqueous solution to produce a pepsin soluble collagen solution having a concentration of about 1.0 %w / w to about 3.0 %w / w, based on the total weight of thepepsin soluble collagen solution; (b) denaturing collagen in an aqueous solution to produce a denatured collagen solution having a concentration about 2.0 %w / w to about 6.0 %w / w denatured collagen, based on the total weight of the denatured collagen solution; (c) mixing the pepsin soluble collagen solution with the denatured collagen solution to produce a combined collagen solution comprising about 0.5 %w / w to about 1.5 %w / w pepsin soluble collagen, based on the total weight of the photocurable adhesive foam and about 1.0 %w / w to about 3.0 %w / w denatured collagen, based on the total weight of the photocurable adhesive foam; (d) adding a photo initiator and a co-initiator to the combined collagen solution to produce a photocurable collagen solution; (e) homogenizing the photocurable collagen solution; (f) aerating the photocurable collagen solution from about 2 minutes to about 5 minutes to produce a wet photocurable adhesive foam; and depositing the wet photocurable adhesive foam on a reinforcement.

[0011] In some embodiments, step (d) comprises adding about 0.005 %w / w to about 0.025 %w / w of RU(BPY)3, based on the total weight of the photocurable adhesive; and about 0.025 %w / w to about 0.125 %w / w of sodium persulfate, based on the total weight of the photocurable adhesive. In some embodiments, after step (g), air drying the wet photocurable adhesive foam to produce a dry photocurable adhesive foam.

[0012] In another aspect, the disclosed technology relates to a method of treating a patient using a surgical mesh, the method comprising: (a) applying the surgical mesh of any one of claims 1-11 to a damaged tissue area to provide a contact induced adhesion between the damaged tissue area and the surgical mesh; (b) illuminating the surgical mesh with a light source to activate the photocurable adhesive and to provide a light-induced adhesion between the damaged tissue area and the photocurable adhesive; and (c) allowing the photocurable adhesive to be metabolized by the damaged tissue area; and allowing tissue ingrowth through pores of the reinforcement part of the surgical mesh wherein step (a) comprises removing and repositioning the surgical mesh without substantial reduction in adhesive strength between the damaged tissue area and the surgical mesh.

[0013] The details of one or more aspects of the disclosure are set forth in the accompanying drawings and the description below. Other features, objects, and advantages of the techniques described in this disclosure will be apparent from the description and drawings, and from the claims.BRIEF DESCRIPTION OF DRAWINGS

[0014] FIG. 1 depicts a perspective view of a first embodiment of a surgical mesh with photocurable adhesive coating.

[0015] FIG. 2 depicts a perspective view of another embodiment of a surgical mesh with photocurable adhesive coating deployed on surface of a tissue.

[0016] FIG. 3 depicts a perspective view of another embodiment of a surgical mesh with activated adhesive coating deployed on surface of a tissue.

[0017] FIG. 4 depicts a perspective view of another embodiment of a surgical mesh showing tissue in-growth through the surgical mesh.

[0018] FIG. 5 depicts a flow chart outlining a synthesis of photocurable adhesive coating of the present disclosure.

[0019] FIG. 6 depicts a perspective view of another embodiment of a surgical mesh with photocurable foam coated on the surface of the mesh.

[0020] FIG. 7 depicts a graph representing adhesion strength of the surgical mesh of the present disclosure.DETAILED DESCRIPTION

[0021] Embodiments of the present disclosure relate generally, for example, to systems for treating tissue disorders, and more particularly, to surgical mesh used to treat or alleviate tissue damage. Embodiments of the devices and methods are described below and with reference to the Figures.

[0022] The following discussion omits or only briefly describes certain components, features and functionality related to medical implants, installation tools, and associated surgical techniques, which are apparent to those of ordinary skill in the art. It is noted that various embodiments are described in detail with reference to the drawings, in which like reference numerals represent like parts and assemblies throughout the several views, where possible. Reference to various embodiments does not limit the scope of the claims appended hereto because the embodiments are examples of the inventive concepts described herein. Additionally, any example(s) set forth in this specification are intended to be non-limiting and set forth some of the many possible embodiments applicable to the appended claims. Further, particular features described herein can be used in combinationwith other described features in each of the various possible combinations and permutations unless the context or other statements clearly indicate otherwise.

[0023] Terms such as “same,” “equal,” “planar,” “coplanar,” “parallel,” “perpendicular,” etc. as used herein are intended to encompass a meaning of exactly the same while also including variations that may occur, for example, due to manufacturing processes and tolerances. The term “substantially” may be used herein to emphasize this meaning, particularly when the described embodiment has the same or nearly the same functionality or characteristic, unless the context or other statements clearly indicate otherwise. Additionally, it shall be understood that the term “about” encompasses a variation of at least + / - 10% from the example values provided herein.

[0024] The following discussion includes a description of a reinforcement part coated with photoactive / photocurable adhesive coating for improved adhesion to damaged tissue area, methods of producing a surgical mesh, and related methods of utilizing the surgical mesh to treat tissue-related disorders in accordance with the principles of the present disclosure. Alternate embodiments are also disclosed. Reference is made in detail to the exemplary embodiments of the present disclosure, which are illustrated in the accompanying figures. FIGS. 1-7, illustrate various components of a surgical mesh, such as, for example, a surgical mesh 100, 200, 300, 400, or 600 having pores 103, 203, 303, 403, or 603, and photocurable adhesive coating 105, 205, 305, 405, or 605.

[0025] Various embodiments and components of the surgical mesh of the present disclosure may be fabricated from any biocompatible material, including non-bioabsorbable materials, biodegradable and / or bioabsorbable materials and combinations thereof.

[0026] As used herein the term “bioabsorbable” or “biodegradable” is understood to mean that the materials having this property can, for example, decompose or lose structural integrity under body conditions (e.g. enzymatic degradation or hydrolysis) or can be broken down (physically or chemically) under physiologic conditions in the body such that the degradation products are excretable or absorbable by the body. after a certain time, which may vary, for example, from a few hours to a few years, depending on the chemical nature of the materials. In this disclosure, the term “bioabsorbable” or “biodegradable may be used interchangeably.

[0027] Referring generally to FIGS. 1-4, a surgical mesh comprising a reinforcement part and photocurable adhesive according to the present disclosure is shown. FIG. 5 depicts a flow-chart illustrating a method to produce a surgical mesh comprising the photocurable adhesive according to the present disclosure. FIG. 6 illustrates an embodiment of a surgical mesh comprising the photocurable foam adhesive according to the present disclosure. FIG. 7 illustrates adhesive properties of a surgical mesh comprising the photocurable adhesive according to the present disclosure.

[0028] In FIG. 1, a surgical mesh assembly according to an embodiment of the present disclosure, is disclosed. A surgical mesh 100 may comprise a reinforcement part 101 designed with a network of yarns or filaments and pores 103. The reinforcement part may be formed using any suitable method known to those of ordinary skill including, but not limited to, weaving, knitting, braiding, crocheting, embroidering, and the like.

[0029] In some embodiments, the implantable mesh includes a knit mesh body. In some embodiments, the implantable knit mesh may be knitted on a warp knitting machine, of the tricot or Raschel type, with at least two or three guide bars. In some embodiments, the implantable mesh is illustrated and described, for example, in any of the U.S. Patent Nos. 6,596,002 to Therin et al.; 7,331,199 to Ory et al.; 9,750,595 to Thomas et al.;9,186,235 to Ory et al.; and 9,510,927 to Simons, the entire contents of which are incorporated herein by reference.

[0030] In some embodiments, the implantable mesh includes a two-dimensional mesh body. For example, the mesh body may include one or more filaments intertwined in a generally planar or horizontal crisscrossing pattern, i.e., weft / warp pattern, forming a mesh body including a single layer of intertwined filament(s).

[0031] In some embodiments, the implantable mesh includes a three-dimensional mesh body. For example, the mesh body may include one or more filaments intertwined in both a horizontal and vertical pattern forming a mesh body including two or more layers of intertwined filament(s) often connected to each other by a spacer filament, i.e., a filament that extends between and connects the two or more layers, defining a space or depth between the two or more layers.

[0032] In some embodiments, the surgical mesh, and particularly the filaments or yams that form the mesh that make up the reinforcement part, may be made from anybiocompatible material, including bioabsorbable materials, non-bioabsorbable materials, and combinations thereof.

[0033] Representative natural bioabsorbable materials may include, but are not limited to: polysaccharides, such as alginate, dextran, chitin, hyaluronic acid, cellulose, fucans, glycosaminoglycans, and chemical derivatives thereof (substitutions and / or additions of chemical groups, for example, alkyl, alkylene, hydroxylations, oxidations, and other modifications routinely made by those skilled in the art); and proteins, such as collagen, gelatin, albumin, casein, zein, silk, and copolymers and blends thereof, alone or in combination with synthetic polymers.

[0034] Synthetically modified natural polymers may include, but are not limited to, cellulose derivatives, such as alkyl celluloses, hydroxyalkyl celluloses, cellulose ethers, cellulose esters, nitrocelluloses, and chitosan. Examples of suitable cellulose derivatives include methyl cellulose, ethyl cellulose, hydroxypropyl cellulose, hydroxypropyl methyl cellulose, hydroxybutyl methyl cellulose, cellulose acetate, cellulose propionate, cellulose acetate butyrate, cellulose acetate phthalate, carboxymethyl cellulose, cellulose triacetate, and cellulose sulfate sodium salt.

[0035] Representative synthetic bioabsorbable polymers may include, but are not limited to, polyhydroxy acids prepared from lactone monomers, such as glycolide, lactide, caprolactone, s-caprolactone, valerolactone, and 5 -valerolactone, as well as pluronics, carbonates (e.g., trimethylene carbonate, tetramethylene carbonate, and the like), dioxanones (e.g., 1,4-dioxanone and p-dioxanone), l,dioxepanones (e.g., l,4-dioxepan-2-one and l,5-dioxepan-2-one), and combinations thereof. Polymers formed therefrom include: polylactides; poly(lactic acid); polyglycolides; poly(glycolic acid); poly(trimethylene carbonate); poly(dioxanone); poly(hydroxybutyric acid); poly(hydroxyvaleric acid); poly(lactide-co-(s-caprolactone-)); poly(glycolide-co-(s-caprolactone)); polycarbonates; poly(pseudo amino acids); poly(amino acids); poly(hydroxyalkanoate)s; polyalkylene oxalates; polyoxaesters; polyanhydrides; polyortho esters; and copolymers, block copolymers, homopolymers, blends, and combinations thereof.

[0036] Some non-limiting examples of suitable non-bioabsorbable materials include polyolefins, such as polyethylene and polypropylene including atactic, isotactic, syndiotactic, and blends thereof; polyethylene glycols; polyethylene oxides; ultra-highmolecular weight polyethylene; copolymers of polyethylene and polypropylene; polyisobutylene and ethylene-alpha olefin copolymers; fluorinated polyolefins, such as fluoroethylenes, including expanded polytetrafluoroethylene (ePTFE) and condensed polytetrafluoroethylene c(PTFE), fluoropropylenes, fluoroPEGSs, and polytetrafluoroethylene; polyamides, such as nylon and polycaprolactam; polyamines; polyimines; polyesters, such as polyethylene terephthalate and polybutylene terephthalate; aliphatic polyesters; polyethers; polyether-esters, such as polybutester; polytetramethylene ether glycol; 1,4-butanediol; polyurethanes; acrylic polymers and copolymers; modacrylics; vinyl halide polymers and copolymers, such as polyvinyl chloride; polyvinyl alcohols; polyvinyl ethers, such as polyvinyl methyl ether; polyvinylidene halides, such as polyvinylidene fluoride and polyvinylidene chloride; polyacrylonitrile;poly aryl etherketones; polyvinyl ketones; polyvinyl aromatics, such as polystyrene; polyvinyl esters, such as polyvinyl acetate; copolymers of vinyl monomers with each other and olefins, such as ethylene-methyl methacrylate copolymers, acrylonitrile-styrene copolymers, ABS resins, and ethylene-vinyl acetate copolymers; alkyd resins; polycarbonates; polyoxymethylene; polyphosphazene; polyimides; epoxy resins; aramids, rayon; rayon-triacetate; spandex; silicones; and combinations thereof.

[0037] As used herein a “mesh” is understood as an arrangement of biocompatible yams, such as a textile or fabric, preferably open-worked, provided with pores that favor colonization of tissue such as cellular growth. Such a mesh can be bioabsorbable / biodegradable, permanent or partially bioabsorbable / biodegradable. It is sufficiently flexible to be folded up at the time of introduction into the abdominal cavity. Meshes for forming hernia prosthesis are well known to a person skilled in the art. The mesh can be supplied in any shape whatsoever, for example rectangular, square, circular, oval, etc., and can then be cut to suit the shape of the hernia defect. For example, the overall shape of the mesh can be circular or oval. Alternatively, the mesh can have a generally square shape, a rectangular shape, diamond shape, or other polygonal shapes.

[0038] In some embodiments, the surgical mesh may comprise a plurality of pores comprising mesh structure. In some embodiments, pores 103 of surgical mesh 100 may have an average size between about 0.1 mm and about 5 mm, about 0.2 mm to about 4.5 mm, about 0.3 mm to about 4.0 mm, about 0.4 mm to about 3.5 mm, about 0.5 mm to about 3.0 mm, about 0.5 mm to about 5 mm, about 1.0 mm to about 4.5 mm, about 1.5mm to about 4.0 mm, about 2 mm to about 3.5 mm, about 2.5 mm to about 3 mm, about 0.1 mm to about 0.5 mm, about 0.5 mm to about 1 mm, about 1 mm to about 1.5 mm, about 1.5 mm to about 2 mm, about 2 mm to about 2.5 mm, about 2.5 mm to about 3.0 mm, about 3.5 mm to about 4.0 mm, about 4.5 mm to about 5.0 mm, or between any two of aforementioned values.

[0039] In some embodiments, the outer surface of surgical mesh 100 may be coated with biocompatible and bioabsorbable / biodegradable photocurable adhesive coating 105 (better seen in figure inset) that may coat or cover only filament and / or yarn portion of reinforcement part 101 of the surgical mesh structure, fill in the gaps, i.e., “pores 103” of the mesh structure, or both. In some embodiments, the adhesive coating may be photocurable adhesive. The term “photocurable adhesive” refers, for example, to a mixture that hardens or cures after photo-activation. Photoactivation is a process by which energy in the form of electromagnetic radiation is absorbed by a compound generally referred as photo initiator, photosensitizer or chromophore which becomes “excited1and then converts the energy to another form of energy, preferably chemical energy. The chemical energy can be in the form of reactive oxygen species like singlet oxygen, superoxide anion, hydroxyl radical, the excited state of the photo-activated molecule, photo-activated free radical or substrate free radical species. The electromagnetic radiation will include “optical energy”, i.e., can have a wavelength in the visible range or portion of the electromagnetic spectrum, and can also include the ultraviolet and infrared regions of the spectrum. The reactive species will initiate a chemical reaction between specific functional groups of a compound generally referred as photopolymer leading to a cross-linking of polymer chains.

[0040] In some embodiments, when exposed to a light energy source, photocurable adhesive coating 105 may further bond to tissue while the surgical mesh is in contact with the wet tissue. In some embodiments, bottom surface 110, top surface 120, or both surfaces of surgical mesh 100 may be coated with, photocurable adhesive coating 105.

[0041] In some embodiments, the photocurable adhesive coating 105 may comprise a photopolymer component, a photo initiator component, and optionally, a co-initiator. In some embodiments, the photopolymer component is a water-soluble polymer having reactive functional groups for photo-curing. The term “reactive functional group” refers to any chemical group able to react in presence of reactive species generated after theexcitation of the photo initiator with an electromagnetic radiation. Some suitable nonlimiting examples of reactive functional groups includes acrylates, acrylamides, methacrylates, methacrylamides, thiols, vinyl ethers, vinyl ether, alkene, arenes, cycloalkene, and combinations thereof.

[0042] These reactive functional groups may be added to the structure of the polymer directly during the synthesis of the polymer or / and added later, i.e., after the polymerization, with a modification of the structure of the polymer. Some suitable nonlimiting examples of polymer includes polysaccharides, such as alginate salts, dextran, chitosan, hyaluronate salts, chondroitin salts, carrageenan, pectin, maltodextrin, starch, gellan gum, xanthan gum, cellulose, fucans, glycosaminoglycans, and chemical derivatives thereof (substitutions and / or additions of chemical groups, for example, alkyl, alkylene, hydroxylations, oxidations, and other modifications routinely made by those skilled in the art); proteins, such as collagen, gelatin, elastin, albumin, casein, zein, silk, and chemical derivatives thereof (substitutions and / or additions of chemical groups, for example, alkyl, alkylene, hydroxylations, oxidations, and other modifications routinely made by those skilled in the art); synthetic polymers such as polyethylene glycols, polyvinyl alcohols, polyurethanes and chemical derivatives thereof (substitutions and / or additions of chemical groups, for example, alkyl, alkylene, hydroxylations, oxidations, and other modifications routinely made by those skilled in the art) and combination thereof. In some embodiments, the photo initiator may comprise chemicals that comprise good water solubility and high absorption coefficient in light spectrum to produce reactive species allowing for cross-linking of the photopolymer component. The photo initiator can be a type I or a type II. The term “type I” refers as molecules typically break down into two or more reactive smaller fragments upon exposure to light energy source. Some suitable nonlimiting examples of water soluble type I photo initiators includes a-hydroxyketones and their derivatives such as Irgacure 2959 (2-hydroxy-l-(4-(hydroxyethoxy)-phenyl)-2-m ethyl- 1 -propanone), Irgacure 184 (1-hydroxy-cyclohexyl-phenylketone), Irgacure 369 (2-Benzyl-2-dimethylamino-l-(4-morpholinophenyl)-l-butanone), Irgacure 651 (2,2-dimethoxy-2-phenylacetophenone), Irgacure 907 (2-Methyl-40-(methylthio)-2-morpholinopropiophenone), MBS (sodium 4-[2-(4-morpholino)benzoyl-2-dimethylamino] butylbenzenesulphone); Phosphine Derivatives such as TPO (diphenyl (2,4,6-trimethylbenzoyl)phosphine oxide), LAP (ithiumphenyl-2,4,6-trimethylbenzoylphosphinate); Azo-Initiators such as VA-086, DAS (tetrapotassium4,40-(l,2-ethenediyl)bis(2-(3-sulfo-phenyl)diazenesulfonate)). The term “type II” refers as photo initiators which can generate reactive species without cleaving into smaller molecules. Unlike type I photo initiators, a type II photo initiator requires a co-initiator, generally an electron donor or acceptor or a hydrogen donor in order to produce the appropriate reactive species. Some suitable non-limiting examples of water soluble type I photo initiators include (tris-bipyridyl-ruthenium(II)hexahydrate (Ru(BPY)3 Eosin-Y, Rose Bengal, Riboflavin, Camphorquinone and its derivatives, P2CK (sodium 3,30-(((lE,lE0)-(2-oxocyclopentane-l,3-diylidene)bis(methanylydiebe))bis(4,l-phenylene))bis(methylazanediyl))dipropanoate). Some suitable non-limiting examples of water soluble co-initiators includes, sodium persulfate, ammonium persulfate, triethanolamine, ethylamine, L-arginine, triethylenamine, disodium ethylenediaminetetraacetate dihydrate and ethyl-4-N,N-dimethylaminobenzoate.

[0043] In some embodiments, the photocurable adhesive may comprise one or more photopolymer component, each in a concentration from about 0.2 % w / w to about 20 % w / w, about 0.4% w / w to about 10% w / w, about 0.6% w / w to about 5.0% w / w, about 0.8% w / w to about 3.0% w / w, about 1.0% w / w to about 2.0% w / w, or between any two of aforementioned values, based on total weight of the photocurable adhesive solution. In some embodiments, a first photopolymer may be pepsin soluble collagen present in an amount about 0.5 % w / w to about 1.5 % w / w and a second photopolymer may be denatured collagen present in an amount about 1.0 w / w to about 3.0 % w / w, each based on total weight of the photocurable adhesive. In some embodiments, denatured polymers may be produced by solubilizing undenatured collagen in solution and heating the solution to about 45 °C for about 30 minutes and cooling the solution to about 30 °C to produce a denatured collagen solution.

[0044] In some embodiments, the photocurable adhesive may comprise a photo initiator component in a concentration from about 0.005% w / w to about 1.0% w / w, about 0.01 % w / w to about 0.50% w / w, about 0.015% w / w to about 0.25 % w / w, about 0.02 % w / w to about 0.10 % w / w, about 0.025 % w / w, about 0.05 % w / w, or between any two of aforementioned values, based on total weight of the photocurable adhesive. In some embodiments, photo initiator may be Ru(BPY)s present in an amount about 0.005 % w / w to about 0.025 % w / w, based on total weight of the photocurable adhesive.

[0045] In some embodiments, the photocurable adhesive may optionally comprise a co-initiator component in a concentration from 0.01 %w / w to about 5.0 %w / w, about 0.02 %w / w to about 2.0 %w / w, about 0.04 %w / w to about 1.0 %w / w, about 0.05 %w / w to about 0.5% w / w, or between any two of aforementioned values, based on total weight of the photocurable adhesive. In some embodiments, co-initiator may be sodium persulfate present in an amount about 0.025 %w / w to about 0.5 %w / w, based on total weight of the photocurable adhesive.

[0046] In some embodiments, the photocurable adhesive may be a powder coating, a film coating, a foam coating, or combinations thereof. In some embodiments, the photocurable adhesive may exhibit their adhesive properties prior to activation by exposure to light, but for example to a lesser degree than upon activation by exposure to an appropriate energy or light source. In some embodiments, the photocurable adhesive of the present disclosure may exhibit adhesive properties prior to, and then to a greater degree when exposed to light source having a wavelength from about 240 nm to about 780 nm. In some embodiments, the appropriate light energy may be provided by a single or monochromatic laser source comprising a single wavelength light, or a broadband light source comprising a range of wavelengths, for example, within ultra-violet range (i.e., about 100 nm to about 380 nm, visible range (i.e., about 380 nm to about 780 nm), or combinations thereof. In some embodiments, the light source may be from a conventional endoscope light source typically used in tissue repair procedures.

[0047] Now referring to FIG. 2, another embodiment of surgical mesh 200 positioned on a patient’s tissue 250 is disclosed herein. Surgical mesh 200 may have the same, similar, and / or substantially the same features and functionality, as well as be partated using the similar and / or substantially the same method as explained above with respect to surgical mesh 100. It should be understood that parts with similar numbering, i.e., 201 and 101, describe the same or substantially the same features. For example, surgical mesh 200 may comprise a biocompatible reinforcement part 201, pores 203, and photocurable adhesive coating 205.

[0048] As illustrated in FIG. 2, surgical mesh 200 may be positioned on damaged area of tissue 250. In some embodiments, when surgical mesh 200 is positioned and pressed on wet surface of tissue 250, the hydration of the photocurable adhesive coating 205 (better seen in figure inset) with the body fluids, i.e., (blood, blood plasma, interstitial fluids,lymphatic fluids) generates an immediate adhesion as a pressure-sensitive adhesive or self-adhesive. In some embodiments, the terms “pressure sensitive adhesive” and “self-adhesive" refer to a nonreactive adhesive designed to be tacky by forming non-permanent bonds with an adherend such as van der Waals force, or hydrogen bonds for example.

[0049] In some embodiments other fluids, such as saline, may be introduced to facilitate wet adhesion. In some embodiments, the compression pressure to achieve the self-adhesion of the surgical mesh on the tissue may be from about 0.05 bar to about 0.50 bar held at a duration of about 1 seconds to about 10 seconds.

[0050] In some embodiments, this self-adhesion may have a duration from about 1 minute to about 30 minutes, about 2 minutes to about 20 minutes, about 3 minutes to about 15 minutes, about 3 minutes to about 10 minutes, or about 3 minutes to about 5 minutes. In some embodiments, during this duration, surgical mesh 200 may be removed and repositioned to another area of the tissue while maintaining adhesive strength / properties of surgical mesh 200.

[0051] Now referring to FIG. 3, another embodiment of surgical mesh 300 positioned on a patient’s tissue 350 is disclosed herein. Surgical mesh 300 may have the same, similar, and / or substantially the same features and functionality, as well as be fabricated using the similar and / or substantially the same method as explained above with respect to surgical mesh 100 or 200. It should be understood that parts with similar numbering, i.e., 301, 201, and 101, describe the same or substantially the same features. For example, surgical mesh 300 may comprise a biocompatible reinforcement part 301, pores 303, and photocurable adhesive coating 305.

[0052] As illustrated in FIG. 3, once positioned (or repositioned) into a desired location, surgical mesh 300 may be exposed to a light energy 365 from light source 360 such as an endoscopy light. As mentioned above, when exposed to an appropriate energy or light source, photo initiator present in photocurable adhesive coating 305 (better seen in figure inset) may undergo chemical reaction to produce reactive species. These reactive species may trigger a chemical reaction to form covalent bonds between functional groups of the photopolymer component in the photocurable coating to activate initial or enhanced adhesive properties thereby permanently bonding tissue 350 with surgical mesh 300 and curing it in place. In some embodiments, the adhesion provided by surgical mesh 300 may be provide at least 100%, at least 90%, at least 80%, at least 70%, at least 60%, or at least50% improvement in the adhesion strength between tissue 350 and surgical mesh 300 compared to a surgical mesh without a photoactivated coating. In some embodiments, the photoactivation and adhesion of surgical mesh 300 to tissue 350 may be achieved in less than about 15 seconds, less than about 10 seconds, or less than about 5 seconds upon exposure to a light source. In some embodiments, un-activated or uncured coating will be eliminated from the body by absorption into surrounding tissue area, without any negative effects on the tissue growth.

[0053] Now referring to FIG. 4, another embodiment of surgical mesh 400 positioned on a patient’s tissue 450 is disclosed herein. Surgical mesh 400 may have the same, similar, and / or substantially the same features and functionality, as well as be fabricated using the similar and / or substantially the same method as explained above with respect to surgical mesh 100, 200, or 300. It should be understood that parts with similar numbering, describe the same or substantially the same features.

[0054] As illustrated in FIG. 4, after bonding surgical mesh 400 to tissue 450 by photoactivation (as illustrated in FIG. 3), photocured adhesive coating is metabolized by enzymes in the body through natural healing process. In some embodiments, surgical mesh 400 may provide adequate and suitable adhesion to the damaged tissue 450 without hindering tissue ingrowth. In some embodiments, tissue may be grown around the outer edges of surgical mesh 400 and through mesh pores 403 as seen by tissue growth 455. In some embodiments, the activated or cured photocurable adhesive coating 405 (better seen in figure inset) may be eliminated from the body as tissue ingrowth progresses within about several weeks.

[0055] Now referring to FIG. 5, a flow chart illustrating an exemplary process 500 for preparing photocurable adhesive is shown. Process 500 begins with block 501, where one or more photopolymer is solubilized in an aqueous solution such as water, saline, or a buffer solution for example. In some embodiments, the photopolymer may be selected from the group consisting of pepsin soluble collagen, denatured collagen, collagen acrylamide, gelatin tyramine, gelatin methacrylamide, sodium hyaluronate tyramine, and combinations thereof. In some embodiments, the solubilized first photopolymer may be present in an amount from about 0.2 % w / w to about 20 % w / w, about 0.4% w / w to about 10% w / w, about 0.6% w / w to about 5.0% w / w, about 0.8% w / w to about 3.0% w / w, about 1.0% w / w to about 2.0% w / w, or between any two of aforementioned values, based ontotal weight of the photocurable adhesive. In some embodiments, photopolymer may be solubilized at a temperature of about 20 °C to about 50 °C, for about 30 minutes to about 24 hours, about 1 hours to about 22 hours, about 2 hours to about 20 hours, about 4 hours to about 18 hours, about 6 hours to about 16 hours, about 8 hours to about 14 hours, about 10 hours to about 12 hours, at least about 30 minutes, at least about 1 hour, at least about 2 hours, at least about 4 hours, at least about 6 hours, at least about 8 hours, at least about 10 hours, at least about 12 hours, at least about 14 hours, at least about 16 hours, at least about 18 hours, at least about 20 hours, at least about 22 hours, or between any two of aforementioned values.

[0056] The process continues to an optional step 502, where a second photopolymer may be added and solubilized under the same, or substantially the same conditions (solubility temperature and time) as the first photopolymer condition disclosed above. In some embodiments, second photopolymer may be selected from the group consisting of consisting of pepsin soluble collagen, denatured collagen, collagen acrylamide, gelatin tyramine, gelatin methacrylamide, sodium hyaluronate tyramine, and combinations thereof. In some embodiments, the solubilized second photopolymer may be present in an amount from about from about 0.2 % w / w to about 20 % w / w, about 0.4% w / w to about 10% w / w, about 0.6% w / w to about 5.0% w / w, about 0.8% w / w to about 3.0% w / w, about 1.0% w / w to about 2.0% w / w, or between any two of aforementioned values, based on total weight of the photocurable adhesive.

[0057] The process proceeds to block 503 where a photo initiator is added to the polymer(s) solution to produce a polymer-photo initiator solution mixture. In some embodiments, photo initiator may be selected from the group consisting of Tris(2,2'-bipyridyl)dichlororuthenium(II) hexahydrate (Ru(BPY)3), Riboflavin, Eosin Y, Rose Bengal, and combinations thereof. In some embodiments, the photocurable adhesive may comprise a photo initiator component in a concentration from about 0.005% w / w to about 1.0 % w / w, about 0.01 % w / w to about 0.50% w / w, about 0.015% w / w to about 0.25 % w / w, about 0.02 % w / w to about 0.10 % w / w, about 0.025 % w / w, about 0.05 % w / w, or between any two of aforementioned values, based on total weight of the photocurable adhesive. In some embodiments, photo initiator may be solubilized at a temperature of about 20 °C to about 50 °C, for about 5 minutes to about 30 minutes, about 10 minutes toabout 25 minutes, about 15 minutes to about 20 minutes, at least about 5 minutes, at least about 10 minutes, at least about 15 minutes, at least about 20 minutes, at least about 25 minutes, or between any two of aforementioned values.

[0058] The process continues to an optional step 504 where a co-initiator may be added to the photopolymer-photo initiator solution and solubilized to produce a combined solution. In some embodiments, co-initiator may be selected from the group consisting of consisting of sodium persulfate, ammonium persulfate and combinations thereof. In some embodiments, the co-initiator may be present in an amount from about 0.01 %w / w to about 5.0% w / w, about 0.02% w / w to about 2.0% w / w, about 0.04% w / w to about 1.0% w / w, about 0.05% w / w to about 0.5% w / w, or between any two of aforementioned values, based on total weight of the photocurable adhesive. In some embodiments, co-initiator may be added to the photopolymer-photo initiator solution at a temperature of about 20 °C to about 50 °C, for about 5 minutes to about 30 minutes, about 10 minutes to about 25 minutes, about 15 minutes to about 20 minutes, at least about 5 minutes, at least about 10 minutes, at least about 15 minutes, at least about 20 minutes, at least about 25 minutes or between any two of aforementioned values.

[0059] After solubilizing curing polymer(s) and photo initiator(s), process proceeds to step 505 where the solution mixture is homogenized at temperature range from about 20 °C to about 50 °C. The homogenized solution may be prepared into a liquid / gel based photocurable coating or a wet foam. As seen in block 506, to prepare the wet photocurable foam, the homogenized solution is foamed using technique such as mechanical foaming. The term “mechanical foaming” refers to a process used to form a foam by aerating, or physically agitating a liquid, typically with the help of mechanical devices like mixers or blenders. This method introduces air or another gas into the liquid (i.e., aeration), forming bubbles that are stabilized by the liquid's surface tension and viscosity.

[0060] In some embodiments, the foam may be produced by mixing the homogenized solution for about 1 minute to about 30 minutes, about 2 minutes to about 20 minutes, about 3 minutes to about 10 minutes, about 4 minutes to about 8 minutes, or between any two of aforementioned values. In some embodiments, the wet foam obtained may have a density ranging from about 0.05 g.cm'3to about 0.50 g.cm'3; about 0.10 g.cm'3to about 0.40 g.cm'3; about 0.20 g.cm'3to about 0.30 g.cm'3, or between any two of aforementioned values.

[0061] In block 507, the wet foam is applied directly to the reinforcement part of the surgical mesh. The wet foam can be applied directly to the reinforcement part in any variety of patterns including but not limited to, a complete coverage, stripes, polygons, circles, ovals, rings, dots, dashes, arrows, numbers, letters, tear drops, etc. The wet foam material can be directly applied to the reinforcement part using any suitable utensil, including but not limited to a syringe, spoon, fork, ladle, scoop, straw, brush, roller, and / or piping bag. Once applied, the pattern is maintained through the drying process to produce a dry foam of a same or similar pattern.

[0062] In block 508, following the casting of the wet foam may be dried into a dry foam by heating the combined wet foam and reinforcement part in an oven, such as a forced air oven. In some embodiments, the combined wet foam and reinforcement part may be heated at about 20 °C to about 100 °C, about 25 °C to about 80 °C, about 30 °C to about 60 °C, about 35 °C to about 50 °C, or between any two of aforementioned values. In some embodiments, the combined wet foam and reinforcement part may be dried for about 1 hour to about 48 hours, about 2 hours to about 24 hours, about 3 hours to about 16 hours, about 4 hours to about 12 hours, or between any two of aforementioned values.

[0063] In some embodiments, homogenized solution mixture in block 505 may be coated directed on reinforcement part or surgical mesh as seen in block 509. In some embodiments, surgical mesh may be coated with homogenized solution mixture by spray, immersion, brushing, or any methods commonly known in the art. After applying homogenized solution mixture to surgical mesh, surgical mesh is dry in block 510 in an oven, such as a forced air oven. In some embodiments, the combined wet foam and reinforcement part may be heated at about 20 °C to about 100 °C, about 25 °C to about 80 °C, about 30 °C to about 60 °C, about 35 °C to about 50 °C, or between any two of aforementioned values. In some embodiments, the combined wet foam and reinforcement part may be dried for about 1 hour to about 48 hours, about 2 hours to about 24 hours, about 3 hours to about 16 hours, about 4 hours to about 12 hours, or between any two of aforementioned values.

[0064] In some embodiments, photocurable foam may be applied or deposited on a top surface, a bottom surface, or both the top and bottom surfaces of surgical mesh. In some embodiments, the foam coating may have a thickness from about 0.1 mm to about 5 mm, about 0.2 mm to about 4 mm, about 0.3 mm to about 3 mm, about 0.4 mm to about 2 mm,about 0.5 mm to about 1 mm, or between any two of aforementioned values. In some embodiments, all or partial coverage of photocurable foam or film may be applied to the surgical mesh. Now referring to FIG. 6, another embodiment of surgical mesh 600 is disclosed herein. Surgical mesh 600 may have the same, similar, and / or substantially the same features and functionality, as well as be fabricated using the similar and / or substantially the same method as explained above with respect to surgical mesh 100, 200, or 300. It should be understood that parts with similar numbering, i.e., 601, 301, 201, and 101, describe the same or substantially the same features. For example, surgical mesh 600 may comprise a biocompatible reinforcement part 601, pores 603, and photocurable adhesive coating 605.

[0065] As illustrated in FIG. 6, surgical mesh 600 may comprise partial coverage of photocurable adhesive coating 605 at various “zones,” i.e., around the edges partially in the middle, on both top surface 620 and bottom surfaces 610 of surgical mesh 600 to facilitate insertion and deployment and of the surgical mesh using an external device such as a trocarfor laparoscopic or robot assisted surgery. In some embodiments, partial coverage allows to form a marker on the surgical mesh to facilitate the identification of the side of the surgical mesh to place against tissue, the orientation of the surgical mesh inside the abdominal cavity and the centering of the surgical mesh on the hernia defect. In some embodiments, partial coverage allows for the use of less materials and provides flexible application of photocurable adhesive coating 605 to desired tissue area, or around certain areas where photocurable adhesive coating may not be required, i.e., specific anatomical part of the dissection plan such as spermatid cord for example.

[0066] A related aspect of the present disclosure provides a method of treating a patient using a surgical mesh of the present disclosure. In some embodiments, a surgeon may apply surgical mesh, i.e., surgical mesh 100, 200, 300, 400, or 600, of the present disclosure to damaged tissue area. By applying a compression to the tissue area, a contact induced adhesion between the tissue and the surgical mesh is achieved. In some embodiments, the surgeon may remove and reposition surgical mesh as needed despite the adhesion that may be present or have occurred. In some embodiments, the surgeon may provide further liquid in the form of, for example, saline. Additionally, in some embodiments the surgeon may illuminate the surgical mesh with a light source to activate photocurable adhesive coating on surgical mesh to provide adhesion between surgicalmesh and the tissue area. Afterwards, tissue is grown around the exterior edges of the surgical mesh and through the pores of the mesh during the healing process. The photocurable adhesive coating is bioabsorbed and biodegraded by enzymes in the tissue and metabolized in the body.EXAMPLE

[0067] The disclosed technology is next described by means of the following examples. The use of these and other examples anywhere in the specification is illustrative only, and in no way limits the scope and meaning of the invention or of any exemplified form. Likewise, the invention is not limited to any particular or preferred embodiments described herein. Indeed, modifications and variations of the invention may be apparent to those skilled in the art upon reading this specification and can be made without departing from its spirit and scope. The invention is therefore to be limited only by the terms of the claims, along with the full scope of equivalents to which the claims are entitled. Efforts have been made to ensure accuracy with respect to values presented (e.g., amounts, temperature, etc.), but some experimental error and deviation should be accounted for.Example 1 : Preparation of a collagen-based photocurable solution.

[0068] A photocurable solution having the formulation set forth in Table 1 was prepared using the method disclosed below.Table 1.Component Chemical Final concentration in photocurable solution Curable Pepsin soluble collagen about 1.25 % w / wPolymer Denatured collagen about 3.0 % w / wPhoto initiator Ru(BPY)3 about 0.025% w / wCo-initiator Sodium Persulfate about 0.125 % w / wSolvent Distilled water

[0069] According to the formulation disclosed in Table 1, pepsin soluble collagen was solubilized in distilled water at 20 °C for 16 hours to produce a pepsin soluble collagen solution comprising about 1.0 %w / w to about 3.0 %w / w pepsin collagen. Afterwards, collagen was denatured and solubilized in distilled water at about 45 °C for about 30 minutes to produce a denatured collagen solution comprising about 2.0 %w / w to about6.0 % w / w denatured collagen. The denatured collagen solution was cooled at about 30 °C and mixed with pepsin soluble collagen solution to form a combined collagen solution comprising from about 0.5 %w / w to about 1.5 %w / w of pepsin soluble collagen and about 1.0 w / w% to about 1.5 %w / w of denatured collagen, based on the total weight of the combined solution / photocurable solution. After homogenization of the combined collagen solution, about 0.025 % w / w of Ru(BPY)3 photo initiator and about 0.125 % w / w sodium persulfate co-initiator, both based on the total weight of the combined solution / photocurable solution, were added and solubilized for 15 minutes at 30 °C. The photocurable solution was also prepared into a film by coating the surgical mesh with photocurable solution on surgical mesh and air drying the mesh producing a thin film on surface of the reinforcement component of the surgical mesh. The surgical mesh coated with photocurable film was evaluated for adhesive strength.

[0070] The photocurable solution was also prepared into a foam by mechanical foaming / aerating for about 2 minutes to about 5 minutes to incorporate air volume into the solution and produce a wet foam with a density of about 0.2 g / cm3. The wet foam was then casted on both sides of a knitted textile in polypropylene. The knitted textile covered with wet foam was then placed in air oven set at 20 °C for 12 hours to dry the wet foam. After drying, the adhesive properties on tissue of the photocurable coated mesh was evaluated.Example 2: Adhesive strength of photocurable coated surgical mesh.

[0071] The surgical mesh samples coated with photocurable film and foam were tested to evaluate adhesion strength on mammalian tissue. As seen in FIG. 7, after initial positioning of the samples, the adhesion strength of the samples was measured to be about 1 kPa for the film coated surgical mesh sample and about 3 kPa for the foam coated surgical mesh sample. The samples were removed and repositioned, i.e., “1stReposition” which slightly reduced the adhesion strength for both samples. The samples were again removed, repositioned, and the photocurable adhesive coating activated by an endoscope light i.e., “2ndReposition + Light.” Upon photoactivation, the adhesion strength of both film and foam increased at least two-fold from the initially measured adhesion to about 5 kPa for the film and about 7 kPa for the foam. Furthermore, both film and foam samples exhibited greater adhesion strength compared to current commercially available state-of-the-art surgical mesh.

[0072] It should be understood that various aspects disclosed herein may be combined in different combinations than the combinations specifically presented in the description and accompanying drawings. For example, features, functionality, and components from one embodiment may be combined with another embodiment and vice versa unless the context clearly indicates otherwise. Similarly, features, functionality, and components may be omitted unless the context clearly indicates otherwise. It should also be understood that, depending on the example, certain acts or events of any of the processes or methods described herein may be performed in a different sequence, may be added, merged, or left out altogether (e.g., all described acts or events may not be necessary to carry out the techniques).

[0073] Unless otherwise specifically defined herein, all terms are to be given their broadest possible interpretation including meanings implied from the specification as well as meanings understood by those skilled in the art and / or as defined in dictionaries, treatises, etc. It must also be noted that, as used in the specification and the appended claims, the singular forms "a," "an" and "the" include plural referents unless otherwise specified, and that the terms "comprises" and / or "comprising," when used in this specification, specify the presence of stated features, elements, and / or components, but do not preclude the presence or addition of one or more other features, steps, operations, elements, components, and / or groups thereof.

[0074] Without excluding further possible embodiments, certain example embodiments are summarized in the following clauses:

[0075] Clause 1 : A surgical mesh comprising: a reinforcement part (101); and a photocurable adhesive (105) deposited on surface of the reinforcement part; wherein the photocurable adhesive is configured to bond to tissue when exposed to an optical energy source while the surgical mesh is in contact with the tissue.

[0076] Clause 2 : The surgical mesh of clause 1, wherein the reinforcement part comprises biocompatible material, bioabsorbable materials, non-bioabsorbable materials, or combinations thereof.

[0077] Clause 3 : The surgical mesh of clause 1 or 2, wherein the photocurable adhesive comprises: about 0.2 %w / w to about 20 %w / w one or more photopolymer, based on the total weight of the photocurable adhesive; and about 0.005 %w / w to about 1.0% w / w photo initiator, based on the total weight of the photocurable adhesive.

[0078] Clause 4 : The surgical mesh of clause 3, further comprising about 0.01 %w / w to about 5.0 %w / w co-initiator, based on the total weight of the photocurable adhesive.

[0079] Clause 5 : The surgical mesh of clause 3 or 4, wherein the photopolymer is selected from the group consisting of pepsin soluble collagen, denatured collagen, collagen acrylamide, gelatin tyramine, gelatin methacrylamide, sodium hyaluronate tyramine, and combinations thereof.

[0080] Clause 6 : The surgical mesh of clause 3 or 4, wherein the photo initiator is selected from the group consisting of Tris(2,2'-bipyridyl)dichlororuthenium(II) hexahydrate (Ru(BPY)3), Riboflavin, Eosin Y, Rose Bengal, and combinations thereof.

[0081] Clause 7 : The surgical mesh of any one of clauses 4-6, wherein the co-initiator is selected from the group consisting of sodium persulfate, ammonium persulfate and combinations thereof.

[0082] Clause 8 : The surgical mesh of any one of clauses 1-7, wherein the photocurable adhesive is a powder coating, a film coating, a foam coating, or combinations thereof.

[0083] Clause 9 : The surgical mesh of any one of clauses 1-8, wherein the photocurable adhesive is deposited on a top surface, a bottom surface, or both the top surface and the bottom surface of the reinforcement part.

[0084] Clause 10: The surgical mesh of any one of clauses 1-9, wherein the optical energy source comprises a light having a wavelength from 240 nm to 780 nm.

[0085] Clause 11: The surgical mesh of any one of clause 4-10, wherein the photocurable adhesive comprises: about 1.0 %w / w to about 3.0 %w / w denatured collagen, based on the total weight of the photocurable adhesive; about 0.5 %w / w to about 1.5 %w / w pepsin soluble collagen, based on the total weight of the photocurable adhesive; about 0.005 %w / w to about 0.025 %w / w of Ru(BPY)s, based on the total weight of the photocurable adhesive; and about 0.025 %w / w to about 0.5 %w / w of sodium persulfate, based on the total weight of the photocurable adhesive.

[0086] Clause 12: A method of producing a photocurable adhesive, the method comprising: (a) solubilizing a photopolymer in an aqueous solution to produce a photopolymer solution having a concentration of about 0.2 %w / w to about 20.0 %w / w photopolymer, based on the total weight of the photocurable adhesive; adding a photo initiator to the photopolymer solution to produce a photopolymer-photo initiator solutionhaving concentration of about 0.005 %w / w to about 1.0 %w / w a photo initiator, based on the total weight of the photocurable adhesive; and (c) homogenizing the combined solution.

[0087] Clause 13: The method of clause 12, further comprising after step (b) and before step (c), adding a co-initiator to the photopolymer-photo initiator solution to produce a combined solution having concentration of about 0.01 %w / w to about 5 %w / w a co-initiator, based on the total weight of the photocurable adhesive.

[0088] Clause 14: The method of clause 12 or 13, wherein step (a) is carried out at a temperature range from about 20 °C to about 50 °C for about 30 minutes to 24 hours.

[0089] Clause 15: The method of any one of clause 12-14, wherein step (b) is carried out at a temperature range from about 20 °C to about 50 °C for about 5 minutes to about 30 minutes.

[0090] Clause 16: The method of any one of clauses 13-15, wherein the adding a coinitiator is carried out at a temperature range from about 20 °C to about 50 °C for about 5 minutes to about 30 minutes.

[0091] Clause 17: The method of any one of clauses 12-16, after step (a) and before step (b), wherein the photopolymer is a first photopolymer, and further comprising adding a second photopolymer, wherein the second photopolymer is present at a concentration about 0.2 %w / w to about 20% w / w, based on the total weight of the photocurable adhesive.

[0092] Clause 18: The method of any one of clauses 11-15, further comprising after step (c): aerating the combined solution from about 1 minute to about 30 minutes to produce a wet foam; depositing the wet foam on a reinforcement part of a surgical mesh; and; air drying the wet foam to produce a dry foam coating.

[0093] Clause 19: A method of producing a photocurable adhesive foam, the method comprising: (a) solubilizing pepsin soluble collagen in an aqueous solution to produce a pepsin soluble collagen solution having a concentration of about 1.0 %w / w to about 3.0 %w / w, based on the total weight of the pepsin soluble collagen solution; (b) denaturing collagen in an aqueous solution to produce a denatured collagen solution having a concentration about 2.0 %w / w to about 6.0 %w / w denatured collagen, based on the total weight of the denatured collagen solution;(c) mixing the pepsin soluble collagen solution with the denatured collagen solution to produce a combined collagen solution comprisingabout 0.5 %w / w to about 1.5 %w / w pepsin soluble collagen, based on the total weight of the photocurable adhesive foam and about 1.0 %w / w to about 3.0 %w / w denatured collagen, based on the total weight of the photocurable adhesive foam;(d) adding a photo initiator and a co-initiator to the combined collagen solution to produce a photocurable collagen solution;(e) homogenizing the photocurable collagen solution; (f) aerating the photocurable collagen solution from about 2 minutes to about 5 minutes to produce a wet photocurable adhesive foam; and (g) depositing the wet photocurable adhesive foam on a reinforcement.

[0094] Clause 20: The method of clause 19, wherein step (d) comprises adding about 0.005 %w / w to about 0.025 %w / w of Ru(BPY)3, based on the total weight of the photocurable adhesive; and about 0.025 %w / w to about 0.125 %w / w of sodium persulfate, based on the total weight of the photocurable adhesive.

[0095] Clause 21: The method of clause 19 or 20, further comprising after step (g), air drying the wet photocurable adhesive foam to produce a dry photocurable adhesive foam.

[0096] Clause 22: A method of treating a patient using a surgical mesh, the method comprising: (a) applying the surgical mesh of any one of claims 1-11 to a damaged tissue area to provide a contact induced adhesion between the damaged tissue area and the surgical mesh; (b) illuminating the surgical mesh with a light source to activate the photocurable adhesive and to provide a light-induced adhesion between the damaged tissue area and the photocurable adhesive; and (c) allowing the photocurable adhesive to be metabolized by the damaged tissue area; and allowing tissue ingrowth through pores of the reinforcement part of the surgical mesh, wherein step (a) comprises removing and repositioning the surgical mesh without substantial reduction in adhesive strength between the damaged tissue area and the surgical mesh.

Claims

WHAT IS CLAIMED IS:

1. A surgical mesh comprising:a reinforcement part (101); anda photocurable adhesive (105) deposited on surface of the reinforcement part; wherein the photocurable adhesive is configured to bond to tissue when exposed to an optical energy source while the surgical mesh is in contact with the tissue.

2. The surgical mesh of claim 1, wherein the reinforcement part comprises biocompatible material, bioabsorbable materials, non-bioabsorbable materials, or combinations thereof.

3. The surgical mesh of claim 1 or claim 2, wherein the photocurable adhesive comprises:about 0.2 %w / w to about 20 %w / w one or more photopolymer, based on the total weight of the photocurable adhesive; andabout 0.005 %w / w to about 1.0% w / w photo initiator, based on the total weight of the photocurable adhesive.

4. The surgical mesh of claim 3, further comprising about 0.01 %w / w to about 5.0 %w / w co-initiator, based on the total weight of the photocurable adhesive.

5. The surgical mesh of claim 3 or 4, wherein the photopolymer is selected from the group consisting of pepsin soluble collagen, denatured collagen, collagen acrylamide, gelatin tyramine, gelatin methacrylamide, sodium hyaluronate tyramine, and combinations thereof.

6. The surgical mesh of claim 3 or 4, wherein the photo initiator is selected from the group consisting of Tris(2,2'-bipyridyl)dichlororuthenium(II) hexahydrate (Ru(BPY)3), Riboflavin, Eosin Y, Rose Bengal, and combinations thereof.

7. The surgical mesh of claim 4, wherein the co-initiator is selected from the group consisting of sodium persulfate, ammonium persulfate and combinations thereof.

8. The surgical mesh of any one of claims 1-7, wherein the photocurable adhesive is a powder coating, a film coating, a foam coating, or combinations thereof.

9. The surgical mesh of any one of claims 1-8, wherein the photocurable adhesive is deposited on a top surface, a bottom surface, or both the top surface and the bottom surface of the reinforcement part.

10. The surgical mesh of any one of claims 1-9, wherein the optical energy source comprises a light having a wavelength from 240 nm to 780 nm.

11. The surgical mesh of any one of claims 4-10, wherein the photocurable adhesive comprises:about 1.0 %w / w to about 3.0 %w / w denatured collagen, based on the total weight of the photocurable adhesive;about 0.5 %w / w to about 1.5 %w / w pepsin soluble collagen, based on the total weight of the photocurable adhesive;about 0.005 %w / w to about 0.025 %w / w of Ru(BPY)3, based on the total weight of the photocurable adhesive; andabout 0.025 %w / w to about 0.5 %w / w of sodium persulfate, based on the total weight of the photocurable adhesive.

12. A method of producing a photocurable adhesive, the method comprising:(a) solubilizing a photopolymer in an aqueous solution to produce a photopolymer solution having a concentration of about 0.2 %w / w to about 20.0 %w / w photopolymer, based on the total weight of the photocurable adhesive;(b) adding a photo initiator to the photopolymer solution to produce a photopolymer-photo initiator solution having concentration of about 0.005 %w / w to about 1.0 %w / w a photo initiator, based on the total weight of the photocurable adhesive; and(c) homogenizing the combined solution(d) aerating the combined solution from about 1 minute to about 30 minutes to produce a wet foam;(e) depositing the wet foam on a reinforcement part of a surgical mesh; and(f) air drying the wet foam to produce a dry foam coating.

13. The method of claim 12, further comprising after step (b) and before step (c), adding a co-initiator to the photopolymer-photo initiator solution to produce a combined solution having concentration of about 0.01 %w / w to about 5 %w / w a co-initiator, based on the total weight of the photocurable adhesive.

14. The method of claim 12 or 13, wherein step (a) is carried out at a temperature range from about 20 oC to about 50 oC for about 30 minutes to 24 hours.

15. The method of any one of claims 12-14, wherein step (b) is carried out at a temperature range from about 20 oC to about 50 oC for about 5 minutes to about 30 minutes.

16. The method of any one of claims 13-15, wherein the adding a co-initiator is carried out at a temperature range from about 20 oC to about 50 oC for about 5 minutes to about 30 minutes.

17. The method of any one of claims 12-16, after step (a) and before step (b), wherein the photopolymer is a first photopolymer, and further comprising adding a second photopolymer, wherein the second photopolymer is present at a concentration about 0.2 %w / w to about 20% w / w, based on the total weight of the photocurable adhesive.

18. A method of producing a photocurable adhesive foam, the method comprising: (a) solubilizing pepsin soluble collagen in an aqueous solution to produce a pepsin soluble collagen solution having a concentration of about 1.0 %w / w to about 3.0 %w / w, based on the total weight of the pepsin soluble collagen solution;(b) denaturing collagen in an aqueous solution to produce a denatured collagen solution having a concentration about 2.0 %w / w to about 6.0 %w / w denatured collagen, based on the total weight of the denatured collagen solution;(c) mixing the pepsin soluble collagen solution with the denatured collagen solution to produce a combined collagen solution comprising about 0.5 %w / w to about 1.5 %w / w pepsin soluble collagen, based on the total weight of the photocurable adhesive foam and about 1.0 %w / w to about 3.0 %w / w denatured collagen, based on the total weight of the photocurable adhesive foam;(d) adding a photo initiator and a co-initiator to the combined collagen solution to produce a photocurable collagen solution;(e) homogenizing the photocurable collagen solution;(f) aerating the photocurable collagen solution from about 2 minutes to about 5 minutes to produce a wet photocurable adhesive foam; and(g) depositing the wet photocurable adhesive foam on a reinforcement.

19. The method of claim 18, wherein step (d) comprises adding about 0.005 %w / w to about 0.025 %w / w of Ru(BPY)3, based on the total weight of the photocurable adhesive; and about 0.025 %w / w to about 0.125 %w / w of sodium persulfate, based on the total weight of the photocurable adhesive.

20. The method of claim 18 or 19, further comprising after step (g), air drying the wet photocurable adhesive foam to produce a dry photocurable adhesive foam.

21. A method of treating a patient using a surgical mesh, the method comprising : (a) applying the surgical mesh of any one of claims 1-11 to a damaged tissue area to provide a contact induced adhesion between the damaged tissue area and the surgical mesh;(b) illuminating the surgical mesh with a light source to activate the photocurable adhesive and to provide a light-induced adhesion between the damaged tissue area and the photocurable adhesive; and(c) allowing the photocurable adhesive to be metabolized by the damaged tissue area; and allowing tissue ingrowth through pores of the reinforcement part of the surgical mesh.wherein step (a) comprises removal and repositioning of the surgical mesh without substantial reduction in adhesive strength between the damaged tissue area and the surgical mesh.30

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