[go: up one dir, main page]

WO2025041142A1 - Composés co-polymères, hydrogels les comprenant et leurs utilisations - Google Patents

Composés co-polymères, hydrogels les comprenant et leurs utilisations Download PDF

Info

Publication number
WO2025041142A1
WO2025041142A1 PCT/IL2024/050846 IL2024050846W WO2025041142A1 WO 2025041142 A1 WO2025041142 A1 WO 2025041142A1 IL 2024050846 W IL2024050846 W IL 2024050846W WO 2025041142 A1 WO2025041142 A1 WO 2025041142A1
Authority
WO
WIPO (PCT)
Prior art keywords
polymeric compound
hydrogel
composition
group
composite material
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Pending
Application number
PCT/IL2024/050846
Other languages
English (en)
Inventor
Jacob Klein
Monika KLUZEK
Weifeng Lin
Panpan ZHAO
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Yeda Research and Development Co Ltd
Original Assignee
Yeda Research and Development Co Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Yeda Research and Development Co Ltd filed Critical Yeda Research and Development Co Ltd
Publication of WO2025041142A1 publication Critical patent/WO2025041142A1/fr
Pending legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Classifications

    • 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
    • A61L27/18—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
    • 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
    • A61L27/40—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L27/44—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
    • A61L27/48—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix with macromolecular fillers
    • 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
    • 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
    • A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/04—Macromolecular materials
    • A61L29/06—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
    • 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
    • A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/08—Materials for coatings
    • A61L29/085—Macromolecular materials
    • 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
    • A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/12—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L29/126—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
    • 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
    • A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
    • A61L29/14—Materials characterised by their function or physical properties, e.g. lubricating compositions
    • A61L29/145—Hydrogels or hydrocolloids
    • 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
    • A61L2400/00—Materials characterised by their function or physical properties
    • A61L2400/10—Materials for lubricating medical devices

Definitions

  • the present invention in some embodiments thereof, relates to material science, and more particularly, but not exclusively, to novel co-polymeric compounds usable, inter alia, in lubrication applications and/or in reducing biofilm formation on a surface of various substrates.
  • Natural articular cartilage is a thin layer of porous hydrated tissue with low friction that is unmatched by any artificial material [Jahn et al., Annual Review of Biomedical Engineering 2016, 18 (1), 235-258; Lin and Klein, Advanced Materials 2021, 33 (18), 2005513]. Damage caused by trauma or aging can lead to joint diseases, such as osteoarthritis [Lotz, M. K., Arthritis Research & Therapy 2010, 12 (3), 211; Loeser, R. F., Current Opinion in Rheumatology 2011, 23 (5), 492- 496].
  • Hydrogels which are widely used in biomedical and other applications [Green and Elisseeff, Nature 2016, 540 (7633), 386-394; Peppas et al., Advanced materials 2006, 18 (11), 1345-1360; Zhang et al., Angewandte Chemie International Edition 2022, 61 (39), e202209741], are considered suitable replacement materials for damaged articular cartilage due to their good biocompatibility, liquid permeability, and wettability [Ngadimin et al., Biomaterials Science 2021, 9 (12), 4246-4259; Zhou et al., Engineering 2022, 13, 71-90].
  • Gulsen et aZ. teach contact lens compositions with drug delivery capabilities, and specifically teach dispersing exceptionally small dimyristoylphosphatidylcholine (DMPC) SUV liposomes (less than 50 nm or 80 nm in diameter) in poly-2-hydroxyethyl methacrylate (pHEMA) hydrogels, which are common contact lens materials.
  • DMPC dimyristoylphosphatidylcholine
  • pHEMA poly-2-hydroxyethyl methacrylate
  • pMPC biomimetic boundary lubricant poly(2- methacryloyloxyethylphosphorylcholine)
  • DN poly(2- acrylamido-2-methylpropanesulfonic acid)-polyacrylamide double network
  • pMPC-DN three-component network
  • a bilayer hydrogel material inspired by the structure of the articular cartilage has also been designed, comprising thick hydrophilic polyelectrolyte brushes on the topmost of the hydrogel which provide effective water-based lubrication, while the hard hydrogel layer as the substrate provides load-bearing capacity [Rong et al., Advanced Functional Materials 2020, 30 (39), 2004062].
  • a synergistic effect has been reported therein, which was suggested to be due to high hydration of charged chains embedded in the composite hydrogel films, which enables a low friction coefficient under heavy load conditions in water, and thus allows its performance to be comparable to that of natural articular cartilage.
  • WO 2017/109784 discloses lipid-polymer conjugates, including lipid-pMPC conjugates, liposomes made therefrom and uses thereof. These liposomes have been reported as exhibiting improved stability and enhanced performance as lubricants compared to, for example, corresponding PEG-functionalized liposomes.
  • Biofilms a group of microorganisms that stick to each other on a surface and produce a self-made matrix composed of extracellular DNA, proteins, and polysaccharides, can facilitate the formation of fouling by providing a surface for the adhesion of microorganisms.
  • Biofilms can also accelerate the corrosion of metallic substrates and become highly antibiotic -resistant, leading to infections associated with medical devices in contact with human tissue, such as stents or catheters.
  • Hydrogels formed by copolymerization of carboxybetaine monomers with 2-hydroxyethyl methacrylate (HEMA) have been reported to exhibit low levels of fouling from blood plasma [Kostina et al., Biomacromolecules 2012, 13, 4164-4170].
  • Modification of polysulfone (PSf) membranes with 2-methacryloxyethyl phosphorylcholine (MPC) polymer was reported to decrease protein adsorption [Ishihara et al., Biomaterials 1999, 20, 1553-1559].
  • Other studies have associated zwitterionic hydrogel surfaces with enhanced antifouling properties [Schlenoff, Langmuir 2014, 30, 9625-9636; Yang et al., J Mat Chem B 2014, 2, 577-584].
  • WO 2015/001564 describes hydrogels having liposomes dispersed therein, which exhibit a reduced friction coefficient compared to neat hydrogels, processes for preparing the same, and methods for using the same, e.g., in replacing missing or damaged cartilage in a living organism suffering from a medical condition associated with loss of or damaged cartilage.
  • WO 2015/193888 discloses solutions comprising a water-soluble polymer, liposomes, and an aqueous carrier, for reducing a friction coefficient of a surface, and methods utilizing same.
  • Yi and Y2 are each independently a backbone unit which forms a polymeric backbone
  • Li and L2 are each independently absent or is a linking moiety
  • Ei and E2 each independently represents a terminal group
  • W is a hydrophobic group
  • A is a substituted or unsubstituted hydrocarbon
  • B is an oxygen atom or is absent
  • R1-R3 are each independently selected from the group consisting of hydrogen, alkyl, cycloalkyl, heteroalicyclic, aryl and heteroaryl, wherein when n+m is greater than 2, the -[Y1-L1-Z]- units and the -[Y2-L2-W]- units are arranged in any order so as to form a random co-polymeric compound.
  • Yi and Y2 are each independently a substituted or unsubstituted alkylene unit. In some of any of the embodiments described herein, Yi and Y2 are each independently a substituted or unsubstituted ethylene unit.
  • each of Y 1 and Y2 independently has the formula -CR4R5-CR6D-, wherein: when Yi is a backbone unit which is not attached to the Li or the Z, D is R7; and when Yi is a backbone unit which is attached to the Li or the Z, D is absent or a linking group attaching Y 1 to the Li or the Z, and when Y2 is a backbone unit which is not attached to the L2 or the W, D is Rs; and when Y2 is a backbone unit which is attached to the L2 or the W, D is absent or a linking group attaching Y2 to the L2 or the W, wherein when D is a linking group, the linking group being selected from the group consisting of -O-, -S-, alkylene, arylene, sulfinyl, sulfonyl, phosphate, phosphonyl, phosphinyl, carbonyl, thiocarbonyl
  • R4-R8 are each independently selected from the group consisting of hydrogen, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, heteroalicyclic, halo, hydroxy, alkoxy, aryloxy, thiohydroxy, thioalkoxy, thioaryloxy, sulfinyl, sulfonyl, cyano, nitro, azide, azo, phosphate, phosphonyl, phosphinyl, oxo, carbonyl, thiocarbonyl, urea, thiourea, O-carbamyl, N-carbamyl, O- thiocarbamyl, N-thiocarbamyl, C-amido, N-amido, C-carboxy, O-carboxy, sulfonamido, and amino.
  • R4 and R5 are each hydrogen.
  • Re is hydrogen or alkyl (e.g., methyl).
  • D is a linking group
  • Li is a substituted or unsubstituted hydrocarbon from 1 to 10 carbon atoms in length.
  • Li is a substituted or unsubstituted ethylene group.
  • B is an oxygen atom.
  • A is a substituted or unsubstituted hydrocarbon of from 1 to 4 carbon atoms in length. In some of any of the embodiments described herein, A is a substituted or unsubstituted ethylene group.
  • R1-R3 are each independently hydrogen or Ci-4-alkyl.
  • R1-R3 are each methyl.
  • Ei is or comprises a lipid moiety.
  • the sum of the n and the m is at least 3.
  • the sum of n+m is in a range of from 3 to 5000.
  • a ratio of n to m representing a mol ratio between the -[Y1-L1-Z]- units and the -[Y2-L2-W]- units in the co-polymeric compound, is in a range of from 1:10 to 1:50, or from 1:2 to 1:50, or from 1:3 to 1:10 (n:m).
  • the polymeric compound comprises at least one targeting moiety.
  • the targeting moiety is attached to one or more of the Yi and Y2 backbone units, Ei and E2 terminal groups, Li and L2 linking moieties, the Z group and the W group.
  • W is a hydrocarbon of at least 3 carbon atoms in length.
  • W is an alkyl of at least 3 carbon atoms in length.
  • W is or comprises a branched alkyl of at least 3 carbon atoms in length.
  • W is isopropyl
  • composition comprising a hydrogel or a composite material comprising a hydrogel, the hydrogel having incorporated therein the co-polymeric compound according to some of any of the embodiments described herein.
  • an amount of the co- polymeric compound is in a range of from 0.1 % to 10 %, or from 0.1 % to 5 %, by weight, of the total weight of the composition or of the hydrogel or the composite material.
  • a degree of crosslinking of the hydrogel is in a range of from 1 to 10, or from 1 to 5, %.
  • the hydrogel is formed of at least one hydrogel-forming agent selected from hydroxyethyl methacrylate (HEMA), hydroxyethyl acrylate (HEA), acrylamide (AAm), methacrylamide (MAAm), acrylic acid (AAc), methacrylic acid (MAAc), hydroxyethyl acrylate (HEA), hexyl methacrylate, N- isopropylacrylamide (NIPAM)), N-isopropylmethacrylamide, polylactic acid, polyamide, polyethylene-terephthalate (PET), polyvinyl alcohol, polyurethane, polycaprolactone, polyethylene-glycol (PEG), polyethylene-glycol methacrylate (PEGMA), polyethyleneoxide dimethacrylate (PEOdMA), N
  • HEMA hydroxyethyl methacrylate
  • HEMA hydroxyethy
  • the hydrogel comprises hydroxyethyl methacrylate (HEMA) and/or poly hydroxyethyl methacrylate (pHEMA).
  • HEMA hydroxyethyl methacrylate
  • pHEMA poly hydroxyethyl methacrylate
  • the composition or composite material is in a dry form.
  • the composition or composite material further comprises at least one additional agent selected from the group consisting of a polymeric compound, a hydrogel-forming agent, a sterol (e.g., cholesterol), a liposome-stabilizing agent, a labeling agent, a bioactive agent, and a therapeutically active agent.
  • the process further comprises, subsequent to the dehydrating, rehydrating the composition.
  • the crosslinking agent is selected from the group consisting of poly(ethylene glycol) n dimethacrylate (EGDMA), N,N’- methylenebis(acrylamide) (MBAm), N,N'-methylenebis(2-methylacrylamide), methylene diacrylate, methylene bis(2-methylacrylate), diethylene glycol diacrylate, hexamethylene diacrylate, oxybis(methylene) bis(2-methylacrylate) and oxybis(ethane-2,l-diyl) bis(2- methylacrylate).
  • composition or composite material prepared by the process according to some of any of the embodiments described herein.
  • the composite material comprises a material selected from the group consisting of a woven mesh of fibers, non-woven fibers, a plurality of rods and a net.
  • a method of lowering a friction coefficient of a hydrogel or of a composite material comprising a hydrogel comprising forming the hydrogel in the presence of the co-polymeric compound as described herein in any of the respective embodiments and any combination thereof.
  • the dynamic friction coefficient in aqueous medium of the hydrogel or composite material containing a hydrogel having the co-polymeric compound incorporated therein is reduced by a factor of at least 2 relative to the friction coefficient of the hydrogel not having the co-polymeric compound incorporated therein.
  • the method further comprises dehydrating the hydrogel or composite material containing a hydrogel and rehydrating the hydrogel.
  • the friction coefficient is substantially maintained after at least one dehydration-rehydration cycle.
  • an article - of-manufacturing comprising the composition or composite material as described herein in any of the respective embodiments and any combination thereof.
  • the article-of- manufacturing is selected from the group consisting of an implantable medical device, a drug- delivery system, a solid body, a disc, a fiber, a fabric, a tube, a film, a rod, a ring, a tubular mesh and any combination thereof.
  • the composition or composite material is for use in replacing missing or damaged cartilage in a living organism suffering from a medical condition associated with loss of or damaged cartilage.
  • the medical condition is selected from the group consisting of a skeletal joint replacement or reconstruction, vertebrate replacement or reconstruction, tendon replacement, tissue regeneration and reduction of tissue irritation by an implantable device.
  • a method of lowering the friction coefficient of a surface of a substrate comprising applying to the surface the composition or composite material according to any of the embodiments described herein.
  • lowering the friction coefficient is under aqueous or non-aqueous conditions.
  • the substrate is a physiological substrate.
  • the substrate is a medical device, e.g., an implantable medical device.
  • a method of inhibiting biofilm formation on a surface of a substrate comprising contacting the substrate with a composition or composite material according to some of any of the embodiments described herein.
  • FIGs. 1A-B present the chemical structure of an exemplary co-polymeric compound according to some embodiments of the present invention, poly(2-methacryloyloxyethyl phosphorylcholine-co-V-isopropylacrylamide) (PMN) co-polymer (FIG. 1A) and a relevant portion of its X H-NMR spectrum in D2O (FIG. IB).
  • PMN poly(2-methacryloyloxyethyl phosphorylcholine-co-V-isopropylacrylamide)
  • FIGs. 2A-B are cryo-SEM images presenting characterization of PMN-free (FIG. 2A) and PMN-incorporating (FIG. 2B) pHEMA hydrogels.
  • FIGs. 2C-D are confocal microscopy images showing an orthogonal view (FIG. 2C, upper inset) and an in-plane view (FIG. 2C, rightmost inset, and FIG. 2D) of a 40 pm thick slice hydrogel incorporating fluorescently labeled PMN pockets recorded at room temperature (RT). Scale bars are 20 pm in FIG. 2C and 10 pm in FIG. 2D.
  • FIGs. 3A-B present comparative plots showing size distribution (FIG. 3 A) and zeta potential (FIG. 3B) characterizations of pHEMA (red) and pHEMA/PMN mixture (green) in water, as measured by DLS after dialysis, as described herein.
  • FIGs. 5A-D are images of Brightfield (FIGs. 5A and 5C) and Syto9 (FIGs. 5B and 5D) fluorescence confocal microscopy images of neat (FIGs. 5A and 5B) and PMN-incorporating (FIGs. 5C and 5D) pHEMA hydrogels. Scale bar is 20 pm.
  • FIG. 6 presents comparative plots showing the storage and loss moduli (G’ and G”, respectively) of PMN-free and PMN-incorporating (2 %) pHEMA hydrogels.
  • FIGs. 7A-E are bar graphs showing sliding friction coefficients (p): of 0.1 %, 0.3 % and 1.0 % PMN-incorporating pHEMA hydrogels relative to the PMN-free HEMA hydrogel at different loads, between a pHEMA hydrogel and a sliding stainless steel sphere (hydrophilic) (FIG. 7 A); of different PMN-free (denoted as “neat”) hydrogels (HEMA-co-HEAA, HEMA-co-DMAA, PEGMA) and a stainless-steel sphere, relative to the respective 1 % PMN-incorporating hydrogel (FIG.
  • p sliding friction coefficients
  • FIG. 7F presents comparative plots showing sliding friction coefficients (p) of PMN-free and PMN-incorporating pHEMA hydrogels at different sliding velocity (V s ), as measured against stainless steel sphere. Error bars indicate standard deviation (SD) from at least three measurements.
  • FIGs. 8A-C are photographs (acquired as described herein) of PMN-free pHEMA hydrogel (FIG. 8A) and pHEMA hydrogels incorporating DMPC (lipid) (FIG. 8B) and PMN copolymer (FIG. 8C) samples on a polyethylene (PE) sphere after 1 hour of sliding back-and-forth under a 10 N load. Hydrogels are immersed in 3 mL of water.
  • FIGs. 9A-D present fluorescence signals recorded by Typhoon FLA 9500 fluorescence scanner (GE Healthcare Bio-Sciences AB, Sweden) on polyethylene (PE) (FIGs. 9A and 9C) and stainless-steel (SS) (FIGs. 9B and 9D) spherical ball upon 5 minutes sliding at 1 mm/s velocity on rhodamine-labeled PMN (FIGs. 9A and 9B) and Dil-labelled DMPC liposomes (FIGs. 9C and 9D) incorporated in pHEMA hydrogels.
  • Photomultiplier tube set up at 500' gain and pixel size 50 pm. Scale bar is 0.2 cm.
  • FIGs. 10A-B present comparative plots showing the fluorescence signal of PMN- rhodamine (FIG. 10A) and DMPC-Dil (FIG. 10B) obtained from stainless steel (SS) and polyethylene (PE) heads upon 5 minutes sliding.
  • the insets present the calibration curve of rhodamine-PMN in water (FIG. 10A) and DMPC-Dil in chloroform (FIG. 10B) solutions.
  • FIGs. 11A-B are bar graphs showing sliding friction coefficients (p) at 100 grams load of a commercial urethral PE catheter (lubricated with glycerol, or modified without lubricant, with neat pHEMA hydrogel, or with PMN-incorporating pHEMA hydrogel) against a sliding polyethylene (hydrophobic) (FIG. 11A), or a sliding pHEMA sphere (FIG. 11B).
  • PMN concentration in the hydrogel was 2 %
  • the pHEMA hydrogel was 2 % cross-linked.
  • FIGs. 12A-C present a schematic illustration of a Vero cells culture setup for evaluating the cytotoxic effect of PMN-incorporating pHEMA hydrogel (1 %.PMN) (FIG. 12A); photographs of neat and PMN-incorporating pHEMA hydrogels placed in Transwell® (FIG. 12B); and a bar graph showing cellular viability of the cells following 48 hours incubation with and without the pHEMA hydrogels (FIG. 12C).
  • Data represents two biological repeats (black and white data point) with a minimum of two technical repeats each.
  • FIG. 13 A presents representative Typhoon-scanned fluorescence images of neat pHEMA hydrogels and of pHEMA hydrogels incorporating DMPC or PMN, incubated for 24 hours with Vero E6 cells labeled with Vybrant DiD (denoted “DiD”) or incubated for 12 hours with GFP- expressing E. coli bacteria (denoted “GFP”). Scale bar is 1.5 mm.
  • FIGs. 13B-C present quantification of the DiD fluorescence intensity (FIG. 13B) and GFP fluorescence intensity (FIG. 13C) of pHEMA hydrogels obtained from plate reader measurements. Fluorescence intensity measurements were conducted on 4 biological samples. Boxes represent the 25-75 percentiles of the sample distribution, with black vertical lines representing 1.5xIQR (interquartile range). Black horizontal line represents the median.
  • FIGs. 14A-B present confocal microscopy images of neat, DMPC -incorporating and PMN- incorporating pHEMA hydrogels after 24 hours incubation with Vero E6 cells labeled with Vybrant DiD (FIG. 14A), and after 12 hours incubation with GFP-expressing E. coli bacteria (FIG. 14B). Images are presented as respective fluorescence signals (yellow-DiD, and green-GFP) and overlays of brightfield and fluorescence staining. Scale bars are 20 pm.
  • FIG. 15A presents a chemical structure and the relevant portion of its 1 H-NMR spectrum in methanol-d4 of the co-polymeric compound poly(2-methacryloyloxyethyl phosphorylcholine- co-A-propylacrylamidc) (PMP).
  • FIG. 15C presents comparative plots showing the storage and loss moduli (G’ and G”, respectively) of PMP- and PMN-incorporating (1 % by weight) pHEMA hydrogels.
  • the exemplary PMN co-polymer which features a branched alkyl, exhibits a superior lubricating performance compared to a similar co-polymer that features a linear alkyl having the same number of carbon atoms.
  • PMN-incorporating hydrogels represent new materials which are beneficial for numerous possible applications.
  • Yi and Y2 are each independently a backbone unit which forms a polymeric backbone
  • Li and L2 are each independently absent or is a linking moiety
  • Ei and E2 each independently represents a terminal group, as described herein;
  • W is a hydrophobic group
  • A is a substituted or unsubstituted hydrocarbon
  • B is an oxygen atom or is absent
  • R1-R3 are each independently selected from the group consisting of hydrogen, alkyl, cycloalkyl, heteroalicyclic, aryl and heteroaryl, wherein when n+m is greater than 2, the -[Y1-E1-Z]- units and the -[Y2-E2-W]- units are arranged in any order so as to form a random co-polymeric compound, as described in more detail herein below.
  • backbone unit refers to a repeating unit, wherein linkage between a plurality of repeating units (e.g., sequential linkage) forms a polymeric backbone.
  • the plurality of repeating units per se (regardless of the pendant groups) when linked to one another, is also referred to herein as a "polymeric backbone”.
  • polymeric compound refers to a compound having at least 2 repeating units (and more preferably at least 3 repeating units, and up to 50,000 repeating units). When all the repeating units are the same, a polymeric compound is considered a homopolymeric compound. When the polymeric compound comprises two or more types of repeating units, which can differ from one another by the type of the backbone units that form the polymeric backbone and/or by the type of the pendant groups, the polymeric compound is a co-polymeric compound.
  • co-polymeric compound refers to a polymeric compound comprising at least two different types of monomeric units. It is to be appreciated that the compound represented by Formula I is by definition co-polymeric when n and m are each a positive integer, as it comprises at least two backbone units represented by Yi and Y2, respectively. In exemplary embodiments, n is 200 and m is 1400.
  • the co-polymeric compound comprises two or more different types of monomeric unit which may be distributed randomly or non-randomly throughout the polymeric moiety.
  • the copolymer may be characterized by any non-random distribution, and can be, for example, an alternating copolymer, a periodic copolymer, and/or a block copolymer.
  • alternating copolymer describes a copolymer in which two adjacent backbone units alternate in a regular sequence along the polymer chain, such that the polymer has a repeating pattern of the two distinct backbone units.
  • each two adjacent backbone units are different from one another (e.g., Y1-Y2-Y1-Y2 or Y1-Y2-Y3-Y1-Y2-Y3)
  • peripheral copolymer describes a copolymer in which the arrangement of monomeric units follows a repeating sequence with a defined periodicity, which may involve more than two types of monomers, creating a regular and predictable sequence along the polymer chain (e.g., Y1-Y2-Y2-Y1-Y2-Y2-Y1-Y2-Y2-).
  • block copolymer describes a copolymer in which distinct blocks of repeating backbone units are linked together in segments, such that the polymer consists of large sequences ("blocks") composed of a plurality (e.g., 3 or more) of one type of backbone unit followed by a block of a plurality of another type of backbone unit (e.g., Yl-Yl-Y 1-Y2-Y2- Y2).
  • blocks a plurality (e.g., 3 or more) of one type of backbone unit followed by a block of a plurality of another type of backbone unit (e.g., Yl-Yl-Y 1-Y2-Y2- Y2).
  • the co-polymeric compound is a random co-polymeric compound in which the different types of the repeating backbone units, are distributed randomly, in any order, throughout the co-polymeric moiety.
  • co-polymeric moiety refers to the portion of the co-polymeric compound (according to any of the embodiments described herein relating to Formula I) which is represented by Formula la:
  • Li and Z together and L2 and W together each form a pendant group of at least a portion of the backbone units (i.e., Yi and Y2, respectively).
  • Each of these groups is referred to herein for brevity simply as the "pendant group”.
  • Each backbone unit Yi with its respective pendant group i.e., a unit represented by Yi(- Li-Z), the number of which is represented by the variable n
  • each backbone unit Y2 with its respective pendant group a unit represented by Y2(-L2-W), the number of which is represented by the variable m
  • a backbone unit may optionally be a residue of a polymerizable monomer or polymerizable moiety of a monomer.
  • a wide variety of polymerizable monomers and moieties are known to the skilled person, and the structure of the residues of such monomers which result upon polymerization (e.g., monomeric units) are also known to the skilled person.
  • a “residue of a polymerizable monomer” refers to a modified form of a polymerizable monomer and/or a portion of a polymerizable monomer that remains after polymerization.
  • a portion of a polymerizable monomer may be formed, for example, by a condensation reaction, e.g., wherein at least one atom or group (e.g., a hydrogen atom or hydroxyl group) in the monomer, and optionally at least two atoms or groups (e.g., a hydrogen atom and a hydroxyl group) in the monomer, is replaced with a covalent bond with another polymerizable monomer.
  • a condensation reaction e.g., wherein at least one atom or group (e.g., a hydrogen atom or hydroxyl group) in the monomer, and optionally at least two atoms or groups (e.g., a hydrogen atom and a hydroxyl group) in the monomer, is replaced with a covalent bond with another polymerizable monomer.
  • a modified form of a polymerizable monomer may be formed, for example, by ringopening (wherein a covalent bond between two atoms in a ring is broken, and the two atoms optionally each become linked to another polymerizable monomer); and/or by adding to an unsaturated bond, wherein an unsaturated bond between two adjacent atoms is broken (e.g., conversion of an unsaturated double bond to a saturated bond, or conversion of an unsaturated triple bond to an unsaturated double bond) and the two atoms optionally each become linked to another polymerizable monomer.
  • ringopening wherein a covalent bond between two atoms in a ring is broken, and the two atoms optionally each become linked to another polymerizable monomer
  • an unsaturated bond between two adjacent atoms is broken (e.g., conversion of an unsaturated double bond to a saturated bond, or conversion of an unsaturated triple bond to an unsaturated double bond) and the two atoms optionally
  • a modified form of a polymerizable monomer may consist essentially of the same atoms as the original monomer, for example, different merely in the rearrangement of covalent bonds, or alternatively, may have a different atomic composition, for example, wherein polymerization includes a condensation reaction (e.g., as described herein).
  • backbone units include, without limitation, substituted or unsubstituted hydrocarbons (which may form a substituted or unsubstituted hydrocarbon backbone), such as alkylene units; hydroxycarboxylic acid units (which may form a polyester backbone), e.g., glycolate, lactate, hydroxybutyrate, hydroxy valerate, hydroxycaproate and hydroxybenzoate units; dicarboxylic acid units (which may form a polyester backbone in combination with a diol and/or a polyamide in combination with a diamine), e.g., adipate, succinate, terephthalate and naphthalene dicarboxylic acid units; diol units (which may form a polyether backbone, or form a polyester backbone in combination with a dicarboxylic acid), e.g., ethylene glycol, 1,2-propanediol, 1,3- propanediol, 1,4-butanediol, and bisphenol
  • Yi and Y2 are each independently a substituted or unsubstituted alkylene unit.
  • Yi and Y2 are each independently a substituted or unsubstituted ethylene unit, that is, an alkylene unit 2 atoms in length.
  • vinyl monomers also referred to herein as "vinyl monomers”
  • any embodiments described herein relating to a polymeric backbone formed by a polymerization encompass any polymeric backbone having a structure which can be formed by such polymerization, regardless of whether the polymeric backbone was formed in practice by such polymerization (or any other type of polymerization).
  • the unsaturated bond of ethylene and substituted ethylene derivatives becomes saturated upon polymerization, such that the backbone units in a polymeric backbone are saturated, although they may be referred to as units of an unsaturated compound (e.g., a "vinyl monomer” or “olefin monomer”) to which they are analogous.
  • an unsaturated compound e.g., a "vinyl monomer” or “olefin monomer”
  • Polymers which can be formed from unsaturated monomers such as vinyl monomers and olefin monomers are also referred to by the terms "polyvinyl” and "polyolefin”.
  • an "unsubstituted" alkylene unit refers to an alkylene unit which does not have any substituent other than the pendant groups discussed herein (represented as (-Li- Z) and (-L2-W)). That is, an alkylene unit attached to the aforementioned pendant groups is considered unsubstituted if there are no substituents at any other positions on the alkylene unit.
  • each of Yi and Y2 independently has the formula -CR4R5-CR6D-, wherein: when Yi is a backbone unit which is not attached to the Li or the Z, D is R7; and when Yi is a backbone unit which is attached to the Li or the Z, D is absent or a linking group attaching Y 1 to the Li or the Z, and when Y2 is a backbone unit which is not attached to the L2 or the W, D is Rs; and when Y2 is a backbone unit which is attached to the L2 or the W, D is absent or a linking group attaching Y2 to the L2 or the W, wherein when D is a linking group, the linking group being selected from the group consisting of -O-, -S-, alkylene, arylene, sulfinyl, sulfonyl, phosphate, phosphonyl, phosphinyl, carbonyl, thiocarbonyl
  • R4-R8 are each independently selected from the group consisting of hydrogen, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, heteroalicyclic, halo, hydroxy, alkoxy, aryloxy, thiohydroxy, thioalkoxy, thioaryloxy, sulfinyl, sulfonyl, cyano, nitro, azide, azo, phosphate, phosphonyl, phosphinyl, oxo, carbonyl, thiocarbonyl, urea, thiourea, O-carbamyl, N-carbamyl, O- thiocarbamyl, N-thiocarbamyl, C-amido, N-amido, C-carboxy, O-carboxy, sulfonamido, and amino.
  • the phrase “linking group” describes a group (e.g., a substituent) that is
  • end group describes a group (e.g., a substituent) that is attached to a single moiety in the compound via one atom thereof.
  • R4 and R5 are each hydrogen.
  • Such embodiments include polymeric backbones formed from many widely used vinyl monomers (including ethylene), including, for example, olefins (e.g., ethylene, propylene, 1- butylene, isobutylene, 4-methyl-l -pentene), vinyl chloride, styrene, vinyl acetate, acrylonitrile, acrylate and derivatives thereof (e.g., acrylate esters, acrylamides), and methacrylate and derivatives thereof (e.g., methacrylate esters, methacrylamides).
  • olefins e.g., ethylene, propylene, 1- butylene, isobutylene, 4-methyl-l -pentene
  • vinyl chloride e.g., ethylene, propylene, 1- butylene, isobutylene, 4-methyl-l -pentene
  • vinyl chloride e.g., ethylene, propylene, 1- butylene,
  • Re is hydrogen.
  • R4 and R5 are each hydrogen.
  • D is a linking group attaching Yi to the Li or the Z, or attaching Y2 to the L2 or the W
  • Yi and Y2 each independently is an unsubstituted ethylene group attached (via D) to a pendant group as described herein.
  • Re is methyl.
  • R4 and R5 are each hydrogen.
  • the backbone unit is a unit of methacrylate or a derivative thereof (e.g., methacrylate ester, methacrylamide).
  • a vinyl alcohol derivative e.g., an ester or ether of a vinyl alcohol unit
  • an acrylate or methacrylate derivative e.g., an ester of an acrylate or methacrylate unit
  • a styrene derivative e.g., a substituted styrene unit
  • Li is a substituted or unsubstituted hydrocarbon from 1 to 10 carbon atoms in length.
  • the hydrocarbon is unsubstituted.
  • the hydrocarbon is a linear, unsubstituted hydrocarbon, that is, -(CH2)i- wherein i is an integer from 1 to 10, or from 1 to 8, or from 1 to 6, preferably from 1 to 4, or from 1 to 3, or is 1 or 2.
  • Li is a substituted or unsubstituted ethylene group. In some embodiments, Li is an unsubstituted ethylene group (- CH2CH2-). In some embodiments of any of the embodiments described herein, B is an oxygen atom. In some such embodiments, Li is a hydrocarbon according to any of the respective embodiments described herein (i.e., Li is not absent), and Z is a phosphate group attached to Li.
  • A is a substituted or unsubstituted hydrocarbon from 1 to 4 carbon atoms in length.
  • A is an unsubstituted hydrocarbon.
  • the unsubstituted hydrocarbon is from 1 to 4 carbon atoms in length.
  • the hydrocarbon is a linear, unsubstituted hydrocarbon, that is, -(CH2)j- wherein j is an integer from 1 to 4.
  • A is a substituted or unsubstituted ethylene group.
  • A is an unsubstituted ethylene group (-CH2CH2-).
  • the moiety represented by Formula II (represented by the variable Z) is similar or identical to a phosphoethanolamine or phosphocholine moiety.
  • Phosphoethanolamine and phosphocholine moieties are present in many naturally occurring compounds (e.g., phosphatidylcholines, phosphatidylethanolamines).
  • A is an ethylene group substituted by a C-carboxy group.
  • the C-carboxy is attached to the carbon atom adjacent to the nitrogen atom depicted in formula II (rather than the carbon atom attached to the depicted oxygen atom).
  • the moiety having general formula II (represented by the variable Z) is similar or identical to a phosphoserine moiety.
  • Phosphoserine is present in many naturally occurring compounds (e.g., phosphatidylserines).
  • moieties similar or identical to naturally occurring moieties such as phosphocholine, phosphoethanolamine and/or phosphoserine may be particularly biocompatible.
  • R1-R3 (the substituents of the nitrogen atom depicted in Formula II) are each independently hydrogen or Ci-4-alkyl. In some embodiments, R1-R3 are each independently hydrogen or methyl. In some embodiments, Ri- R3 are each methyl.
  • L2 is a substituted or unsubstituted hydrocarbon from 1 to 10 carbon atoms in length. In some embodiments, the hydrocarbon is unsubstituted. In some embodiments, the hydrocarbon is a linear, unsubstituted hydrocarbon, that is, -(CFhji- wherein i is an integer from 1 to 10, or from 1 to 8, or from 1 to 6, preferably from 1 to 4, or from 1 to 3, or is 1 or 2. In some embodiments of any of the embodiments described herein, L2 is a substituted or unsubstituted ethylene group. In some embodiments, L2 is an unsubstituted ethylene group (- CH2CH2-).
  • W is a hydrophobic group, such that the polymer features, in addition to the phosphatidyl choline-type moiety Z, a hydrophobic moiety that improves at least the contribution of the co-polymeric compound in reducing friction coefficient of hydrophobic surfaces, as is discussed in further detail hereinbelow.
  • hydrophobic describes a physical property of a material or a portion of a material (e.g., a chemical group in a compound) which does not form bond(s) with water and tend to associate with non-polar materials. Hydrophobic materials dissolve more readily in oil than in water.
  • hydrophobic group describes a chemical moiety that can interact via hydrophobic interactions with a compound (e.g., a surface as defined herein), depending on its chemical nature. It encompasses functional moieties that repel or fail to interact with water and/or other polar substances, and tend to associate with non-polar substances or solvents.
  • Hydrophobicity is commonly measured by its distribution behavior in a biphasic system: either liquid-liquid (e.g., partition coefficient in 1-octanol/water, as described herein) or solidliquid (retention on reversed-phase high-performance liquid chromatography (RP-HPLC) or thin- layer chromatography (TLC) system).
  • liquid-liquid e.g., partition coefficient in 1-octanol/water, as described herein
  • solidliquid retention on reversed-phase high-performance liquid chromatography (RP-HPLC) or thin- layer chromatography (TLC) system.
  • Hydrophilic, amphiphilic, and hydrophobic materials can be determined by the partition coefficient thereof.
  • a partition coefficient is the ratio of concentrations of a compound in the two phases of a mixture of two immiscible liquids at equilibrium, typically at room temperature. Normally, one of the solvents chosen is water while the second is hydrophobic such as n-octanol. The logarithm of the ratio of the concentrations of the un-ionized solute in the solvents is called LogP.
  • Hydrophobic materials are characterized by LogP higher than 1 ; hydrophilic materials are characterized by LogP lower than 1 ; and amphiphilic materials are characterized by LogP of about 1 (e.g., 0.8-1.2).
  • the Hansch-Fujita Scale measures the relative hydrophobicity of substituents by using a parameter 7t, which indicates how the hydrophobicity of a molecule changes when a substituent is introduced or modified.
  • the 7t parameter is determined according to the following equation:
  • Positive 7t values indicate that the substituent increases hydrophobicity (i.e., the substituted compound has a higher log P than the parent compound), and negative values indicate decrease in hydrophobicity.
  • W is selected capable of providing a co-polymeric compound characterized by LogP of at least 1, or at least 1.5, or at least 2, or at least 2.5, or at least 3, or at least 3.5, or at least 4, or at least 5, or more.
  • W is an alkyl. In some of any one of the embodiments described herein, W is Ci-4-alkyl, or Ci-3-alkyl (an alkyl of 1 to 4 or 1 to 3 carbon atoms in length). In some of any one of the embodiments described herein, W is an alkyl of at least 3 carbon atoms, for example, of from 3 to 10, or from 3 to 8, or from 3 to 6, or from 3 to 5, or of 3 or 4 carbon atoms.
  • W is a branched alkyl. In some of any one of the embodiments described herein, W is a branched alkyl of at least 3 carbon atoms, for example, for example, of from 3 to 10, or from 3 to 8, or from 3 to 6, or from 3 to 5, or of 3 or 4 carbon atoms.
  • Exemplary branched alkyls include, but are not limited to, isopropyl, isobutyl, isopentyl, amyl, neopentyl, sec-butyl, 2-methylbutyl, 3 -methylbutyl, 2-ethylhexyl, isooctyl, 3,3- dimethylbutyl, 3 -ethylpentyl, 4-methylhexyl, 3,3-dimethylpentyl, 2,2-dimethylhexyl, and 2-ethyl- 3-methylpentyl.
  • W is a hydrophobic moiety that is characterized by a value of the 7t parameter, according to the Hansch-Fujita Scale described hereinabove, which is in a range of from 0.5 to 1.2, or from 0.5 to 1.0, including any intermediate values and subranges therebetween.
  • W is a hydrophobic moiety that is characterized by a value of the 7t parameter, according to the Hansch-Fujita Scale described hereinabove, which is lower than 1.30, or is 1.20 or lower.
  • W is a hydrophobic moiety that is characterized by a value of the 7t parameter, according to the Hansch-Fujita Scale described hereinabove, which is lower than 1.10, or is lower than 1.00.
  • W is a hydrophobic moiety that is characterized by a value of the 7t parameter, according to the Hansch-Fujita Scale described hereinabove, within a range of from about 0.5 to about 1.2, or from about 0.5 to about 1.1, or from about 0.5 to about 1., or from about 0.6 to about 1.0, or from about 0.7 to about 1.0, or from about 0.8 to about 1.0 or from about 0.9 to about 1.0.
  • W is a hydrophobic moiety that is characterized by a value of the 7t parameter, according to the Hansch-Fujita Scale described hereinabove, within a range of from about 0.8 to about 1.20, or from about 0.9 to about 1.20, or from about 0.9 to about 1.10, including any intermediate values and subranges therebetween.
  • W is or comprises a branched alkyl of 3 or 4 carbon atoms in length. In some of any one of the embodiments described herein, W is isopropyl. Alternatively, W can be iso-butyl.
  • Ei and E2 each independently represents a terminal group.
  • the terminal groups can be an intrinsic terminal group, derived from the monomers used to form the co-polymeric compound.
  • Ei and E2 can each independently be hydrogen, alkyl, cycloalkyl, hydroxy, carboxy, amine, and the like.
  • Ei is hydrogen or alkyl (e.g., methyl).
  • E2 is hydrogen or alkyl (e.g., methyl).
  • Ei is or comprises a lipid moiety.
  • the lipid moiety is derived from a natural lipid (e.g., phosphatidylcholine, phosphatidylethanolamine, phosphatidylserine, phosphatidylinositol).
  • the lipid comprises a moiety derived from a bilayer-forming lipid (e.g., a glycerophospholipid).
  • moieties of a bilayer-forming lipid include sphingolipids (e.g., sphingomyelin), glycolipids (e.g., gangliosides), sterols (e.g., cholesterol), and fatty acids (e.g., oleic acid, palmitic acid).
  • sphingolipids e.g., sphingomyelin
  • glycolipids e.g., gangliosides
  • sterols e.g., cholesterol
  • fatty acids e.g., oleic acid, palmitic acid
  • lipid describes a class of naturally occurring molecules that are characterized by their hydrophobic or amphiphilic properties, which allow them to form structures such as membranes, vesicles, or droplets in aqueous environments.
  • Suitable examples of lipids include, without limitation, fatty acids, glycerides, phospholipids, sphingolipids, glycolipids, sterols, and other related compounds.
  • the lipid moiety is a moiety of a lipid which is a fatty acid, a monoglyceride, a diglyceride, a triglyceride, a glycerophospholipid, a sphingolipid, or a sterol.
  • the lipid is a glyceropho spholipid .
  • the lipid moiety comprises at least one fatty acid moiety (e.g., an acyl group derived from a fatty acid).
  • the fatty acid moiety may be derived from a saturated or unsaturated fatty acid.
  • the lipid moiety may consist of a fatty acid moiety, or be a monoglyceride moiety comprising one fatty acid moiety, a diglyceride moiety comprising two fatty acid moieties, or a triglyceride moiety comprising three fatty acid moieties.
  • fatty acid moieties which may optionally be comprised by the lipid moiety include, without limitation, lauroyl, myristoyl, palmitoyl, stearoyl, palmitoleoyl, oleoyl, and linoleoyl.
  • glycerophospholipids describes a class of lipids that consist of a glycerol backbone esterified to two fatty acid chains and a phosphate group.
  • the phosphate group is typically further linked to additional polar head groups, such as choline, ethanolamine, serine, or inositol, making glycerophospholipids amphiphilic molecules.
  • additional polar head groups such as choline, ethanolamine, serine, or inositol, making glycerophospholipids amphiphilic molecules.
  • Suitable examples of glycerophospholipids include, without limitation, a phosphatidyl ethanolamine, a phosphatidyl serine, a phosphatidyl glycerol and a phosphatidyl inositol.
  • variable n may be regarded as representing a number of backbone units (represented by the variable Yi) which are substituted by the pendant group represented by (-Li-Z)
  • variable m may be regarded as representing a number of backbone units (represented by the variable Y2) which are substituted by the pendant group represented by (-L2-W).
  • n is in a range of from 1 to 10,000, or from 10 to 1,000, or from 50 to 750, or from 100 to 500, or from 100 to 300, including any intermediate values and subranges therebetween.
  • a sum of n+m (i.e., the sum of variable n and variable m) may be regarded as representing the total number of backbone units in the polymeric backbone.
  • the sum of n+m is in a range of from 3 to 15,000, or from 3 to 5,000, or from 100 to 5,000, or from 300 to 5,000, or from 500 to 3,000, or from 1,000 to 3,000, or from 1,000 to 2,000, including any intermediate values and subranges therebetween. Higher values are also contemplated.
  • the number- average molecular weight (Mn) of the co-polymeric compound or the co-polymeric moiety as described herein, as determined by a gel-permeation chromatography (GPC) analysis is at least 500 or at least 1,000 or at least 5,000 or at least 10,000 or at least 20,000 grams/mol, and can be in a range of, for example, 1,000 to 50,000, or 1,000 to 30,000 or 1,000 to 25,000, or 5,000 to 50,000, or 5,000 to 30,000 or 5,000 to 25,000 or 10,000 to 50,000 or 10,000 to 30,000, or 1,000 to 20,000 or 1,000 to 10,000, or 1,000 to 5,000, grams/mol, including any intermediate values and subranges therebetween.
  • GPC gel-permeation chromatography
  • the percentage of backbone units represented by the variable Y 1 which are substituted by the pendant group represented by (- Li-Z) (as represented by the formula 100%*n/(n+m), the percentage of variable n from the sum of n+m) is in a range of from 0.01 % to 50 %, or from 1 % to 25 %, or from 5 % to 25 %, or from 7 % to 20 %, or from 10 % to 20 %, or from 10 % to 15 %, including any intermediate values and subranges therebetween.
  • the percentage of backbone units represented by the variable Y2 which are substituted by the pendant group represented by (-L2-W) (as represented by the formula 100%*m/(n+m), the percentage of variable m from the sum of n+m) is in a range of from 50 % to 99.99 %, or from 60 % to 99 %, or from 70 % to 99 %, or from 70 % to 95 %, or from 80 % to 95 %, or from 85 % to 90 %, including any intermediate values and subranges therebetween.
  • the co-polymeric compound comprises more than two different backbone units.
  • the different types of backbone units may differ in whether they comprise the pendant group (-Li-Z) according to any of the respective embodiments described herein (e.g., when n is at least 2), differ in the type of backbone unit Yi, and/or differ in the type of pendant group (-Li-Z).
  • backbone unit and “monomeric unit” are used interchangeably to describe the repeating units that are covalently bound to another and form the polymeric backbone chain.
  • the plurality (indicated by the variable n) of pendant groups (-Li-Z) attached to a plurality of backbone units Yi may be the same or different from one another (e.g., may differ in the identity of any one or more of A, B, Ri, R2, R3 and Li).
  • the backbone unit Yi in each of the Yi(-Li-Z) units may optionally be the same or different, while the Li and Z moieties are the same among the Yi(-Li-Z) units.
  • backbone units not substituted by the pendant group may optionally be the same as backbone unit Yi in each of the Yi(-Li-Z) units.
  • backbone units not substituted by the pendant group may optionally be different than backbone unit Yi in each of the Yi(-Li-Z) units (while optionally being the same among all backbone units not substituted by the pendant group).
  • the Li moiety in each of the Y i(-Li-Z) units may optionally be the same or different, while the backbone units Y 1 and the Z moieties are the same among the Yi(-Li-Z) units.
  • backbone units not substituted by the pendant group may optionally be the same as backbone unit Yi in each of the Yi(-Li-Z) units.
  • backbone units not substituted by the pendant group may optionally be different than backbone unit Yi in each of the Yi(-Li-Z) units (while optionally being the same among all backbone units not substituted by the pendant group).
  • the backbone units represented by the variable Yi which are substituted by the pendant group represented by (-Li-Z), and the backbone units represented by the variable Y2 which are substituted by the pendant group represented by (-L2-W), are distributed in the co-polymer randomly, in any order.
  • the Z moiety in each of the Y i(-Li-Z) units may optionally be the same or different, while the backbone units Y 1 and the Z moieties are the same among the Yi(-Li-Z) units.
  • backbone units not substituted by the pendant group may optionally be the same as backbone unit Yi in each of the Yi(-Li-Z) units.
  • backbone units not substituted by the pendant group may optionally be different than backbone unit Yi in each of the Yi(-Li-Z) units (while optionally being the same among all backbone units not substituted by the pendant group).
  • the co-polymeric compound comprises more than two different monomeric units.
  • the different types of monomeric unit may differ in whether they comprise the pendant group (-L2-W) according to any of the respective embodiments described herein (e.g., when m is at least 2), differ in the type of backbone unit Y2, and/or differ in the type of pendant group (-L2-W).
  • the plurality (indicated by the variable m) of backbone units Y2 substituted by the pendant group (-L2-W) may be the same as each other or different from each other.
  • the plurality (indicated by the variable m) of pendant groups (-L2-W) attached to a plurality of backbone units Y2 may be the same as each other or different from each other (e.g., may differ in the identity of any one or more of W and L2).
  • the backbone unit Y2 in each of the Y2(-L2-W) units may optionally be the same or different, while the L2 and W moieties are the same among the Y2(-L2-W) units.
  • backbone units not substituted by the pendant group may optionally be the same as backbone unit Y2 in each of the Y2(-L2-W) units.
  • backbone units not substituted by the pendant group may optionally be different than backbone unit Y2 in each of the Y2(-L2-W) units (while optionally being the same among all backbone units not substituted by the pendant group).
  • the L2 moiety in each of the Y2(-L2-W) units may optionally be the same or different, while the backbone units Y2 and the W moieties are the same among the Y2(-L2-W) units.
  • backbone units not substituted by the pendant group may optionally be the same as backbone unit Y2 in each of the Y2(-L2-W) units.
  • backbone units not substituted by the pendant group may optionally be different than backbone unit Y2 in each of the Y2(-L2-W) units (while optionally being the same among all backbone units not substituted by the pendant group).
  • the W moiety in each of the Y2(-L2-W) units may optionally be the same or different, while the backbone units Y2 and the W moieties are the same among the Y2(-L2-W) units.
  • backbone units not substituted by the pendant group may optionally be the same as backbone unit Y2 in each of the Y2(-L2-W) units.
  • backbone units not substituted by the pendant group may optionally be different than backbone unit Y2 in each of the Y2(-L2-W) units (while optionally being the same among all backbone units not substituted by the pendant group).
  • the co-polymeric compound further comprises a targeting moiety.
  • the targeting moiety can be attached to at least a portion of the monomeric units of the co-polymeric compound.
  • a “targeting moiety” refers to a moiety which is capable of bringing a compound (e.g., a compound according to some embodiments of the invention) into proximity with a selected substance and/or material (which is referred to herein as a "target").
  • the target is optionally a cell (e.g., a proliferating cell associated with the proliferative disease or disorder), wherein the proximity is such that the targeting moiety facilitates attachment and/or internalization of the compound into a target cell, and such that the compound may exert a therapeutic effect.
  • the targeting moiety can be attached (e.g., covalently) to one or more of the Yi backbone units, the Y2 backbone units, the Ei terminal group, the E2 terminal group, the Li linking group, the L2 linking group, the Z moiety and/or the W moiety.
  • a targeting moiety may optionally be comprised by a backbone unit Y 1 according to any of the respective embodiments described herein, a backbone unit Y2 according to any of the respective embodiments described herein, a linking moiety Li according to any of the respective embodiments described herein, a linking moiety L2 according to any of the respective embodiments described herein, moiety Z according to any of the respective embodiments described herein, moiety W according to any of the respective embodiments described herein, a terminal group Ei according to any of the respective embodiments described herein, and/or a terminal group E2 according to any of the respective embodiments described herein, for example, wherein a substituent according to any of the respective embodiments described herein comprises (and optionally consists of) the targeting moiety.
  • any one or more of R4-R6 and D comprises a targeting moiety according to any of the respective embodiments described herein (e.g., wherein any one or more of R4-R6 and D is a substituted group, comprising a substituent which is a targeting moiety), and optionally any one or more R4-R6 and D is a targeting moiety.
  • a targeting moiety according to any of the respective embodiments described herein (e.g., wherein any one or more of R4-R6 and D is a substituted group, comprising a substituent which is a targeting moiety), and optionally any one or more R4-R6 and D is a targeting moiety.
  • many other structures of monomeric units comprising a substituent which comprises (and optionally consist of) a targeting moiety are also encompassed by embodiments of the invention.
  • At least one type of monomeric unit comprises a targeting moiety (according to any of the respective embodiments described herein) and at least one type of monomeric unit does not comprise such a targeting moiety.
  • the distribution of a monomeric unit comprising a targeting moiety may be in accordance with any distribution described herein of a monomeric unit in a co-polymer moiety (e.g., random, alternating, periodic copolymer, and/or block copolymer).
  • a monomeric unit comprising a targeting moiety according to any of the respective embodiments described herein may optionally be prepared by preparing a monomer comprising a targeting moiety, and using the monomer to prepare a co-polymeric moiety as described herein (e.g., by co -polymerization of monomeric units according to any of the respective embodiments described herein) and/or by modifying a monomeric unit in a co-polymeric moiety subsequently to preparation of a co-polymeric moiety (e.g., by polymerization of monomers according to any of the respective embodiments described herein), using any suitable technique known in the art, including, but not limited to, techniques for conjugation.
  • the targeting moiety does not comprise a moiety represented by Formula II (according to any of the respective embodiments described herein).
  • a moiety represented by Formula II is capable of forming a bond with a target as described herein, the phrase "targeting moiety", in some embodiments, is to be understood as relating to a moiety distinct from a moiety represented by variable Z (represented by Formula II).
  • the pendant group represented by (-Li-Z) is selected so as not to form a bond with the target and/or so as not to include a structure and/or property of a targeting moiety as described herein in any one of the respective embodiments.
  • a targeting moiety comprising a nucleophilic group for example, an amine group - is capable of forming a bond (e.g., covalent bond) with a target
  • the variable Z (represented by Formula II) is optionally selected such that the depicted amine/ammonium group is a tertiary amine/ammonium (i.e., no more than one of R1-R3 is hydrogen) or quaternary ammonium (i.e., none of R1-R3 is hydrogen), preferably a quaternary ammonium (e.g., comprising a trimethylamino group, such as in phosphocholine).
  • Tertiary amine groups, and especially quaternary ammonium groups may be significantly less reactive nucleophilic groups than primary and secondary amine groups.
  • the targeting moiety comprises (and optionally consists of) at least one functional group capable of forming a covalent bond or non-covalent bond (preferably a selective non-covalent bond) with a substance and/or material (which is referred to herein as a "target"), e.g., at a surface of the target (e.g., a surface of a cell and/or tissue).
  • a substance and/or material which is referred to herein as a "target”
  • the phrase “functional group” encompasses chemical groups and moieties of any size and any functionality described herein (for example, any functionality capable of forming a covalent bond or non-covalent bond with a target).
  • a non-covalent bond according to any of the respective embodiments described herein may optionally be effected by non-covalent interactions such as, without limitation, electrostatic attraction, hydrophobic bonds, hydrogen bonds, and aromatic interactions.
  • the targeting moiety comprises a functional group capable of forming a non-covalent bond which is selective for the target, e.g., an affinity (e.g., as determined based on a dissociation constant) of the targeting moiety and/or functional group to the target is greater than an affinity of the of the targeting moiety and/or functional group to most (or all) other compounds capable of forming a non-covalent bond with the targeting moiety.
  • an affinity e.g., as determined based on a dissociation constant
  • the functional group(s) are capable of forming a covalent bond with one or more specific functional groups (e.g., hydroxy, amine, thiohydroxy and/or oxo groups) which are present on the target (e.g., a target according to any of the respective embodiments described herein).
  • specific functional groups e.g., hydroxy, amine, thiohydroxy and/or oxo groups
  • Examples of functional groups (in a targeting moiety) capable of forming a covalent bond with a target (according to any of the respective embodiments described herein) and the type of covalent bonds they are capable of forming include, without limitation: nucleophilic groups such as thiohydroxy, amine (e.g., primary or secondary amine) and hydroxy, which may form covalent bonds with, e.g., a nucleophilic leaving group (e.g., any nucleophilic group described herein), Michael acceptor (e.g., any Michael acceptor described herein), acyl halide, isocyanate and/or isothiocyanate (e.g., as described herein) in a target; nucleophilic leaving groups such as halo, azide (-N3), sulfate, phosphate, sulfonyl (e.g.
  • nucleophilic leaving groups such as halo, azide (-N3), sulfate, phosphate, sulf
  • A/- hydroxy succinimide (NHS) (e.g. NHS esters), sulfo-A ⁇ -hydroxysuccinimide, and anhydride, which may form covalent bonds with, e.g., a nucleophilic group (e.g., as described herein) in a target;
  • NHS hydroxy succinimide
  • anhydride which may form covalent bonds with, e.g., a nucleophilic group (e.g., as described herein) in a target;
  • Modification of a monomer (e.g., prior to polymerization or co-polymerization) or a monomeric unit of a co-polymeric moiety (e.g., subsequent to polymerization or copolymerization) to comprise any of the functional groups described herein may optionally be performed using any suitable technique for conjugation known in the art.
  • suitable technique for conjugation known in the art.
  • the skilled person will be readily capable of selecting a suitable technique for any given molecule to be modified.
  • dihydroxyphenyl refers to an aryl group (as defined herein) which is a phenyl substituted by two hydroxyl groups at any positions thereof.
  • the phenyl may optionally be substituted by additional substituents (which may optionally comprise additional hydroxyl groups), to thereby form a substituted dihydroxyphenyl group; or alternatively, the phenyl comprises no substituents other than the two hydroxyl groups, such that the dihydroxyphenyl group is an unsubstituted dihydroxyphenyl group.
  • the dihydroxyphenyl group is an ortho-dihydroxyphenyl (wherein the hydroxyl groups are attached to the phenyl at adjacent positions) or a para-dihydroxyphenyl (wherein the hydroxyl groups are attached to opposite sides of the phenyl ring), each being a substituted or unsubstituted dihydroxyphenyl.
  • the ortho-dihydroxyphenyl or para- dihydroxyphenyl is an unsubstituted dihydroxyphenyl.
  • a dihydroxyphenyl group according to any of the respective embodiments described herein may optionally bond covalently and/or non-covalently to a target according to any one or more attachment mechanism described for dihydroxyphenyl (catechol) groups in Lee et al. [PNAS 2006, 103:12999-13003], Brodie et al. [Biomedical Materials 2011, 6, 015014] and/or International Patent Application PCT/IL2015/050606, the contents of each of which are incorporated in their entirety, and especially contents regarding bonds formed by dihydroxyphenyl (catechol) groups to surfaces.
  • the functional group capable of forming a bond to a target is a functional group capable of forming a covalent bond with an amine group, optionally a primary amine group.
  • the target comprises on or more amino acids or amino acid residues, for example, a peptide or polypeptide of any length (e.g., at least two amino acid residues, for example, proteins), and the amine groups may optionally be lysine side chain amine groups and/or N-terminal amine groups.
  • the target comprises an extracellular matrix protein, for example, collagen.
  • the target comprises cartilage (e.g., articular cartilage).
  • the targeting moiety comprises (and optionally consists of) at least one functional group capable of forming a non- covalent bond with the target (e.g., as described herein in any one of the respective embodiments).
  • a functional group capable of forming a non-covalent bond with the target comprises (and optionally consists of) a polysaccharide and/or polypeptide (e.g., a protein and/or fragment thereof), wherein the target optionally comprises a ligand of the polysaccharide and/or polypeptide; and/or the target comprises a polysaccharide and/or polypeptide (e.g., a protein and/or fragment thereof) and the functional group capable of forming a non-covalent bond with the target is a ligand of the polysaccharide and/or polypeptide.
  • suitable polysaccharides and/or polypeptides, and ligands thereof include, without limitation: avidin or streptavidin as a polypeptide described herein, and biotin as a ligand thereof; a polysaccharide-binding polypeptide as a polypeptide described therein, and a complementary polysaccharide as a ligand thereof (or a complementary polysaccharide-binding polypeptide as a ligand of a polysaccharide described herein); a collagen-binding polypeptide as a polypeptide described therein, and a complementary collagen as a ligand thereof (or a collagen as a polypeptide described herein and a complementary collagen-binding polypeptide as a ligand thereof); a cell receptor expressed by a cell, and a ligand selectively bound by the receptor; an antibody towards any antigen (e.g., wherein the target described herein optionally comprises the antigen) or a fragment of such an antibody as a polypeptide
  • cell receptors expressed by a cell include, without limitation, receptors characteristic of a particular type of cell and/or tissue, and receptors overexpressed by a cancer cell.
  • the cell receptor or the cell is optionally a target described herein, and the targeting moiety optionally comprises any ligand of the receptor.
  • ligands include, without limitation, transferrin, a ligand of transferrin receptor which may optionally target transferrin receptor overexpressed by some cancer cells; keratinocyte growth factor (KGF or FGF7) which is specific for cells of epithelial origin, and may optionally target KGF receptor such as that overexpressed by an endometrial carcinoma or pancreatic carcinoma [Visco et al., Int J Oncol 1999, 15:431-435; Siegfried et al., Cancer 1997, 79:1166-1171]; and epidermal growth factor (EGF) which may optionally target an EGF receptor, optionally an erbB, such as that overexpressed by gliomas and endometrial carcinomas [Normanno et al., Curr Drug Targets 2005, 6:243-257]).
  • transferrin a ligand of transferrin receptor which may optionally target transferrin receptor overexpressed by some cancer cells
  • KGF or FGF7 keratinocyte growth factor
  • EGF
  • antibody encompasses any type of immunoglobin.
  • antibody mimetic encompasses any type of molecule, optionally a polypeptide, referred as such in the art capable of selectively binding an antigen (e.g., non-covalently).
  • Non-limiting examples of antibody mimetics include affibodies, affilins, affimers, affitins, alphabodies, anticalins, avimers, DARPins, Fynomers, Kunitz domain peptides, and monobodies, e.g., as described in Nygren [FEBS J 2008, 275:2668-2676], Ebersbach et al. [J Mol Biol 2007, 372:172-185], Johnson et al.
  • polysaccharide-binding polypeptide encompasses any polypeptide or oligopeptide (peptide chains of at least 2, and preferably at least 4 amino acid residues in length) capable of selectively binding (e.g., non-covalently) to a polysaccharide.
  • polysaccharide-binding polypeptides and their binding specificities will be known to the skilled person, and include short peptide sequences (e.g., from 4 to 50, optionally 4 to 20 amino acid residues in length), and longer polypeptides such as proteins or fragments (e.g., carbohydrate-binding modules and/or domains) thereof.
  • polysaccharide- binding polypeptide encompasses antibodies capable of specifically binding to a polysaccharide. Such antibodies will be available to the skilled person and/or the skilled person will know how to prepare such antibodies, using immunological techniques known in the art.
  • polysaccharide-binding polypeptides which may be used in some of any one of the embodiments of the invention include, without limitation, carbohydrate-binding modules (CBMs); and hyaluronic acid-binding peptides, polypeptides and/or modules (e.g., having a sequence as described in any of International Patent Application publication WO 2013/110056; International Patent Application publication WO 2014/071132; Barta et al. [Biochem J 1993, 292:947-949], Kohda et al. [Cell 1996, 86:767-775], Brisset & Perkins [FEBS Lett 1996, 388:211- 216], Peach et al.
  • CBMs carbohydrate-binding modules
  • hyaluronic acid-binding peptides, polypeptides and/or modules e.g., having a sequence as described in any of International Patent Application publication WO 2013/110056; International Patent Application publication WO 2014/071132;
  • CBMs which may be used in some of any one of the embodiments of the invention, include, without limitation, CBMs belonging to the families CBM3, CBM4, CBM9, CBM10, CBM17 and/or CBM28 (which may optionally be used to bind cellulose, e.g., in a cellulose-containing target); CBM5, CBM12, CBM14, CBM18, CBM19 and/or CBM33 (which may optionally be used to bind chitin and/or other polysaccharides comprising N- acetylglucosamine, e.g., in a chitin-containing target); CBM15 (which may optionally be used to bind hemicellulose, e.g., in a hemicellulose-containing target); and/or CBM20, CBM21 and/or CBM48 (which may optionally be used to bind starch and/or glycogen, e.g., in a starch-containing and/or glycogen-containing target).
  • collagen-binding polypeptide encompasses any polypeptide or oligopeptide (peptide chains of at least 2, and preferably at least 4 amino acid residues in length) capable of selectively binding (e.g., non-covalently) to a collagen (e.g., one type of collagen, some types of collagen, all types of collagen), including glycosylated polypeptides and oligopeptides such as peptidoglycans and proteoglycans.
  • collagen-binding polypeptides and their binding specificities will be known to the skilled person, and include short peptide sequences (e.g., from 4 to 50, optionally 4 to 20 amino acid residues in length), and longer polypeptides such as proteins or fragments (e.g., collagen-binding domains) thereof.
  • collagen-binding polypeptide encompasses antibodies capable of specifically binding to a collagen. Such antibodies will be available to the skilled person and/or the skilled person will know how to prepare such antibodies, using immunological techniques known in the art.
  • collagen-binding polypeptides which may be used in embodiments of the invention include, without limitation, collagen-binding proteins (e.g., decorin), fragments thereof and/or other polypeptides as described in U.S. Patent No. 8,440,618, Abd-Elgaliel & Tung [Biopolymers 2013, 100:167-173], Paderi et al. [Tissue Eng Part A 2009, 15:2991-2999], Rothenfluh et al. [Nat Mater 2008, 7 :248-254] and Helms et al. [J Am Chem Soc 2009, 131:11683- 11685] (the contents of each of which are incorporated in their entirety, and especially contents regarding particular collagen-binding polypeptides), for example, the sequence WYRGRL.
  • collagen-binding proteins e.g., decorin
  • the polymeric moiety does not comprise a targeting moiety described herein according to any of the respective embodiments.
  • a monomeric unit comprising phospholipid headgroups e.g., highly hydrated phosphatidylcholine (PC), 2-methacryloyloxyethylphosphorylcholine (MPC)), an N-substituted acrylamide monomeric unit (e.g., NIP AM), and an oxidizing agent (e.g., APS) are dissolved in a solvent (e.g., water).
  • a solvent e.g., water
  • the solution is deoxygenated (e.g., by nitrogen for 30 minutes).
  • a polymerization accelerator e.g., TMEDA
  • polymerization is carried out (e.g., at room temperature for 16 hours) under a deoxygenated atmosphere (e.g., nitrogen atmosphere).
  • the reaction mixture is dialyzed (e.g., against pure water for 48 hours), and dehydrated (e.g., using a freeze-drying technique), to thereby obtain the random co-polymeric compound.
  • the ratio between the monomers in the random co-polymeric compound is confirmed by comparing the respective signal from each monomer (e.g., the characteristic peak from each monomer) in a ’ H NMR spectrum of the co-polymeric compound.
  • the random co-polymeric compound represented by Formula I may be synthesized in accordance with other known methods for co-polymerization.
  • compositions and composite materials are Compositions and composite materials:
  • a composition comprising a hydrogel or a composite material containing a hydrogel.
  • the hydrogel has incorporated therein the co- polymeric compound as described herein in any of the embodiments.
  • hydrogel describes a three-dimensional fibrous network containing at least 20 %, typically at least 50 %, or at least 80 %, and up to about 99.99 % (by mass) water.
  • a hydrogel can be regarded as a material, which is mostly water, yet behaves like a solid or semi-solid due to a three-dimensional crosslinked solid-like network, made of natural and/or synthetic polymeric chains, within the liquid dispersing medium.
  • a hydrogel may contain polymeric chains of various lengths and chemical compositions, depending on the precursors used for preparing it.
  • the polymeric chains can be made of monomers, oligomers, block-polymeric units, which are inter-connected (crosslinked) by chemical bonds (covalent, hydrogen and ionic/complex/metallic bonds, typically covalent bonds).
  • the network-forming material comprises either small aggregating molecules, particles, or polymers that form extended elongated structures with interconnections (the crosslinks) between the segments.
  • the crosslinks can be in the form of covalent bonds, coordinative, electrostatic, hydrophobic, or dipole-dipole interactions or chain entanglements between the network segments.
  • crosslinking degree describes the percentage of crosslinks or interconnections between polymeric chains or other network segments within the hydrogel (i.e., the hydrogel-forming agents).
  • the degree of crosslinking affects the mechanical properties of the hydrogel, for example, a higher degree of crosslinking typically results in a stiffer hydrogel, while a lower degree of crosslinking typically allows for increased flexibility and water absorption.
  • the co-polymeric compound as described herein in any of the respective embodiments is incorporated in the hydrogel in a form of liposomes as described herein in any of the respective embodiments.
  • an amount of the co- polymeric compound is in a range of from 0.1 % to 50 %, or from 0.1 % to 25 %, or from 0.1 % to 10 %, or from 0.1 % to 5 %, by weight, of the total weight of the composition or the composite material, or the hydrogel, including any intermediate values and subranges therebetween.
  • a degree of crosslinking of the hydrogel is in a range of from 0.1 to 15, or from 1 to 15, or from 1 to 10, or from 1 to 5, or is 2, %, including any intermediate values and subranges therebetween.
  • the hydrogel is formed of at least one hydrogel-forming agent.
  • hydrogel-forming agent describes an agent that is capable of forming a hydrogel as defined herein.
  • hydrogel-forming agents include hydroxyethyl methacrylate (HEM A), hydroxyethyl acrylate (HE A), acrylamide (A Am), methacrylamide (MAAm), acrylic acid (AAc), methacrylic acid (MAAc), hexyl methacrylate, N- isopropylacrylamide (NIPAM)), N-isopropylmethacrylamide, polylactic acid, polyamide, polyethylene-terephthalate (PET), polyvinyl alcohol, polyurethane, polycaprolactone, polyethylene-glycol (PEG), polyethylene-glycol methacrylate (PEGMA), polyethyleneoxide dimethacrylate (PEOdMA), N,N-dimethacrylamide (nnDMAA), hyaluronic acid (HA), HA methacrylate, peptides, saccharides
  • the hydrogel comprises hydroxyethyl methacrylate (HEMA) and/or poly hydroxyethyl methacrylate (pHEMA) as hydrogel-forming agents.
  • HEMA hydroxyethyl methacrylate
  • pHEMA poly hydroxyethyl methacrylate
  • the composition or composite material as described in any one of the embodiments herein, and any combination thereof is in a dry form.
  • dry form it is meant that the composition or composite material comprises a minimal amount of moisture and/or solvents, for example, up to 10 %, or up to 5 %, or up to 4 %, or up to 3 %, or up to 2 %, or up to 1 %, water and/or other solvents by weight of the total weight of the composition or composite material.
  • Non-limiting examples for dry forms include solids, powders, and granulates. It is to be appreciated that in a dry form, the material is free from significant water content, making it easier to store and suitable for reconstitution or use in further formulations when water and/or other solvents are added.
  • the dry form of the composition or the composite material can be rehydrated.
  • the composition or composite material is characterized by a storage modulus G’ (at 1 Hz) of at least 10 MPa, and up to 1000 MPa, or of from 10 MPa to 500 MPa, or from 10 MPa to 100 MPa, or from 10 MPa to 50 MPa, or from 100 MPa to 1000 MPa, or from 100 MPa to 500 MPa, or from 500 MPa to 1000 MPa, including any intermediate values and subranges therebetween.
  • a storage modulus G’ at 1 Hz
  • the composition or composite material is characterized by a loss modulus G” (at 1 Hz) of at least 1,000 Pa, and up to 50,000 Pa, or from 1,000 Pa to 30,000 Pa, or from 1,000 Pa to 10,000 Pa, or from 1,000 Pa to 5,000 Pa, or from 5,000 Pa to 30,000 Pa, or from 5,000 Pa to 50,000 Pa, or from 5,000 Pa to 10,000 Pa, or from 10,000 Pa to 30,000 Pa, or from 10,000 Pa to 50,000 Pa, or from 30,000 Pa to 50,000 Pa, including any intermediate values and subranges therebetween.
  • a loss modulus G at 1 Hz
  • the composition or composite material is characterized by a sliding friction coefficient p lower than 0.05, or lower than 0.01, or lower than 0.001, or even lower, (e.g., lower than 0.0001), including any intermediate values and subranges therebetween. According to some of any of the embodiments described herein, the composition or composite material is characterized by such a sliding friction coefficient p on a polyethylene (hydrophobic) sphere.
  • the composition or composite material is characterized by a sliding friction coefficient p in a range of from 0.0001 to 0.01, or from 0.005 to 0.01, or from 0.001 to 0.01, or from 0.05 to 0.01, or from 0.0001 to 0.05, or from 0.005 to 0.05, or from 0.001 to 0.05, or from 0.005 to 0.001, or from 0.0001 to 0.005, including any intermediate values and subranges therebetween.
  • the composition or composite material is characterized by such a sliding friction coefficient p on a polyethylene (hydrophobic) sphere.
  • the composition or composite material is characterized by a storage modulus G’ (at 1 Hz) of at least 10 MPa, and by a loss modulus G” (at 1 Hz) of at least 1,000 Pa.
  • the composition or composite material is characterized by a storage modulus G’ (at 1 Hz) of from 10 MPa to 1000 MPa, or of from 10 MPa to 500 MPa, or from 10 MPa to 100 MPa, or from 10 MPa to 50 MPa, or from 100 MPa to 1000 MPa, or from 100 MPa to 500 MPa, or from 500 MPa to 1000 MPa, and by a loss modulus G’ ’ (at 1 Hz) of from 1,000 Pa to 50,000 Pa, or from 1,000 Pa to 30,000 Pa, or from 1,000 Pa to 10,000 Pa, or from 1,000 Pa to 5,000 Pa, or from 5,000 Pa to 30,000 Pa, or from 5,000 Pa to 50,000 Pa, or from 5,000 Pa to 10,000 Pa, or from 10,000 Pa to 30,000 Pa, or from 10,000 Pa to 50,000 Pa, or from 30,000 Pa to 50,000 Pa.
  • a storage modulus G’ at 1 Hz
  • the composition or composite material is characterized by a storage modulus G’ (at 1 Hz) of at least 10 MPa, and by a sliding friction coefficient p lower than 0.05 on a polyethylene (hydrophobic) sphere.
  • the composition or composite material is characterized by a storage modulus G’ (at 1 Hz) of from 10 MPa to 1000 MPa, or of from 10 MPa to 500 MPa, or from 10 MPa to 100 MPa, or from 10 MPa to 50 MPa, or from 100 MPa to 1000 MPa, or from 100 MPa to 500 MPa, or from 500 MPa to 1000 MPa, and by a sliding friction coefficient p of from 0.0001 to 0.01, or from 0.005 to 0.01, or from 0.001 to 0.01, or from 0.05 to 0.01, or from 0.0001 to 0.05, or from 0.005 to 0.05, or from 0.001 to 0.05, or from 0.005 to 0.001, or from 0.0001 to 0.005, on a polyethylene (hydrophobic) sphere, including any intermediate values and subranges therebetween.
  • G storage modulus G’
  • the composition or composite material is characterized by a loss modulus G” (at 1 Hz) of at least 1,000 Pa, and by a sliding friction coefficient lower than 0.05 on a polyethylene (hydrophobic) sphere.
  • the composition or composite material is characterized by a loss modulus G” (at 1 Hz) of from 1,000 Pa to 50,000 Pa, or from 1,000 Pa to 30,000 Pa, or from 1,000 Pa to 10,000 Pa, or from 1,000 Pa to 5,000 Pa, or from 5,000 Pa to 30,000 Pa, or from 5,000 Pa to 50,000 Pa, or from 5,000 Pa to 10,000 Pa, or from 10,000 Pa to 30,000 Pa, or from 10,000 Pa to 50,000 Pa, or from 30,000 Pa to 50,000 Pa, and by a sliding friction coefficient p of from 0.0001 to 0.01, or from 0.005 to 0.01, or from 0.001 to 0.01, or from 0.05 to 0.01, or from 0.0001 to 0.05, or from 0.005 to 0.05, or from 0.001 to 0.05, or from 0.005 to 0.001, or from 0.0001 to 0.005, on a polyethylene (hydrophobic) sphere, including any intermediate values and subranges therebetween.
  • a loss modulus G at 1 Hz
  • the composition or composite material is characterized by a storage modulus G’ (at 1 Hz) of at least 10 MPa, by a loss modulus G” (at 1 Hz) of at least 1,000 Pa, and by a sliding friction coefficient p lower than 0.05 on a polyethylene (hydrophobic) sphere.
  • the composition or composite material is characterized by a storage modulus G’ (at 1 Hz) of from 10 MPa to 1000 MPa, or of from 10 MPa to 500 MPa, or from 10 MPa to 100 MPa, or from 10 MPa to 50 MPa, or from 100 MPa to 1000 MPa, or from 100 MPa to 500 MPa, or from 500 MPa to 1000 MPa, and by a loss modulus G’ ’ (at 1 Hz) of from 1,000 Pa to 50,000 Pa, or from 1,000 Pa to 30,000 Pa, or from 1,000 Pa to 10,000 Pa, or from 1,000 Pa to 5,000 Pa, or from 5,000 Pa to 30,000 Pa, or from 5,000 Pa to 50,000 Pa, or from 5,000 Pa to 10,000 Pa, or from 10,000 Pa to 30,000 Pa, or from 10,000 Pa to 50,000 Pa, or from 30,000 Pa to 50,000 Pa, and by a sliding friction coefficient
  • the composition or composite material further comprises at least one additional agent, such as, but not limited to, a polymeric or co-polymeric compound, a hydrogel-forming polymer, a lipid, a sterol (e.g., cholesterol), a liposome-stabilizing agent, a labeling agent, a bioactive agent and/or a therapeutically active agent, as described in further detail herein.
  • additional agent such as, but not limited to, a polymeric or co-polymeric compound, a hydrogel-forming polymer, a lipid, a sterol (e.g., cholesterol), a liposome-stabilizing agent, a labeling agent, a bioactive agent and/or a therapeutically active agent, as described in further detail herein.
  • hydrogel-forming polymer refers to a polymeric compound, as described herein, which also serves as a hydrogel-forming agent, as described herein.
  • sterol encompasses all sterols derived from any source and includes synthetic sterols, animal-derived sterols, and plant-derived sterols (hereinafter termed “phytosterols”), as well as the saturated forms of sterols thereof (i.e., stands).
  • sterols as used herein encompasses both sterols and stands.
  • Sterols are steroids with a hydroxyl group at C3 (steroid alcohol) and most of the skeleton of cholestane (IUPAC Steroid Nomenclature, 1987). Additional carbon atoms may be present in the side chain, usually in the C17 position. In nature, sterols are found as C26-C30 steroid alcohols.
  • the liposome- stabilizing agent is a polymer.
  • the polymer can be poly(2-hydroxyethyl methacrylate) (pHEMA), alginate and/or hyaluronic acid (HA).
  • pHEMA poly(2-hydroxyethyl methacrylate)
  • HA hyaluronic acid
  • the concentration of the polymer in the liposome preparation solution ranges from 0.1 mg polymer per 1 ml of liposome suspension solution to 5 mg/ml, including any intermediate values and subranges therebetween.
  • biologically active agent or “bioactive agent” describes a chemical substance, which exhibits a biological or physiological activity in an organism.
  • a bioactive agent is a therapeutically active agent, such as described herein.
  • a process of preparing the composition or composite material as described herein, in any one of the embodiments thereof, and any combination thereof is effected by contacting an aqueous solution or suspension comprising a hydrogel-forming agent as described in any of the respective embodiments herein, and a crosslinking agent, with the co- polymeric compound as described in any of the respective embodiments herein, thereby obtaining the composition or composite material.
  • the aqueous solution or suspension further comprises an oxidizing agent.
  • the oxidizing agent is or comprises ammonium persulfate (APS). Any other suitable oxidizing agents are contemplated.
  • the aqueous solution or suspension further comprises a catalyst.
  • the catalyst is or comprises tetramethylethylenediamine (TMEDA). Without being bound to any particular theory, it is assumed that TMEDA acts as co-catalyst by accelerating radical formation of the oxidizing agent. Any other suitable catalysts are contemplated.
  • crosslinking agents that are usable in the context of these embodiments include, but are not limited to, poly(ethylene glycol)n dimethacrylate (EGDMA), N,N’- methylenebis(acrylamide) (MBAm), N,N'-methylenebis(2-methylacrylamide), methylene diacrylate, methylene bis(2-methylacrylate), diethylene glycol diacrylate, hexamethylene diacrylate, oxybis(methylene) bis(2-methylacrylate), oxybis(ethane-2,l-diyl) bis(2- methylacrylate).
  • EGDMA poly(ethylene glycol)n dimethacrylate
  • MAm methylenebis(acrylamide)
  • MAm N,N'-methylenebis(2-methylacrylamide)
  • methylene diacrylate methylene bis(2-methylacrylate)
  • diethylene glycol diacrylate diethylene glycol diacrylate
  • hexamethylene diacrylate oxybis(methylene) bis(2-methylacrylate)
  • crosslinking agents include, but are not limited to, glutaraldehyde, genipin, bisphenol A diglycidyl ether (DGEBA), toluene diisocyanate (TDI), polyethylene glycol diisocyanate (PEGDI), methylenebis(phenyl isocyanate) (MDI), sulfur dichloride, epichlorohydrin, tetraethyl orthosilicate (TEOS), and tris(hydroxymethyl) aminomethane (Tris). Any other crosslinking agent is contemplated.
  • DGEBA bisphenol A diglycidyl ether
  • TDI toluene diisocyanate
  • PEGDI polyethylene glycol diisocyanate
  • MDI methylenebis(phenyl isocyanate)
  • Tris tris(hydroxymethyl) aminomethane
  • the process further comprises dehydrating the composition or composite material, to thereby obtain the composition or composite material in a dry form as described herein.
  • the process may further comprise, subsequent to the dehydrating, rehydrating the composition or composite material, to thereby obtain a rehydrated form of the composition or the composite material as described herein.
  • dehydration and rehydration of the composition or composite material according to some of the present embodiments can be effected repeatedly as desired, substantially without affecting the friction coefficient of the composition or composite material.
  • the friction coefficient of the composition or the composite material is substantially the same as the friction coefficient of the rehydrated form of the composition or the composite material, for example, the friction coefficient of the composition or the composite material is up to 30 % lower or higher than the friction coefficient of the rehydrated form of the composition or the composite material. In some such embodiments, the friction coefficient of the composition or the composite material is up to 20 % lower or higher than the friction coefficient of the rehydrated form of the composition or the composite material. In some such embodiments, the friction coefficient of the composition or the composite material is up to 10 % lower or higher than the friction coefficient of the rehydrated form of the composition or the composite material.
  • the friction coefficient of the composition or the composite material is from 1 % to 30 %, or from 1 % to 20 %, or from 1 % to 10 %, or from 2 % to 30 %, or from 2 % to 20 %, or from 2 % to 10 %, or from 3 % to 30 %, or from 3 % to 20 %, or from 3 % to 10 %, or from 4 % to 30 %, or from 4 % to 20 %, or from 4 % to 10 %, or from 5 % to 30 %, or from 5 % to 20 %, or from 5 % to 10 %, lower or higher than the friction coefficient of the rehydrated form of the composition or the composite material, including any intermediate values and subranges therebetween.
  • the method of incorporating a co- polymeric compound as described herein in any of the respective embodiments and any combination thereof in a hydrogel may be effected such that the tensile strength of the resulting composition or composite material is augmented thereby rendering the composition or composite material useful in applications in which the neat hydrogel was not.
  • a hydrogel can be characterized by its degree of crosslinking, which is also correlated to its tensile strength and its ability to disperse and stabilize the co-polymeric compound
  • the method of lowering the friction coefficient of a hydrogel is effected, according to some of the embodiments presented herein, for hydrogels which are characterized by a molar percentage of the crosslinking agent that ranges from 0.00001 % to 50 % per hydrogel-forming agent total molar content.
  • a mol % of the crosslinking agent as defined herein to the hydrogelforming agent as defined herein is in a range of from 0.1 % to 50 %, from 0.5 % to 25 %, from 1 % to 10 % or from 1 % to 5 %, including any intermediate values and subranges therebetween.
  • composition or composite material prepared by the process as described herein in any of the respective embodiments.
  • a hydrogel may contain macromolecular polymeric and/or fibrous elements which are not chemically connected to the main crosslinked network but are rather mechanically intertwined therewith and/or immersed therein.
  • macromolecular fibrous elements can be woven (as in, for example, a mesh structure), or non-woven, and can, in some embodiments, serve as reinforcing materials of the hydrogel’s fibrous network.
  • Non-limiting examples of such macromolecules include polycaprolactone, gelatin, gelatin methacrylate, alginate, alginate methacrylate, chitosan, chitosan methacrylate, glycol chitosan, glycol chitosan methacrylate, hyaluronic acid (HA), HA methacrylate, and other non-crosslinked natural or synthetic polymeric chains and the likes.
  • the amount of such non-crosslinked additives is small and typically does not exceed 100 mg in 1 ml of the hydrogel-forming precursor solution.
  • hydrogel when used in combination with such macromolecular structures, it is referred to interchangeably as “a composite material comprising a hydrogel”, “a composite structure comprising a hydrogel”, “hydrogelcontaining composite material or structure”, “hydrogel-containing composite” or simply as “a hydrogel” or as a “composite”.
  • a composite material comprising a hydrogel may further comprise a woven mesh of fibers, non-woven fibers, a plurality of rods, a net etc.
  • Exemplary hydrogel/fiber-network composites are described, for example, in Moutos et al. Nat. Mater., 2007, 6(2), p. 162-7.
  • composition or composite material examples include, but are not limited to, a woven mesh of fibers, non-woven fibers, a plurality of rods, and a net.
  • a method of reducing a friction coefficient of a hydrogel or of a composition or composite material comprising a hydrogel as described herein in any of the respective embodiments According to some of any of the embodiments described herein, lowering a friction coefficient of a hydrogel or of a composition or composite material containing a hydrogel is effected by forming the hydrogel as described herein in any of the respective embodiments and in any combination thereof, in the presence of the co-polymeric compound as described herein in any of the respective embodiments and in any combination thereof.
  • forming the hydrogel in the presence of the co-polymeric compound is such that the co-polymeric compound is dispersed throughout the bulk of the hydrogel, thereby lowering the friction coefficient of the resulting composition compared to the friction coefficient of the neat hydrogel (not having co-polymeric compound dispersed therein).
  • the capacity to lower the friction coefficient of any given hydrogel is based on the premise that the neat hydrogel is such that the notion of having a friction coefficient is relevant thereto, namely that the neat hydrogel is hard enough to allow its friction coefficient to be measured or assessed by conventional means.
  • the method is applied to hydrogels or composite materials containing a hydrogel as described herein in any one of the respective embodiments.
  • the ability to lower the friction coefficient of a hydrogel depends to some extent on the amount of co-polymeric compound dispersed therein.
  • the method is effected by forming the hydrogel in the presence of the co-polymeric compound such that the amount of co- polymeric compound dispersed in the hydrogel is at least 0.00001 %, or at least 0.0001 %, or at least 0.001 %, or at least 0.01 %, or at least 0.1 %, or at least 1 %, as defined herein, including any intermediate values and subranges therebetween.
  • hydrogels which are characterized by a dynamic friction coefficient in aqueous media that ranges from 0.0001 to 0.2 under a pressure of at least 1.5 N. These values are not only low in comparison to neat hydrogels, but are notably low in absolute terms even in comparison to lubricated systems in aqueous media.
  • friction coefficient values presented in the Examples section that follows below and referred to hereinthroughout refer to dynamic friction coefficient, however, the general propensity to lower the friction coefficient of hydrogels is evident in both static and dynamic friction coefficients.
  • applying the method for lowering the friction coefficient of a hydrogel or a composite material containing a hydrogel, namely incorporating co-polymeric compound as described herein in any of the respective embodiments in a hydrogel as described herein in any of the respective embodiments reduces the friction coefficient of the neat hydrogel by a factor of at least 1.5, or at least 2, or at least 3, or at least 5, or at least 10, or at least 20, or at least 50, or at least 100, or at least 500, or at least 1000, or more, including any intermediate values and subranges therebetween.
  • the dynamic friction coefficient in aqueous medium of the hydrogel or composite material containing a hydrogel having the co- polymeric compound incorporated therein is reduced by a factor of at least 1.5, or at least 2, or at least 3, or at least 5, or at least 10, or at least 20, or at least 50, or at least 100, or at least 500, or at least 1000, or more, relative to the friction coefficient of the hydrogel not having the co-polymeric compound incorporated therein, including any intermediate values and subranges therebetween.
  • the low friction coefficient of the composition or composite material as described in herein in any of the embodiments is maintained under a wide range of loads and in various surface-to-surface combinations, including a gel-to-gel configuration, a gel-to-metal configuration, and even a gel-to-polyethylene, as these are described in detail herein and in the Examples section hereinbelow.
  • the low friction coefficient of the composition or composite material as described in herein in any of the embodiments is maintained under a wide range of loads and in gel-to -hydrophobic surface, as described herein in any of the respective embodiments.
  • the method further comprises dehydrating the hydrogel or composite material containing a hydrogel and rehydrating the hydrogel, as described herein.
  • the reduction in friction coefficient is maintained even after the hydrogel/co -polymeric compound composition or composite material has been dehydrated.
  • the low friction coefficient of the composition or composite material presented herein is substantially maintained after at least one dehydration-rehydration cycle, as described herein in any of the respective embodiments.
  • a co-polymeric compound, a composition or composite material as described herein in any of the embodiments and any combination thereof, and optionally a lipid bi-layer or liposome comprising the co-polymeric compound, as described herein, is useful for lubricating a surface, for example, a surface coated by a co-polymeric compound, a composition or composite material as described herein, and/or a lipid bi-layer or liposome comprising the co-polymeric compound, and/or contacted with a co-polymeric compound, or a composition or composite material comprising the co-polymeric compounds as described herein in any of the embodiments and any combination thereof, or a lipid bi-layer or liposome comprising the co-polymeric compound, as described herein.
  • the co-polymeric compound, or the composition or composite material as described herein in any of the embodiments and any combination thereof, and optionally a lipid bi-layer or liposome comprising the co- polymeric compound is for use in lubricating objects (e.g., inanimate objects such as stents, catheters, condoms).
  • lubricating objects e.g., inanimate objects such as stents, catheters, condoms.
  • At least a portion e.g., at least 10 %, or at least 25 %, or at least 50 %, or at least 75 %, or at least 90 %, or at least 95 %, or essentially all
  • a surface of the object is made of a hard metal surface, a hydrophobic surface, and/or a soft hydrogel surface, as those are described herein in any of the respective embodiments.
  • the object comprises in at least a portion thereof a hydrophobic surface as described herein in any of the respective embodiments.
  • objects that comprise a hydrophobic surface include medical devices (e.g., stents, catheters, implants, condoms), laboratory equipment (e.g., pipettes, beakers, flasks), cookware (e.g., nonstick pans, baking sheets), automotive parts (e.g., hydrophobic coatings on windshields, metal parts for rust prevention), electronics (e.g., waterproof casings, circuit boards), construction materials (e.g., hydrophobic tiles, insulation materials, tents), textiles (e.g., water-resistant fabrics, outdoor gear, jackets, tents), packaging materials (e.g., food packaging, containers), industrial machinery components (e.g., gears, bearings, seals), aerospace components (e.g., hydrophobic coatings on aircraft surfaces, landing gear), recreational gear (e.g., tents, sleeping bags, backpacks), storage
  • medical devices e.
  • a lubricant composition comprising the co-polymeric compound, or the composition or composite material according to any of the embodiments described herein, or, optionally a lipid bi-layer or liposome comprising the co-polymeric compound as described herein.
  • a "lubricant composition” refers to a composition intended for reducing a friction coefficient of a surface (e.g., according to a method described herein).
  • the lubricant composition comprises a carrier.
  • the carrier may optionally be a liquid carrier.
  • the carrier comprises an aqueous liquid.
  • the lubricant composition (or any other composition described herein comprising the co-polymeric compound, or the composition or composite material as described herein, or optionally a lipid bi-layer or liposome comprising the co-polymeric compound) further comprises a water-soluble polymer, optionally as part of the carrier.
  • water-soluble polymer encompasses polymers having a solubility of at least 1 gram per liter in an aqueous (e.g., water) environment at pH 7 (at 25 °C).
  • the water-soluble polymer has a solubility of at least 2 grams per liter (under the abovementioned conditions).
  • the solubility is at least 5 grams per liter.
  • the solubility is at least 10 grams per liter.
  • the solubility is at least 20 grams per liter.
  • the solubility is at least 50 grams per liter.
  • the solubility is at least 100 grams per liter.
  • the water-soluble polymer(s) may comprise at least one ionic polymer and/or at least one non-ionic polymer which are water-soluble as defined herein.
  • non-ionic polymer refers to a polymer which does not have a charged group.
  • non-ionic water-soluble polymers include, without limitation, polyvinylpyrrolidone (also referred to herein interchangeably as povidone and/or PVP) and polyethylene oxide (also referred to herein interchangeably as PEO, PEG and/or polyethylene glycol).
  • ionic polymer refers to polymers having at least one charged group, and encompasses polymers having a net negative charge (also referred to herein as “anionic polymers”), polymers having a net positive charge (also referred to herein as “cationic polymers”), and polymers having no net charge (also referred to herein as “zwitterionic polymers”), in an aqueous (e.g., water) environment at pH 7.
  • anionic polymers also referred to herein as “anionic polymers”
  • cationic polymers also referred to herein as “cationic polymers”
  • zwitterionic polymers polymers having no net charge
  • charged group refers to any functional group (e.g., a functional group described herein) which is ionic (as defined herein), including, for example, amine, carboxylic acid, sulfate, sulfonate, phosphate and phosphonate.
  • ionic as defined herein
  • each electric charge in a moiety or molecule is associated with one charged group, although a single charged group (e.g., non-substituted phosphate) may be associated with more than one electric charge of the same sign (e.g., a dianion, a dication).
  • the term “ionic” refers to the presence of an electric charge on at least one atom in a moiety and/or molecule (in at least 50 % of moieties and/or molecules in a population) in an aqueous medium (e.g., water) at pH 7.
  • the electric charge may be negative (anionic) or positive (cationic). If more than one electric charge is present, the electric charges may be negative (anionic) and/or positive (cationic), for example, both a negative and a positive charge may be present (zwitterionic).
  • ionic polymers include, without limitation, ionic polysaccharides, such as hyaluronic acid, chondroitin sulfate, alginic acid, xanthan gum, chitosan and N-alkyl chitosan derivatives.
  • a method of lowering a friction coefficient of a surface of a substrate comprising applying to the surface the co-polymeric compound, or the composition or composite material according to any of the respective embodiments described herein, or optionally a lipid bi-layer or liposome comprising the co-polymeric compound, as described herein.
  • the method is effected by contacting the surface with the co-polymeric compound, or the composition or composite material according to any of the respective embodiments described herein, or optionally a lipid bi-layer or liposome comprising the co-polymeric compound as described herein, or contacting the surface with a lubricant composition according to any of the respective embodiments described herein, which may further comprise a carrier.
  • the substrate is a physiological substrate as defined herein.
  • the substrate is a medical device (e.g. an implantable medical device, e.g., as described herein).
  • the lubrication is optionally effected according to any of the embodiments described in WO 2015/193887 and/or WO 2015/193888, which are incorporated herein by reference (especially in respect to methods and compositions for lubricating a surface), with the proviso that at least a portion of the co-polymeric compound, or the composition or composite material, or optionally a lipid bi-layer or liposome comprising the co-polymeric compound, is in accordance with any of the embodiments described herein.
  • the method further comprises contacting the surface with a water- soluble polymer (e.g., according to any of the respective embodiments described herein), optionally prior to and/or concomitantly with contacting the surface with the co-polymeric compound, or the composition or composite material as described herein, or optionally with a lipid bi-layer or liposome comprising the co-polymeric compound as described herein.
  • a water- soluble polymer e.g., according to any of the respective embodiments described herein
  • the method is effected by contacting the surface with a co-polymeric compound, or a composition or composite material as described herein in any of the respective embodiments, or optionally with a lipid bi-layer or liposome comprising the co-polymeric compound, as described herein, and the water-soluble polymer (optionally a lubricant composition comprising the water-soluble polymer according to any of the respective embodiments described herein), optionally in combination with an aqueous liquid.
  • the surface is a hard metal surface (e.g., stainless steel surface).
  • the surface is a hydrophobic surface (e.g., a polyethylene surface).
  • the surface is a soft hydrogel surface (e.g., a pHEMA surface).
  • the surface is a hydrophilic surface.
  • hydrophobic hydrogel surface is PDMS
  • hydrophilic hydrogel surface is polyvinyl alcohol (PVA). Please ensure these are included below
  • hard metal surface encompasses a surface that comprises, in at least a portion thereof (e.g., at least 10 %, or at least 25 %, or at least 50 %, or at least 75 %, or at least 90 %, or more) a metal specie.
  • metal species include metal particles, metal oxides (e.g., anodized surfaces), metal carbides, metal nitrides, metal sulfides, metal phosphides, metal films, metal nanostructures (e.g., metal NPs, metal nanowires), metal coatings, and alloys (e.g., stainless steel surface).
  • soft hydrogel surface encompasses a surface which is or comprises a hydrogel as described herein.
  • Soft hydrogel surfaces include hydrogels made from at least hydrogel-forming agent as described herein, such as pHEA, pAAm, pMAAm, pAAc, pNIPAM, and PEG-based hydrogels, and any oligomer, polymer and/or copolymer thereof.
  • hydrophilic surfaces include surfaces made of hydrophilic or amphiphilic polymers or co-polymeric, including, for example, polyvinyl alcohol (PVA), polyethylene Glycol (PEG), polyacrylamides (PAM), polyacrylic Acid (PAA), poly(N-vinylpyrrolidone) (PVP), cellulose and cellulose derivatives (e.g., hydroxyethyl Cellulose), and any co-polymers and combinations thereof.
  • PVA polyvinyl alcohol
  • PEG polyethylene Glycol
  • PAM polyacrylamides
  • PAA polyacrylic Acid
  • PVP poly(N-vinylpyrrolidone)
  • cellulose and cellulose derivatives e.g., hydroxyethyl Cellulose
  • hydrophobic surface encompasses a surface that is hydrophobic and/or is or comprises a hydrophobic material, as those are described herein.
  • hydrophobic materials include hydrophobic polymers and non- polymeric hydrophobic materials.
  • non-polymeric hydrophobic materials which are usable as surfaces include, but are not limited to, waxes, fatty acids, graphene, ceramic coatings (e.g., silicon carbide, alumina), , alkylated surfaces (e.g., silanized glass, alkylated cellulose), and metals coated with hydrophobic agents (e.g., silane-coated aluminum).
  • ceramic coatings e.g., silicon carbide, alumina
  • alkylated surfaces e.g., silanized glass, alkylated cellulose
  • metals coated with hydrophobic agents e.g., silane-coated aluminum
  • hydrophobic polymers which are usable as surfaces include, but are not limited to, silicones (e.g., PDMS), fluoropolymers such as polytetrafluoroethylene (PTFE; Teflon®) or poly vinylidene fluoride (PVDF), polyethylenes, polypropylenes, polystyrenes, polyvinyl chloride (PVC), poly(methyl methacrylate) (PMMA), polycarbonates (PC), polyurethanes, polyimides, and non-polymeric materials coated with hydrophobic polymers (e.g., fluoropolymer-coated stainless steel).
  • silicones e.g., PDMS
  • fluoropolymers such as polytetrafluoroethylene (PTFE; Teflon®) or poly vinylidene fluoride (PVDF)
  • PVC polyvinyl chloride
  • PMMA poly(methyl methacrylate)
  • PC polycarbonates
  • PC polyurethanes
  • the surface is a contact lens surface.
  • the contact lens comprises a hydrogel surface.
  • the contact lens comprises a hydrogel surface and a rigid center.
  • the contact lens consists essentially of a hydrogel.
  • the hydrogel comprise any material known in the art for use in contact lens hydrogels.
  • hydrogel materials include, without limitation, alphafilcon A, asmofilcon A, balafilcon A, bufilcon A, comfilcon A, crofilcon, deltafilcon A, dimefilcon, droxifilcon A, enfilcon A, etafilcon A, galyfilcon A, hefilcon A, hefilcon B, hilafilcon A, hilafilcon B, hioxifilcon A, hioxifilcon D, isofilcon, lidofilcon A, lidofilcon B, lotrafilcon B, mafilcon, methafilcon A, methafilcon B, narafilcon A, narafilcon B, ocufilcon A, ocufilcon B, ofilcon A, omafilcon A, perfilcon, phemfilcon A, polymacon, scafilcon A, senofilcon A, surfilcon, tefilcon, tetrafilcon A, tetraf,
  • the hydrogel comprises a polymer consisting of poly(2-hydroxyethyl methacrylate) and/or a silicone.
  • the polymer comprises a silicone.
  • Such polymers may optionally comprise small amounts of additional monomers (e.g., crosslinking monomers) copolymerized with the 2- hydroxyethyl methacrylate or silicone monomer.
  • 2-hydroxyethyl methacrylate may optionally be copolymerized with vinyl pyrrolidone, methyl methacrylate, methacrylic acid (an anionic monomer), ethylene glycol dimethacrylate (a crosslinking monomer) and/or 3- (ethyldimethyl-ammonium)propyl methacrylamide (a cationic monomer) in a contact lens hydrogel.
  • the co-polymeric compound, the liposome, or the composition or composite material as described herein in any of the embodiments and any combination thereof is for use in lubricating a biological tissue (e.g., when applied to an external surface of the tissue via, for example, adsorption from solution).
  • the surface is a physiological surface
  • a carrier used with the co-polymeric compound, or the composition or composite material as described herein is a physiologically acceptable carrier, as described herein.
  • a surface for which a friction coefficient is reduced according to any of the respective embodiments described herein is an articular surface of a synovial joint.
  • the method of reducing a friction coefficient of a surface is for use in the treatment of a synovial joint disorder associated with an increased friction coefficient of an articular surface in the synovial joint.
  • the co-polymeric compound, or the composition or composite material as described herein in any of the respective embodiments and any combination thereof, or of a lipid bi-layer or liposome made of the co- polymeric compound as described herein is for use in the treatment of a synovial joint disorder associated with an increased friction coefficient of an articular surface in the synovial joint.
  • synovial joint disorders associated with an increased friction coefficient of an articular surface include, without limitation, arthritis, traumatic joint injury, locked joint (also known in the art as joint locking), and joint injury associated with surgery.
  • the arthritis is osteoarthritis, rheumatoid arthritis and/or psoriatic arthritis.
  • the locked joint is associated with osteochondritis dissecans and/or synovial osteochondromatosis.
  • the joint injury associated with surgery described herein may optionally be associated with surgery which directly inflicts damage on an articular surface (e.g., by incision), and/or surgery which damages an articular surface only indirectly.
  • surgery which repairs or otherwise affects tissue in the vicinity of the joint e.g., ligaments and/or menisci
  • the traumatic joint injury described herein may optionally be injury caused directly by trauma (e.g., inflicted at the time of the trauma) and/or injury caused by previous trauma (e.g., a post-traumatic injury which develops sometime after the trauma).
  • the co-polymeric compound, or the composition or composite material as described herein in any of the embodiments and any combination thereof, or optionally or of a lipid bi-layer or liposome made of the co- polymeric compound as described herein is for use in the treatment and/or alleviation of osteoarthritis (OA) (e.g., as biolubricants for intra- articular administration).
  • OA osteoarthritis
  • the co-polymeric compound, or the composition or composite material as described herein in any of the respective embodiment, or a lipid bi-layer or liposome made of the co-polymeric compound as described herein, may optionally be administered as part of a composition (e.g., a solution) that comprises a physiologically acceptable carrier, for example an aqueous carrier which is a physiologically acceptable carrier.
  • a composition e.g., a solution
  • a physiologically acceptable carrier for example an aqueous carrier which is a physiologically acceptable carrier.
  • physiologically acceptable carrier refers to a carrier or a diluent that does not cause significant irritation to a subject upon administration in the intended manner, and does not abrogate the activity and properties of the co-polymeric compound in the composition (e.g., their ability to reduce a friction coefficient of a surface, as described herein in any one of the respective embodiments).
  • carriers are: propylene glycol, saline, emulsions and mixtures of organic solvents with water, as well as solid (e.g., powdered) and gaseous carriers.
  • Solutions according to any one of the embodiments of the present invention may be manufactured by processes well known in the art, e.g., by means of conventional mixing or dissolving processes.
  • Solutions for use in accordance with the present invention thus may be formulated in conventional manner using one or more physiologically acceptable carriers, which facilitate processing of the co-polymeric compounds or the composition or composite material into preparations which can be used pharmaceutically. Proper formulation is dependent upon the route of administration chosen.
  • the co-polymeric compound, the liposome, or the composition or composite material as described herein may be formulated in aqueous solutions, preferably in physiologically compatible buffers such as Hank’s solution, Ringer’s solution, histidine buffer, or physiological saline buffer with or without organic solvents such as propylene glycol, polyethylene glycol.
  • physiologically compatible buffers such as Hank’s solution, Ringer’s solution, histidine buffer, or physiological saline buffer with or without organic solvents such as propylene glycol, polyethylene glycol.
  • the co-polymeric compound, the liposome, or the composition or composite material as described herein may be formulated for parenteral administration, e.g., by bolus injection or continuous infusion.
  • Formulations for injection may be presented in unit dosage form, e.g., in ampoules or in multi-dose containers with optionally, an added preservative.
  • the compositions may be suspensions, solutions or emulsions in oily or aqueous vehicles, and may contain formulatory agents such as suspending, stabilizing and/or dispersing agents.
  • the co-polymeric compound, or the composition or composite material as described herein, or a lipid bi-layer or liposome made of the co-polymeric compound as described herein may be formulated as an aqueous solution per se.
  • the solution may be in the form of a suspension and/or emulsions (e.g., the aqueous phase of a suspension or water-in-oil, oil-in-water or water-in-oil-in-oil emulsion), for example, in order to increase the viscosity of the formulation.
  • Aqueous injection suspensions may contain substances, which increase the viscosity of the suspension, such as sodium carboxymethyl cellulose, sorbitol or dextran.
  • the suspension may also contain suitable stabilizers or agents, which increase the solubility of the co- polymeric compound, the liposome, or the composition or composite material as described herein, for example, to allow for the preparation of highly concentrated solutions.
  • the co-polymeric compound, the liposome, or the composition or composite material as described herein may be in powder form for constitution with a suitable vehicle, e.g., sterile, pyrogen-free water, before use.
  • a suitable vehicle e.g., sterile, pyrogen-free water
  • solutions may be formulated wherein the co-polymeric compound, the liposome, or the composition or composite material as described herein in any of the respective embodiments are contained in an amount effective to achieve the intended purpose, for example, an amount effective to prevent, alleviate or ameliorate symptoms of a disorder in the subject being treated.
  • the dosage may vary depending upon the dosage form employed, the route of administration utilized, and the location of administration (e.g., the volume and/or surface of the region contacted with the co-polymeric compound, the liposome, or the composition or composite material as described herein).
  • compositions to be administered will, of course, be dependent on the subject being treated, the severity of the affliction, the manner of administration, the judgment of the prescribing physician, etc.
  • compositions e.g., solutions
  • a pack or dispenser device such as an FDA (the U.S. Food and Drug Administration) approved kit, which may contain one or more unit dosage forms containing the active ingredient(s) (e.g., the co-polymeric compounds or the composition or composite material as described herein).
  • the pack may, for example, comprise metal or plastic foil, such as, but not limited to a blister pack.
  • the pack or dispenser device may be accompanied by instructions for administration.
  • the pack or dispenser may also be accompanied by a notice associated with the container in a form prescribed by a governmental agency regulating the manufacture, use or sale of pharmaceuticals, which notice is reflective of approval by the agency of the form of the compositions for human or veterinary administration.
  • Such notice for example, may be of labeling approved by the U.S. Food and Drug Administration for prescription drugs or of an approved product insert.
  • Compositions comprising the co-polymeric compound, the liposome, or the composition or composite material as described herein (optionally with a water- soluble polymer described herein), as described herein in any one of the respective embodiments, formulated in a physiologically acceptable carrier may also be prepared, placed in an appropriate container, and labeled for treatment of an indicated condition or diagnosis, as is detailed herein.
  • a co-polymeric compound, or a composition or composite material as described herein, or optionally a lipid bi-layer or liposome made of the co-polymeric compound as described herein, may optionally or in addition be useful for inhibiting adhesion, biofouling and/or biofilm formation on a surface, for example, a surface coated by a composition or composite material as described herein, and/or contacted with a composition or composite material as described herein.
  • a method of inhibiting adsorption of a biofouling-promoting agent on a surface of a substrate is effected by contacting the substrate with a co-polymeric compound, or a composition or composite material according to any of the respective embodiments, or optionally with a lipid bi-layer or liposome made of the co-polymeric compound as described herein,.
  • biofouling-promoting agent refers to an agent whose presence facilitates formation and/or participates in formation of a biofilm (as defined herein) on a substrate surface.
  • An agent is considered to facilitate formation of a biofilm on a substrate surface when a presence of the agent enhances formation of a biofilm on a substrate surface as compared to formation of a biofilm on the same substrate surface in an absence of the agent.
  • An agent is considered to participate in formation of a biofilm on a substrate surface when the biofilm formed on the surface comprises the agent as a portion of the biofilm.
  • an agent is identified as a biofouling-promoting agent by comparing growth (e.g., over the course of 1, 2, 3, 4, 5, 6 or 7 days) of a biofilm (e.g., P. aeruginosa) on the surface in the presence of an aqueous liquid (e.g., water or broth, optionally at 37 °C) and the agent, to growth of a biofilm (under the same conditions) on the surface in the presence of the same aqueous liquid (e.g., water or broth) without the agent.
  • the agent is optionally mixed within the aqueous liquid, or alternatively, adsorbed onto the surface prior to exposure of the surface to the aqueous liquid.
  • the growth of the biofilm is considered as the biofilm load at the end of the growth period (e.g., 1, 2, 3, 4, 5, 6 or 7 days) minus the initial biofilm load.
  • the measurement is performed such that the initial biofilm is substantially zero (e.g., absent or at least undetectable), for example, the microorganism is in a planktonic form, such that growth of the biofilm is considered as the biofilm load at the end of the growth period.
  • biofilm load is defined as an area of the biofilm.
  • biofilm load is defined as a mass and/or volume of the biofilm.
  • biofilm load is defined as a number of cells in the biofilm.
  • the biofilm load may optionally be determined using any technique known in the art for detecting and quantifying an amount of cells and/or microorganisms in a biofilm.
  • an agent is considered a biofouling-promoting agent if the growth of a biofilm in its presence is at least 10 % higher, or at least 20 % higher, or at least 50 % higher, or at least 100 % higher (i.e., two-fold), or more, than the growth of a biofilm in the absence of the agent, including any intermediate values and subranges therebetween.
  • biofouling-promoting agents include, without limitation, a biofoulingpromoting protein and a biofouling-promoting polysaccharide, that is, any protein or polysaccharide which is a biofouling-promoting agent as defined herein.
  • the method is considered as being capable of inhibiting adsorption of a biofouling-promoting agent when the method is capable of inhibiting adsorption of a selected biofouling-promoting agent (e.g., the selected agent is considered representative of biofouling -promoting agents in general).
  • the selected biofouling-promoting agent is a protein.
  • the selected protein is an antibody which does not exhibit any specific affinity to the substrate (e.g., an anti-IgG antibody).
  • biofilm refers to an aggregate of living cells which are stuck to each other and/or immobilized onto a surface as colonies. The cells are frequently embedded within a self-secreted matrix of extracellular polymeric substance (EPS), also referred to as "slime”, which is a polymeric sticky mixture of nucleic acids, proteins and polysaccharides.
  • EPS extracellular polymeric substance
  • the living cells forming a biofilm can be cells of a unicellular microorganism, including prokaryotes (e.g., bacteria, archaeal microorganisms) and eukaryotes such as fungi and protists (e.g., algae, euglena, protozoa, dinoflagellates, apicomplexa, trypanosomes, amoebae) and the like; or cells of multicellular organisms, in which case the biofilm can be regarded as a colony of cells (as in the case of the unicellular organisms) or as a lower form of a tissue.
  • prokaryotes e.g., bacteria, archaeal microorganisms
  • eukaryotes such as fungi and protists
  • fungi and protists e.g., algae, euglena, protozoa, dinoflagellates, apicomplexa, trypanosomes, am
  • the substrate may be any substrate described herein, and encompasses any surface, structure, product or material which can support, harbor or promote the growth of a microorganism.
  • the substrate is optionally a portion of an object (e.g., an article-of-manufacture) which can support, harbor or promote the growth of a microorganism.
  • Such a portion of an object may span only a portion of an area of the object, such that a surface of the substrate represents only a portion of a surface of the object (e.g., a portion most likely to support, harbor or promote the growth of a microorganism); and/or span only a portion of the thickness of the object (e.g., along an axis perpendicular to a surface of the substrate and object), such that the substrate does not include the entire volume of the object lying underneath a surface of the substrate (which may represent the entire surface of the object or only a portion of the surface of the object).
  • Non-limiting examples include the inner walls of a storage container (e.g., a box, a can) and/or conduit (e.g., a tubes, a pipe) for an organic product susceptible to spoilage associated with biofouling, for example, food and/or drink (e.g., a food container, a water pipe), surfaces intended to come into contact with such an organic product (e.g., agricultural and/or food processing machinery, a kitchen surface, waterpurification equipment), and surfaces exposed to moisture (e.g., bathroom walls, water system components, outer surfaces of housing exposed to rain, surfaces in the vicinity of water leakage).
  • a storage container e.g., a box, a can
  • conduit e.g., a tubes, a pipe
  • an organic product susceptible to spoilage associated with biofouling for example, food and/or drink (e.g., a food container, a water pipe)
  • surfaces intended to come into contact with such an organic product e.g., agricultural and/or food processing machinery
  • the substrate is a medical device or any other device which is intended for contacting a living tissue, as defined herein.
  • the inhibition of adsorption described herein is for reducing adhesion of pathogenic microorganisms (e.g., any biofilm-forming microorganism described herein which is potentially pathogenic) to a medical device (e.g., any medical device described herein).
  • adsorption of the biofouling-promoting agent (any biofouling-promoting agent described herein) on the surface of the substrate subjected to a method described herein (according to any of the respective embodiments) is reduced by at least 10 % relative to adsorption on the surface of the substrate in the absence of the co-polymeric compound, the liposome, or the composition or composite material as described herein in any of the respective embodiments and any combination thereof.
  • biofilm load is defined as an area of the biofilm.
  • biofilm load is defined as a mass and/or volume of the biofilm. In some embodiments of any of the embodiments described herein, biofilm load is defined as a number of cells in the biofilm.
  • the biofilm load may optionally be determined using any technique known in the art for detecting and quantifying an amount of cells and/or microorganisms in a biofilm.
  • the time period of biofilm formation, after which biofilm load is determined is in determined in accordance with the biofilm load, for example, the time period being a time period after which a biofilm covers 100 %, 50 %, or any other pre-determined percentage of the area of the substrate in the absence of inhibition of biofilm formation by contact with the co-polymeric compound, the liposome, or the composition or composite material as described herein.
  • biofilm formation inhibition may be considered to result in a reduction of 40 % (i.e., (50 % - 30 %)/50 %) in biofilm formation.
  • the phrase “upon contact with the agent” means that in addition to the biofilmpromoting conditions, the agent is also present (e.g., in the aqueous liquid containing the cells).
  • a method of inhibiting biofilm formation on a surface of a substrate as defined herein in any embodiment and any combination of embodiments, the method comprising contacting the substrate with a co- polymeric compound, a liposome, or a composition or composite material as described herein in any of the respective embodiments and any combination thereof.
  • “inhibiting biofilm formation” refers to the prevention of formation of a biofilm; and/or to a reduction in the rate of buildup of a biofilm; and/or to a reduction in the mass of a biofilm, the area or the volume of the biofilm, or in the number of cells forming the biofilm.
  • the inhibition of adsorption described herein is for reducing adhesion of pathogenic microorganisms (e.g., any biofilm-forming microorganism described herein which is potentially pathogenic) to a medical device. Such a reduction may result in inhibiting biofilm formation, as defined in some embodiments herein.
  • pathogenic microorganisms e.g., any biofilm-forming microorganism described herein which is potentially pathogenic
  • biofilm formation on the surface of the substrate subjected to a method described herein is reduced by at least 10 % relative to biofilm formation on the surface of the substrate in the absence of the co-polymeric compound, the liposome, or the composition or composite material as described herein.
  • biofilm formation is reduced by at least 20 %.
  • biofilm formation is reduced by at least 30 %.
  • biofilm formation is reduced by at least 40 %.
  • biofilm formation is reduced by at least 50 %.
  • biofilm formation is reduced by at least 60 %.
  • biofilm formation is reduced by at least 70 %.
  • biofilm formation is reduced by at least 80 %.
  • biofilm formation is reduced by at least 90 %.
  • the reduction in biofilm formation is optionally determined by measuring a biofilm load (in accordance with any of the respective embodiments described herein) for a biofilm of a cell (e.g., P. aeruginosa) on each surface after being subjected to biofouling-promoting conditions, as defined herein (e.g., over the course of 1, 2, 3, 4, 5, 6 or 7 days, or any other time period as described herein).
  • a biofilm load in accordance with any of the respective embodiments described herein
  • a biofilm of a cell e.g., P. aeruginosa
  • any of the embodiments described herein relating to inhibition of biofilm formation and/or biofouling may optionally be effected by a composition which is essentially the same as a lubricant composition according to any of the respective embodiments described herein (although optionally identified for inhibition of biofilm formation and/or biofouling rather than for lubrication).
  • the inhibition is optionally effected according to any of the embodiments described in Israel Patent Application No. 234929 and/or WO 2016/051413, which are incorporated herein by reference (especially in respect to methods and compositions for inhibiting adhesion, biofilm formation and/or biofouling on a surface), with the proviso that at least a portion of the co- polymeric compounds, the liposome, or the composition or composite material used are in accordance with any of the embodiments described herein.
  • inhibition of the adsorption of the biofouling-promoting agent is substantially unchanged after at least one dehydration- rehydration cycle of the hydrogel.
  • an article - of-manufacturing comprising the co-polymeric composition, or the composition or composite material as described herein in any of the respective embodiments, or optionally a lipid bi-layer or liposome made of the co-polymeric compound as described herein.
  • article-of-manufacturing include, but are not limited to, an implantable medical device, a drug-delivery system, a solid body, a disc, a fiber, a fabric, a tube, a film, a rod, a ring, a tubular mesh, and any combination thereof.
  • the co-polymeric composition, or the composition or composite as described herein in any of the respective embodiments, or optionally a lipid bi-layer or liposome made of the co-polymeric compound as described herein is for use in replacing missing or damaged cartilage in a living organism suffering from a medical condition associated with loss of or damaged cartilage.
  • a medical condition associated with loss of or damaged cartilage Non-limiting examples of the medical conditions include skeletal joint replacement or reconstruction, vertebrate replacement or reconstruction, tendon replacement, tissue regeneration, and reduction of tissue irritation by an implantable device.
  • the substrate may comprise any type of material or combination of different types of material, including inorganic material and/or organic material, in crystalline, amorphous and/or gel (e.g., hydrogel) forms, for example, metal, mineral, ceramic, glass, polymer (e.g., synthetic polymer, biopolymer), plant and/or animal biomass, and combinations thereof.
  • inorganic material and/or organic material in crystalline, amorphous and/or gel (e.g., hydrogel) forms, for example, metal, mineral, ceramic, glass, polymer (e.g., synthetic polymer, biopolymer), plant and/or animal biomass, and combinations thereof.
  • amorphous and/or gel e.g., hydrogel
  • the substrate comprises a physiological surface (e.g., a physiological tissue) and/or a surface in contact with and/or intended to come into contact with a physiological surface (e.g., as described herein in any one of the respective embodiments).
  • a physiological surface e.g., a physiological tissue
  • a surface in contact with and/or intended to come into contact with a physiological surface e.g., as described herein in any one of the respective embodiments.
  • the article is a medical device (the substrate being a medical device or portion of a medical device, as described herein).
  • the medical device is a device designed to come into contact with a part of the body susceptible to infection, such as an internal portion of the body, a mucous membrane and/or a surface of the eye. Examples of such medical devices include, without limitation, catheters, surgical tools and implants (which are for coming into contact with an internal portion of the body) and contact lenses (which are for contacting a surface of the eye).
  • the phrase "medical device” includes any material or device that is used on, in, or through a subject's body, for example, in the course of medical treatment (e.g., for a disease or injury).
  • the subject may be human or a non-human animal, such that the phrase “medical device” encompasses veterinary devices.
  • Medical devices include, but are not limited to, such items as medical implants (including permanent implants and transient implants), wound care devices, medical devices for drug delivery, contact lenses and body cavity and personal protection devices.
  • the medical implants include, but are not limited to, catheters (e.g., urinary catheters, intravascular catheters), injection ports, intubation equipment, dialysis shunts, wound drain tubes, skin sutures, vascular grafts, implantable meshes, intraocular devices, heart valves, and the like.
  • Wound care devices include, but are not limited to, general wound dressings, biologic graft materials, tape closures and dressings, and surgical incise drapes.
  • Medical devices for drug delivery include, but are not limited to, needles, drug delivery skin patches, drug delivery mucosal patches and medical sponges.
  • Body cavity and personal protection devices include, but are not limited to, tampons, sponges, surgical and examination gloves, and toothbrushes.
  • birth control devices include, but are not limited to, intrauterine devices (IUDs), diaphragms and condoms.
  • Exemplary articles include the following:
  • Medical devices such as, but not limited to, pacemakers, heart valves, replacement joints, catheters, catheter access ports, dialysis tubing, gastric bands, shunts, screw plates, artificial spinal disc replacements, internal implantable defibrillators, cardiac resynchronization therapy devices, implantable cardiac monitors, mitral valve ring repair devices, left ventricular assist devices (LVADs), artificial hearts, implantable infusion pumps, implantable insulin pumps, stents, implantable neurostimulators, maxillofacial implants, dental implants, and the like;
  • pacemakers heart valves, replacement joints, catheters, catheter access ports, dialysis tubing, gastric bands, shunts, screw plates, artificial spinal disc replacements, internal implantable defibrillators, cardiac resynchronization therapy devices, implantable cardiac monitors, mitral valve ring repair devices, left ventricular assist devices (LVADs), artificial hearts, implantable infusion pumps, implantable insulin pumps, stents, implantable neurostimulators, maxillofacial implants, dental implants, and
  • Packages or containers for example, food packages and containers, beverage packages and containers, medical device packages, agricultural packages and containers (of agrochemicals), blood sample or other biological sample packages and containers, and any other packages or containers of various articles;
  • Food packages such as packages of dairy products and/or containers for storage or transportation of dairy products
  • Milk storage and processing devices such as, but not limited to, containers, storage tanks, raw milk holding equipment, dairy processing operations conveyer belts, tube walls, gaskets, rubber seals, stainless steel coupons, piping systems, filling machine, silo tanks, heat exchangers, post-pasteurization equipment, pumps, valves, separators, and spray devices;
  • Energy harvesting device for example, a microelectronic device, a microelectromechanical device, a photovoltaic device and the like;
  • Microfluidic devices for example, micro-pumps or micro valves and the like;
  • Sealing parts for example, O rings, and the like;
  • Textiles for example, tough cottons
  • Construction elements such as, but not limited to, paints, walls, windows, door handles, and the like; Elements of water treatment systems (such as for containing and/or transporting and/or treating aqueous media or water), devices, containers, filters, tubes, solutions and gases and the like; and
  • Elements of organic waste treatment systems (such as for containing and/or disposing and/or transporting and/or treating organic waste), devices, containers, filters, tubes, solutions and gases and the like.
  • the article-of- manufacturing comprises a catheter having applied on at least a portion thereof a co-polymeric compound or a composition or composite material, as described herein in any of the respective embodiments and any combination thereof.
  • the co-polymeric compound, or the composition or composite material, or optionally a lipid bi-layer or liposome made of the co-polymeric compound as described herein reduces wear and surface damage.
  • a lipid bilayer (referred to herein interchangeably as simply a "bilayer") comprising a polymeric compound according to any of the respective embodiments described herein.
  • the bilayer further comprises at least one bilayer-forming lipid in addition to the co- polymeric compound.
  • a lipid bilayer or a liposome can be formed when one of El and E2 terminal groups is a lipid moiety as described herein in any of the respective embodiments and any combination thereof.
  • a total sum of n+m is lower than 1,000 or lower than 500, or lower than 300, or lower than 200, or lower than 100, and can range, for example, from 2 to 1,000 or from 5 to 1,000, or from 10 to 1,000, or fro, 50 to 1,000, or from 2 to 100, or from 5 to 100, or from 10 to 100, including any intermediate values and subranges therebetween.
  • bilayer-forming lipid encompasses any compound in which a bilayer may form from a pure aqueous solution of the compound, the bilayer comprising two parallel layers of molecules of the compound (referred to as a "lipid"). It is to be appreciated that the co-polymeric compound described herein in any of the embodiments may optionally comprise a bilayer-forming lipid which can form a bilayer per se or in combination with one or more additional bilayer- forming lipids.
  • the bilayer comprises relatively polar moieties of the lipid at the two surfaces of the bilayer, which may optionally comprise an interface with the aqueous solution and/or an interface with a solid surface; and relatively hydrophobic moieties of the lipid at the interior of the bilayer, at an interface between the two layers of lipid molecules which form the bilayer.
  • bilayer- forming lipids examples include glycerophospholipids (e.g., a glycerophospholipid according to any of the respective embodiments described herein). It is to be appreciated that the polymeric compound described herein may optionally be a bilayer-forming lipid which can form a bilayer per se or in combination with one or more additional bilayer- forming lipids.
  • Exemplary glycerophospholipids include phosphatidyl ethanolamine, phosphatidyl serine, phosphatidyl glycerol, and phosphatidyl inositol.
  • the bilayer- forming lipid comprises at least one charged group (e.g., one or more negatively charged groups and/or one or more positively charged groups).
  • the bilayer-forming lipid is zwitterionic; comprising both (e.g., an equal number of) negatively charged and positively charged groups (e.g., one of each).
  • lipid moiety of a polymeric moiety facilitates anchorage of the lipid moiety of the polymeric moiety in a bilayer comprising the bilayer-forming lipid.
  • the bilayer according to some of any of the embodiments described herein may optionally be closed upon itself (e.g., such that the bilayer has no edges), thereby forming an inner volume separated by the bilayer from the surrounding environment, which is referred to herein and in the art as a "liposome" .
  • the bilayer may be open-faced and/or with edges.
  • a liposome may optionally comprise a single bilayer or a plurality of bilayers (each bilayer optionally independently forming a closed vesicle) comprising, for example, concentric bilayer vesicles and/or a plurality of separate bilayer vesicles encompassed by the same bilayer vesicle.
  • a liposome comprising a co-polymeric compound as described herein in any of the respective embodiments and any combination thereof and a bilayer-forming lipid according to any of the respective embodiments described herein.
  • liposome refers to an artificially prepared vesicle comprising a bilayer composed of molecules of an amphiphilic lipid.
  • the bilayer is typically configured such that hydrophilic moieties of the amphiphilic lipid are exposed to the medium at both surfaces of the bilayer, whereas lipophilic moieties of the lipid are located in the internal portion of the bilayer, and therefore less exposed to the medium.
  • liposomes which may be used in any one of the embodiments described herein include, without limitation, small unilamellar vesicles, large unilamellar vesicles, and multilamellar vesicles.
  • the liposomes are characterized by a diameter (e.g., an average diameter) in a range of from 1 to 1000 nm, or from 10 to 750 nm, or from 100 to 750 nm, including any intermediate values and subranges therebetween.
  • a diameter e.g., an average diameter
  • a liposome may optionally comprise a single bilayer or a plurality of bilayers (each bilayer optionally independently forming a closed vesicle) comprising, for example, concentric bilayer vesicles and/or a plurality of separate bilayer vesicles encompassed by the same bilayer vesicle.
  • a liposome according to any of the respective embodiments described herein may be approximately spherical in shape or may have any alternative shape, such as an elongated tube and/or a flattened (e.g., sheet-like) shape.
  • the liposome further comprises at least one functional moiety or agent bound to, or associated with, a surface of the liposome and/or within a lipid bilayer and/or core of the liposome (e.g., within the liposome bilayer and/or enveloped by the liposome bilayer).
  • a functional moiety is covalently attached to a liposome. Such attachment may be obtained in some embodiments by using techniques known in the art (e.g., amide bond formation).
  • Examples of functional moieties and agents suitable for inclusion in a liposome include, without limitation, a therapeutically active agent or a moiety of a therapeutically active agent (e.g., wherein the active agent is releasable upon cleavage of the moiety), a labeling moiety or agent, and/or a targeting moiety or targeting agent (e.g., a targeting moiety or agent on a surface of the liposome).
  • a therapeutically active agent or a moiety of a therapeutically active agent e.g., wherein the active agent is releasable upon cleavage of the moiety
  • a labeling moiety or agent e.g., wherein the active agent is releasable upon cleavage of the moiety
  • a targeting moiety or targeting agent e.g., a targeting moiety or agent on a surface of the liposome.
  • Exemplary therapeutically active agents suitable for inclusion in a liposome include, without limitation, amphotericin B, cisplatin, cytarabine, daunorubicin, doxorubicin, estradiol, influenza virosome, morphine, surfactant protein B, surfactant protein C, verteporfin and vincristine.
  • labeling agent refers to a detectable moiety or a probe and includes, for example, chromophores, fluorescent compounds, phosphorescent compounds, heavy metal clusters, and radioactive labeling compounds, as well as any other known detectable moieties.
  • a targeting moiety in a liposome according to any of the respective embodiments described herein may optionally be a targeting moiety according to any of the respective embodiments described herein.
  • a targeting moiety in a liposome may be comprised by a co-polymeric compound according to some embodiments of the invention (according to any of the respective embodiments described herein), the liposome comprising the co-polymeric compound.
  • a targeting moiety in a liposome may optionally be comprised by another compound in the liposome, optionally a bilayer- forming lipid (according to any of the respective embodiments described herein) conjugated to a targeting moiety according to any of the respective embodiments described herein.
  • the liposome may further comprise an additional agent that is bound to or associated with the lipid bilayer.
  • agents can be, for example, lipidic agents, including, but not limited to, fatty acids, fatty amines, fatty acyls, fatty alcohols, monoglycerides, diglycerides, triglycerides, glycerophospholipids, sphingolipids, and sterols (e.g., cholesterol).
  • a liposome as described herein comprises a therapeutically active agent, bound to, or associated with, a surface of the liposome and/or within a lipid bilayer and/or core of the liposome (e.g., within the liposome bilayer and/or enveloped by the liposome bilayer), the liposome can be used, for example, in drug delivery applications.
  • a liposome comprising at least one bilayer-forming lipid; a co-polymeric compound; optionally a sterol; and a therapeutically active agent, as described herein in any of the respective embodiments and any combination thereof, in the manufacture of a medicament for delivering the therapeutically active agent to a subject in need thereof.
  • delivery and “delivering” encompass targeting of a therapeutically active agent to a specific bodily site, such that a higher proportion of the agent reaches the bodily site (e.g., using a suitable targeting moiety); and/or control over duration of a presence of such an agent in the body (e.g., in the blood) - for example, by sustained release - which may be associated with a duration of such an agent at a desired bodily site (even if in the absence of specific targeting to the bodily site).
  • the phrase "bodily site” includes any organ, tissue, membrane, cavity, blood vessel, tract, biological surface or muscle, which contacting therewith (e.g., delivering thereto or applying thereon) the liposome or the therapeutically active agent disclosed herein is beneficial.
  • Exemplary bodily sites include, but are not limited to, the skin, a dermal layer, the scalp, an eye, an ear, a mouth, a throat, a stomach, a small intestines tissue, a large intestines tissue, a kidney, a pancreas, a liver, the digestive system, the respiratory tract, a bone marrow tissue, a mucosal membrane, a nasal membrane, the blood system, a blood vessel, a muscle, a pulmonary cavity, an artery, a vein, a capillary, a heart, a heart cavity, a male or female reproductive organ and any visceral organ or cavity. Any organ or tissue onto which microorganism can exist in contemplated.
  • sustained release refers to a formulation of an agent which provides a gradual and/or delayed (“sustained") release of the agent (e.g., from a reservoir such a liposome according to any of the respective embodiments described herein), which results in the agent being present in a bodily site (e.g., in the blood upon systemic administration, or in a bodily site to which the agent is locally administered) for a longer duration and/or at a later time (relative to administration) than if the agent is administered per se (via the same administration route).
  • a bodily site e.g., in the blood upon systemic administration, or in a bodily site to which the agent is locally administered
  • the sustained release is characterized by a concentration of therapeutically active agent (e.g., in the blood upon systemic administration, or in a bodily site to which the agent is locally administered) which is at least half of the maximal concentration (Cmax) for a time period which is at least 50 % more than a corresponding time period (i.e., during which a concentration of an agent is at least half of the maximal concentration) an agent upon administration of the therapeutically effective agent per se (e.g., as defined herein) in an amount which results in the same maximal concentration.
  • the time period (for sustained release) is at least 100 % more than (i.e., twice) a corresponding time period (for the agent per se).
  • the time period (for sustained release) is at least 200 % more than (i.e., 3-fold) a corresponding time period (for the agent per se). In some embodiments, the time period (for sustained release) is at least 400 % more than (i.e., 5-fold) a corresponding time period (for the agent per se).
  • Sustained release may allow, for example, for a regimen characterized by less frequent administration and/or by greater therapeutic efficacy of any given administration.
  • the skilled person will be readily capable of determining a suitable frequency of administration for a given therapeutically active agent based on the duration of the sustained release (e.g., a time period during which the concentration of the agent is at least half of the maximal concentration, according to any of the respective embodiments described herein, and/or at least a minimal effective concentration), and the ratio between a desirable maximal concentration and a minimal effective concentration for the given agent (e.g., a "therapeutic window" of the agent).
  • hydrocarbon describes an organic moiety that includes, as its basic skeleton, a chain of carbon atoms, substituted mainly by hydrogen atoms.
  • the hydrocarbon can be saturated or non-saturated, be comprised of aliphatic, alicyclic or aromatic moieties, and can optionally be substituted by one or more substituents (other than hydrogen).
  • a substituted hydrocarbon may have one or more substituents, whereby each substituent group can independently be, for example, cycloalkyl, alkenyl, alkynyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy, aryloxy, thiohydroxy, thioalkoxy, thioaryloxy, oxo, cyano, nitro, azo, azide, sulfonamide, carboxy, thiocarbamate, urea, thiourea, carbamate, amide, and hydrazine.
  • substituent group can independently be, for example, cycloalkyl, alkenyl, alkynyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy, aryloxy,
  • the hydrocarbon can be an end group or a linking group, as these terms are defined herein.
  • the hydrocarbon moiety is optionally interrupted by one or more heteroatoms, including, without limitation, one or more oxygen, nitrogen and/or sulfur atoms. In some embodiments of any of the embodiments described herein relating to a hydrocarbon, the hydrocarbon is not interrupted by any heteroatoms.
  • the hydrocarbon moiety has 1 to 20 carbon atoms.
  • a numerical range e.g., “1 to 20”, is stated herein, it implies that the group, in this case the alkyl group, may contain 1 carbon atom, 2 carbon atoms, 3 carbon atoms, etc., up to and including 20 carbon atoms.
  • alkyl describes a saturated aliphatic hydrocarbon end group, as defined herein, including straight chain and branched chain groups.
  • the alkyl group has 1 to 20 carbon atoms. More preferably, the alkyl is a medium size alkyl having 1 to 10 carbon atoms. Most preferably, unless otherwise indicated, the alkyl is a lower alkyl having 1 to 4 carbon atoms.
  • the alkyl group may be substituted or non-substituted.
  • Substituted alkyl may have one or more substituents, whereby each substituent group can independently be, for example, cycloalkyl, alkenyl, alkynyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy, aryloxy, thiohydroxy, thioalkoxy, thioaryloxy, cyano, nitro, azo, azide, sulfonamide, carboxy, thiocarbamate, urea, thiourea, carbamate, amide, and hydrazine.
  • substituent group can independently be, for example, cycloalkyl, alkenyl, alkynyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy, aryloxy, thio
  • alkylene describes a saturated aliphatic hydrocarbon linking group, as this term is defined herein, which differs from an alkyl group, as defined herein, only in that alkylene is a linking group rather than an end group.
  • alkenyl describes an unsaturated aliphatic hydrocarbon end group which comprises at least one carbon-carbon double bond, including straight chain and branched chain groups.
  • the alkenyl group has 2 to 20 carbon atoms. More preferably, the alkenyl is a medium size alkenyl having 2 to 10 carbon atoms. Most preferably, unless otherwise indicated, the alkenyl is a lower alkenyl having 2 to 4 carbon atoms.
  • the alkenyl group may be substituted or non-substituted.
  • Substituted alkenyl may have one or more substituents, whereby each substituent group can independently be, for example, cycloalkyl, alkynyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy, aryloxy, thiohydroxy, thioalkoxy, thioaryloxy, cyano, nitro, azo, azide, sulfonamide, carboxy, thiocarbamate, urea, thiourea, carbamate, amide, and hydrazine.
  • substituent group can independently be, for example, cycloalkyl, alkynyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy, aryloxy, thiohydroxy, thioalkoxy,
  • alkynyl describes an unsaturated aliphatic hydrocarbon end group which comprises at least one carbon-carbon triple bond, including straight chain and branched chain groups.
  • the alkynyl group has 2 to 20 carbon atoms. More preferably, the alkynyl is a medium size alkynyl having 2 to 10 carbon atoms. Most preferably, unless otherwise indicated, the alkynyl is a lower alkynyl having 2 to 4 carbon atoms.
  • the alkynyl group may be substituted or non-substituted.
  • Substituted alkynyl may have one or more substituents, whereby each substituent group can independently be, for example, cycloalkyl, alkenyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy, aryloxy, thiohydroxy, thioalkoxy, thioaryloxy, cyano, nitro, azo, azide, sulfonamide, carboxy, thiocarbamate, urea, thiourea, carbamate, amide, and hydrazine.
  • substituent group can independently be, for example, cycloalkyl, alkenyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy, aryloxy, thiohydroxy, thioalkoxy,
  • cycloalkyl describes an all-carbon monocyclic or fused ring (i.e., rings which share an adjacent pair of carbon atoms) group where one or more of the rings does not have a completely conjugated pi-electron system.
  • the cycloalkyl group may be substituted or nonsubstituted.
  • Substituted cycloalkyl may have one or more substituents, whereby each substituent group can independently be, for example, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy, aryloxy, thiohydroxy, thioalkoxy, thioaryloxy, cyano, nitro, azo, azide, sulfonamide, carboxy, thiocarbamate, urea, thiourea, carbamate, amide, and hydrazine.
  • the cycloalkyl group can be an end group, as this phrase is defined herein, wherein it is attached to a single adjacent atom, or a linking group, as this phrase is defined herein, connecting two or more moieties.
  • aryl describes an all-carbon monocyclic or fused -ring polycyclic (i.e., rings which share adjacent pairs of carbon atoms) end group (as this term is defined herein) having a completely conjugated pi-electron system.
  • the aryl group may be substituted or non-substituted.
  • Substituted aryl may have one or more substituents, whereby each substituent group can independently be, for example, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy, aryloxy, thiohydroxy, thioalkoxy, thioaryloxy, cyano, nitro, azo, azide, sulfonamide, carboxy, thiocarbamate, urea, thiourea, carbamate, amide, and hydrazine.
  • Phenyl and naphthyl are representative aryl end groups.
  • heteroaryl describes a monocyclic or fused ring (i.e., rings which share an adjacent pair of atoms) group having in the ring(s) one or more atoms, such as, for example, nitrogen, oxygen and sulfur and, in addition, having a completely conjugated pi-electron system.
  • heteroaryl groups include pyrrole, furan, thiophene, imidazole, oxazole, thiazole, pyrazole, pyridine, pyrimidine, quinoline, isoquinoline and purine.
  • the heteroaryl group may be substituted or non-substituted.
  • Substituted heteroaryl may have one or more substituents, whereby each substituent group can independently be, for example, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy, aryloxy, thiohydroxy, thioalkoxy, thioaryloxy, cyano, nitro, azo, azide, sulfonamide, carboxy, thiocarbamate, urea, thiourea, carbamate, amide, and hydrazine.
  • substituent group can independently be, for example, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy,
  • the heteroaryl group can be an end group, as this phrase is defined herein, where it is attached to a single adjacent atom, or a linking group, as this phrase is defined herein, connecting two or more moieties.
  • Representative examples are pyridine, pyrrole, oxazole, indole, purine and the like.
  • arylene describes a monocyclic or fused-ring polycyclic linking group, as this term is defined herein, and encompasses linking groups which differ from an aryl or heteroaryl group, as these groups are defined herein, only in that arylene is a linking group rather than an end group.
  • heteroalicyclic describes a monocyclic or fused ring group having in the ring(s) one or more atoms such as nitrogen, oxygen and sulfur.
  • the rings may also have one or more double bonds. However, the rings do not have a completely conjugated pi-electron system.
  • the heteroalicyclic may be substituted or non-substituted.
  • Substituted heteroalicyclic may have one or more substituents, whereby each substituent group can independently be, for example, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy, aryloxy, thiohydroxy, thioalkoxy, thioaryloxy, cyano, nitro, azo, azide, sulfonamide, carboxy, thiocarbamate, urea, thiourea, carbamate, amide, and hydrazine.
  • substituent group can independently be, for example, alkyl, alkenyl, alkynyl, cycloalkyl, aryl, heteroaryl, heteroalicyclic, amine, halide, sulfonate, sulfoxide, phosphonate, hydroxy, alkoxy
  • the heteroalicyclic group can be an end group, as this phrase is defined herein, where it is attached to a single adjacent atom, or a linking group, as this phrase is defined herein, connecting two or more moieties.
  • Representative examples are piperidine, piperazine, tetrahydrofuran, tetrahydropyran, morpholine and the like.
  • amine and “amino” describe both a -NRxRy end group and a -NRx- linking group, wherein Rx and Ry are each independently hydrogen, alkyl, cycloalkyl, aryl, heteroaryl or heteroalicyclic, as these terms are defined herein.
  • Rx or Ry is heteroaryl or heteroalicyclic
  • the amine nitrogen atom is bound to a carbon atom of the heteroaryl or heteroalicyclic ring.
  • hydroxy and “hydroxyl” describe a -OH group.
  • alkoxy describes both an -O-alkyl and an -O-cycloalkyl end group, or -O- alkylene or -O-cycloalkyl linking group, as defined herein.
  • aryloxy describes both an -O-aryl and an -O-heteroaryl end group, or an -O- arylene- linking group, as defined herein.
  • thiohydroxy describes a -SH group.
  • thioalkoxy describes both an -S-alkyl and an -S-cycloalkyl end group, or -S- alkylene or -S-cycloalkyl linking group, as defined herein.
  • thioaryloxy describes both an -S-aryl and an -S-heteroaryl end group, or an -S- arylene- linking group, as defined herein.
  • nitro describes an -NO2 group.
  • halide and “halo” refer to fluorine, chlorine, bromine or iodine.
  • phosphinyl refers to a -PRxRy group, where Rx and Ry are as defined hereinabove.
  • hydrazine describes a -NRx-NRyRw end group or -NRx-NRy- linking group, with Rx, Ry, and Rw as defined herein.
  • compositions, methods or structure may include additional ingredients, steps and/or parts, but only if the additional ingredients, steps and/or parts do not materially alter the basic and novel characteristics of the claimed composition, method or structure.
  • a compound or “at least one compound” may include a plurality of compounds, including mixtures thereof.
  • range format is merely for convenience and brevity and should not be construed as an inflexible limitation on the scope of the invention. Accordingly, the description of a range should be considered to have specifically disclosed all the possible subranges as well as individual numerical values within that range. For example, description of a range such as from 1 to 6 should be considered to have specifically disclosed subranges such as from 1 to 3, from 1 to 4, from 1 to 5, from 2 to 4, from 2 to 6, from 3 to 6 etc., as well as individual numbers within that range, for example, 1, 2, 3, 4, 5, and 6. This applies regardless of the breadth of the range.
  • a numerical range is indicated herein, it is meant to include any cited numeral (fractional or integral) within the indicated range.
  • the phrases “ranging/ranges between” a first indicate number and a second indicate number and “ranging/ranges from” a first indicate number “to” a second indicate number are used herein interchangeably and are meant to include the first and second indicated numbers and all the fractional and integral numerals therebetween.
  • method refers to manners, means, techniques and procedures for accomplishing a given task including, but not limited to, those manners, means, techniques and procedures either known to, or readily developed from known manners, means, techniques and procedures by practitioners of the chemical, pharmacological, biological, biochemical and medical arts.
  • treating refers to inhibiting, preventing or arresting the development of a pathology (disease, disorder or condition) and/or causing the reduction, remission, or regression of a pathology.
  • pathology disease, disorder or condition
  • Those of skill in the art will understand that various methodologies and assays can be used to assess the development of a pathology, and similarly, various methodologies and assays may be used to assess the reduction, remission or regression of a pathology.
  • the term “preventing” refers to keeping a disease, disorder or condition from occurring in a subject who may be at risk for the disease, but has not yet been diagnosed as having the disease. It is appreciated that certain features of the invention, which are, for clarity, described in the context of separate embodiments, may also be provided in combination in a single embodiment. Conversely, various features of the invention, which are, for brevity, described in the context of a single embodiment, may also be provided separately or in any suitable subcombination or as suitable in any other described embodiment of the invention. Certain features described in the context of various embodiments are not to be considered essential features of those embodiments, unless the embodiment is inoperative without those elements.
  • Ampicillin was obtained from Tivan Biotech (Israel).
  • RPMI medium Gibco
  • FBS fetal bovine serum
  • penicillin-streptomycin Vybrant DiD cell-labeling solution
  • pBAD Kit V43001
  • Water used was purified using a BarnsteadTM NanopureTM system (Thermo Fisher Scientific, Waltham, MA, USA) to MQ.cm (at 25 °C) and total organic content ⁇ 1 ppb.
  • N- propylacrylamide (nPAM, >98 %) was obtained from Tokyo Chemical Industry Co., Ltd.
  • PMN-free pHEMA hydrogels were prepared as follows: HEMA (3 mL), EGDMA (0.1 mL or 0.3 mL), APS aqueous solution (0.2 mL, 24 mg APS), and purified water (2 mL) were added together and vigorously stirred for 15 minutes at room temperature. The molar ratio of the EGDMA crosslinker to the HEMA monomer was kept at 2 %. To accelerate the reaction, TMEDA (50 pL) was added to the mixture, which was then stirred for 20 seconds and poured into a 6 centimeter (cm) diameter petri dish. The mixture was allowed to gel at room temperature for 4 hours, followed by immersion in an excess of purified water for 3 days to remove unreacted materials.
  • PMN-incorporating hydrogels were prepared similarly, while replacing the 2 mL purified water by 2 mL of a respective PMN-containing solution at a concentration of 25 mg/mL, to provide a 1 % PMN-incorporating pHEMA hydrogel (1 % by weight).
  • PMP-incorporating hydrogels (1 % by weight) were prepared in a similar manner, with the exception that the PMN solution (2 mL) was replaced by the respective PMP solution (2 mL).
  • An exemplary preparation process is as follows:
  • HEMA 3 mL
  • EGDMA 0.1 mL or 0.3 mL
  • APS aqueous solution 0.2 mL, 24 mg APS
  • PMP copolymer solution 25 mg/mL, 2 mL
  • TMEDA 50 pL
  • the mixture was allowed to gel at room temperature for 4 hours, and unreacted materials were removed by immersion in an excess of purified water for 3 days, to provide a PMP-incorporating hydrogel.
  • PMN-rhodamine conjugate-incorporating hydrogels were similarly prepared, while replacing the 2 mL purified water by 2 mL aqueous solution of PMN and 0.5 weight % of acryloxyethyl thiocarbamoyl rhodamine B.
  • DMPC-incorporating hydrogels were prepared by the following procedures:
  • HEMA 3 mL, 24.6 mmol
  • EGDMA generally 0.095 mL, 0.5 mmol
  • APS aqueous solution 0.2 mL containing 0.105 mmol APS
  • 45 mM DMPC aqueous suspension 2 mL
  • the molar ratio of the EGDMA crosslinker to the HEMA monomer was thus generally 2 %.
  • TMEDA 50 pL was added to the mixture, stirring took place for 20 seconds and the mixture was poured into a 6-cm diameter petri dish. The mixture was allowed to gel at room temperature for 4 hours, followed by immersion in a large excess of purified water for 3 days to remove unreacted materials.
  • TMEDA 50 pL was added to the mixture, stirring took place for 20 seconds and the mixture was poured into a 6-cm diameter petri dish. The mixture was allowed to gel at room temperature for 4 hours, followed by immersion in a large excess of purified water for 3 days to remove unreacted materials.
  • pMPC-incorporating hydrogel HEMA (3 mL, 24.6 mmol), EGDMA (generally 0.095 mL, 0.5 mmol), APS aqueous solution (0.2 mL containing 0.105 mmol APS), and 12.5 mg/mL pMPC aqueous solution (2 mL) were added together and vigorously stirred for 0.5 hour.
  • the molar ratio of the EGDMA cross-linker to the HEMA monomer was thus generally 2 %.
  • TMEDA 50 pL was added to the mixture, stirring took place for 20 seconds and the mixture was poured into a 6-cm diameter petri dish. The mixture was allowed to gel at room temperature for 4 hours, followed by immersion in a large excess of purified water for 3 days to remove unreacted materials.
  • HEMA 3 mL, 24.6 mmol
  • EGDMA generally 0.095 mL, 0.5 mmol
  • APS aqueous solution 0.2 mL containing 0.105 mmol APS
  • 25 mg/mL pNIPAM+12.5 mg/mL pMPC aqueous solution 2 mL
  • the molar ratio of the EGDMA cross-linker to the HEMA monomer was thus generally 2%.
  • TMEDA 50 pL was added to the mixture, stirring took place for 20 seconds and the mixture was poured into a 6-cm diameter petri dish. The mixture was allowed to gel at room temperature for 4 hours, followed by immersion in a large excess of purified water for 3 days to remove unreacted materials.
  • HEMA-co-HEAA hydrogel HEMA (1.5 mL, 12.3 mmol), HEAA (1.5 mL, 14.5 mL), EGDMA (generally 0.095 mL, 0.5 mmol), APS aqueous solution (0.2 mL containing 0.105 mmol APS), and 2 mL pure water were added together and vigorously stirred for 0.5 hour.
  • the molar ratio of the EGDMA cross-linker to the HEMA monomer was thus generally 2 %.
  • TMEDA 50 pL was added to the mixture, stirring took place for 20 seconds and the mixture was poured into a 6-cm diameter petri dish. The mixture was allowed to gel at room temperature for 4 hours, followed by immersion in a large excess of purified water for 3 days to remove unreacted materials.
  • HEMA-co-DMAA hydrogel HEMA (1.5 mL, 12.3 mmol), DMAA (1.5 mL, 16.1 mL), EGDMA (generally 0.095 mL, 0.5 mmol), APS aqueous solution (0.2 mL containing 0.105 mmol APS), and 2 mL pure water were added together and vigorously stirred for 0.5 hour.
  • the molar ratio of the EGDMA cross-linker to the HEMA monomer was thus generally 2 %.
  • TMEDA 50 pL was added to the mixture, stirring took place for 20 seconds and the mixture was poured into a 6-cm diameter petri dish.
  • PEGMA hydrogel PEGMA (3 mL, 8.3 mmol), EGDMA (generally 0.095 mL, 0.5 mmol), APS aqueous solution (0.2 mL containing 0.105 mmol APS), and 2 mL pure water were added together and vigorously stirred for 0.5 hour.
  • the molar ratio of the EGDMA cross-linker to the HEMA monomer was thus generally 2 %.
  • TMEDA 50 pL was added to the mixture, stirring took place for 20 seconds and the mixture was poured into a 6-cm diameter petri dish. The mixture was allowed to gel at room temperature for 4 hours, followed by immersion in a large excess of purified water for 3 days to remove unreacted materials.
  • FIGs. 4A-B and FIGs. 8A-C were acquired using a 8 MP Sony IMX586 1/2.0" sensor, f/1.75-aperture lens with 26 mm-equivalent focal length, equipped on a OnePlus Nord phone (OnePlus, China).
  • Cryo-SEM freeze fracture imaging Hydrogel samples (20 mm disks) were sectioned to slices of thickness 100 pm using a vibratome (Electron Microscopy Sciences, USA). The slices were sandwiched between an aluminum disc with a depression of depth 150 pm and a flat disc (M. Wohlwend GmbH, Switzerland) and were then cryo-immobilized by HPM010 High Pressure Freezing Machine (BalTech, Liechtenstein).
  • the frozen sample was removed from the disc under liquid nitrogen, mounted perpendicularly in a holder, transferred to a BAF060 Freeze-fracturing device (Leica Microsystems, Austria) using a Leica EM VCT100 cryo transfer shuttle (Leica Microsystems, Austria) and was fractured perpendicularly to the plane of the frozen slice at -120 °C under a pressure of about 5- 10’ 7 mbar.
  • the cold fractured surface was sometimes "etched” by increasing the temperature to about -105 °C for several minutes to let some frozen water sublime.
  • the fractured sample was then transferred to an Ultra 55 cryo-scanning electron microscope (Zeiss, Germany) and observed using an InLens Secondary electrons detector at an acceleration voltage ranging between 1-2.5 kV.
  • Viscoelastic measurements were performed using a strain/stress-controlled rheometer (Thermo-Haake, Mars III, Düsseldorf, Germany). Samples were prepared in the form of disks with a diameter of 20 mm and thickness of about 2 mm. Samples were tested using a parallel plate geometry. The samples were placed between the rheometer plates and a slight compression of about 1.0 N was applied. Amplitude sweep tests were performed in constant strain mode for strains in the range of 10’ 4 to 0.5, the oscillation frequency being 1 Hz. Frequency sweep tests were performed in stress control mode, with stress being in the range of linear viscoelasticity, as determined from the amplitude sweep studies. The frequency range was between 0.05 and 30-100 Hz.
  • Confocal fluorescence microscopy imaging To prepare PMN-based hydrogels for confocal fluorescence microscopy imaging, PMN-rhodamine conjugated based hydrogels were prepared as described hereinabove. Confocal pictures were acquired using confocal laser scanning microscopy LSM700 (Zeiss, Germany). All images were acquired using a 40X oil immersion objective (NA 1.4 Zeiss, Germany) and recorded in brightfield mode and in confocal mode using a 540 nm excitation laser channel, with a 0.3 pm optical slice step for z scanning. Picture analysis was performed using ImageJ software vl.52i (NIH, USA).
  • Actreen® Hi-Lite Cath Nelaton (glycerol-coated catheter for male intermittent self-catheterization) was washed with excess water to remove the existing lubricant, to thereby provide an uncoated commercial catheter.
  • the catheter was washed with toluene, and dried in the air.
  • Hydrogel coating (w/o PMN) on the catheter was performed by pulling out the catheter from the polymerization solution after 1 minute, and the polymerization was proceeding for 12 hours under N2 atmosphere.
  • Vero E6 cells were cultured in RPMI medium, supplemented with 1% Pen/Strep and 10 % fetal bovine serum (FBS), and were maintained at 37 °C in a humidified atmosphere of 95 % air and 5 % CO2. Cytotoxicity studies:
  • Cell culture Prior to cytotoxicity experiment, cells were cultured in 12-well plates at 8- 10 4 cells per mL and allowed to attach for 24 hours.
  • Cytotoxicity evaluation The cytotoxicity of hydrogel containing 3 mg/mL PMN was conducted in 12-well plates using Transwell® cell culture inserts. Hydrogel (0.6 mm disk) was placed in a center of Transwell® and pre-incubated in a cell culture media for 1 hour at room temperature in order to exchange water within the hydrogel. The inserts with hydrogels were then placed into wells containing the cultured cells and incubated for 48 hours at 37 °C (95 % air and 5 % CO 2 ).
  • Cell viability was determined by the production of the yellow formazan product upon cleavage of XTT by mitochondrial dehydrogenases in viable Vero cells. After 48 hours incubation with hydrogels, the cells were incubated with 500 pL of XTT solution for 4 hours at 37 °C (95 % air and 5 % CO2). Absorbance values were later measured with ClarioStar microplate reader (BMG LABTECH GmbH, Germany) at a wavelength of 450 nm. Background absorbance was measured at 620 nm and subtracted from the 450 nm measurement. The absorbance of a solution in RPMI-cell-free media with XTT was subtracted from all samples. The potential toxic effect of the different liposomal formulations tested was expressed as a viability percentage calculated using the following formula:
  • ODtest was the optical density of those wells with hydrogels
  • ODc was the optical density of cells in RPMI media only (no hydrogel).
  • PMN-rhodamine conjugateincorporating hydrogels were prepared as described hereinabove. PMN transfer via SS-gel (stainless steel, SS) or PE-gel (polyethylene, PE) sliding and imaging of transferred material.
  • the spherical head (SS or PE) was slid past hydrogels incorporating PMN-rhodamine-conjugate or DMPC-MLV stained with 1 % Dil, at a sliding velocity 1 mm/second for 5 minutes.
  • the spherical head (PE or SS) head was washed with water (PMN) or ethanol (DMPC), and evaporated overnight using a nitrogen stream followed by lyophilization. 400 pL of water (PMN) or chloroform (DMPC) was used to re-suspend polymer or lipids, and the solution was placed in a quartz silica cuvette with a 1 mm path length. Acquisition of rhodamine and Dil emission spectra was performed with an Agilent Cary Eclipse Fluorescence Spectrophotometer (Varian Instruments, Walnut Creek, CA) at room temperature (FIGs. 5A-D).
  • the excitation wavelength was set at 500 nm with a bandpass of 20 nm, and the emission was also recorded with bandpass of 20 nm. Spectrum acquisition was repeated over a minimum of 3 separate samples. Calibration curves were prepared by measuring the maximal (Inserts of FIGs. 10A and 10B) fluorescence intensity of known amounts of pure PMN-Rhodamine- water and DMPC-DiL chloroform solution by the same method and parameters to ensure the same experimental conditions.
  • Vero E6 cells adhesion to hydrogels Vero E6 cell suspension (1.5 mL of 5.2- 10 5 ) was seeded onto 6 mm hydrogel discs (neat and PMN) in 24 well plates and allowed to attach for 24 hours. The cells were then stained with Vybrant DiD by adding 5 pL of stock solution and incubated for 20 minutes at 37 °C. After 20 minutes hydrogels were washed carefully with PBS and placed in a fresh cell medium. Hydrogels were placed on the slide and observed with confocal laser scanning microscopy LSM700 (Zeiss, Germany). All images were acquired using a 60X oil immersion objective and recorded in brightfield mode and in confocal mode using a 635 nm excitation laser channel.
  • the anti-biofouling property of hydrogel was further determined by using Typhoon FLA 9500 scanner (GE Healthcare Bio-Sciences AB, Sweden) with 635 nm laser wavelength, photomultiplier tube set up at 250' gain and pixel size 25 pm. Pictures were analyzed using ImageJ software (NIH, USA). For comparative analysis, all parameters during image acquisition were kept constant throughout each experiment. Additionally, fluorescence signal on hydrogel surfaces was determined with a ClarioStar microplate reader (BMG LABTECH GmbH, Germany) in 96- well plate at a wavelength of 630 nm with top reading and spiral scan mode (scan diameter: 6 mm, No. of flashes per well: 106). Bacteria adhesion to hydrogels: GFP-expressing E.
  • Coli culture was developed by plasmid transfection.
  • the sf-gfp-his plasmid was cloned into a pBAD24.
  • the plasmid was then transformed into E. coli MG1655 imp4213.
  • E. coli (MG1655) precultures cultures were inoculated at OD600 0.05 from an overnight culture, and growth was carried out at 37 °C with shaking for 4 hours, in Luria-Bertani broth (LB) supplemented with ampicillin (100 mg/L) and 0.2 % arabinose until mid-exponential phase (OD at 600 nm is about 0.5).
  • Hydrogel discs (diameter 6 mm) were placed in 24-well plate and 1 mL of bacteria suspension was added and incubated at 37 °C without shaking for 12 hours. Subsequently, hydrogels were washed carefully with PBS and placed in fresh PBS. Hydrogels were placed on the slide and observed with confocal laser scanning microscopy LSM700 (Zeiss, Germany).
  • Hydrogels were further visualized using Typhoon FLA 9500 scanner (GE Healthcare BioSciences AB, Sweden) with 635 nm laser wavelength, photomultiplier tube set up at 250' gain, and pixel size 25 pm.
  • Healthy articular cartilage has excellent lubricating properties, with friction coefficients (p) reaching about 0.002-0.02 at physiological pressures.
  • Such high -performing lubricating layer in joints is attributed to the surface hydration arising from the interplay between multiple hydrophilic biopolymers (e.g., hyaluronic acid, proteoglycans, lubricin) and phospholipids in the cartilage matrix. Mimicking such molecular structure, hydrogels composed of a hydrophilic polymer network have the potential to replicate the lubricating feature and possibly replace natural cartilages.
  • hydrophilic biopolymers e.g., hyaluronic acid, proteoglycans, lubricin
  • the present inventors have previously uncovered that reducing a friction coefficient of a surface can be performed via the hydration lubrication mechanism [Goldberg et al., 2011, supra; Seror et al., 2015, supra; Schmidt, T. A., 2020, supra].
  • WO 2017/109784 describes lipid-polymer conjugates (LPCs) comprising highly hydrated phosphatidylcholine (PC) lipid headgroups, which, when incorporated in hydrogels, displayed reduction in friction and wear relative to the lipid-free hydrogels over a wide range of conditions.
  • LPCs lipid-polymer conjugates
  • PC phosphatidylcholine
  • the counter surface is a hydrophilic surface (such as glass, hydrogel, or stainless steel) but not with hydrophobic surfaces (e.g., polyethylene), which are implicated in many applications, such as artificial joints and plastic stents.
  • hydrophilic surface such as glass, hydrogel, or stainless steel
  • hydrophobic surfaces e.g., polyethylene
  • the present inventors have conceived utilizing a polymeric structure featuring positively-charged phosphoryl alkylamine headgroups (e.g., phosphoryl choline), which exhibits a more hydrophobic nature, and have designed, to this effect, as an exemplary co-polymeric compound, poly(2-methacryloyloxyethyl phosphorylcholine- co-A-isopropylacrylamidc) random co-polymer (which is also referred to herein throughout as pMPC-co-pNIPAM; p(MPC-co-NIPAM); or simply as PMN) (see, FIG. 1A).
  • pMPC-co-pNIPAM poly(2-methacryloyloxyethyl phosphorylcholine- co-A-isopropylacrylamidc) random co-polymer
  • PMN simply as PMN
  • the random copolymer PMN was prepared as follows:
  • the reaction mixture was thereafter dialyzed against pure water for 48 hours and then dehydrated by freeze-drying, to thereby obtain the random copolymer (14.7 grams, 91.9 % yield).
  • the chemical structure was verified by 'H NMR (400 MHz, DMSO), a portion of which is presented in FIG. IB.
  • the estimated 7 : 1 ratio between NIP AM and MPC was determined by comparing the integral intensity signal.
  • the number-average molecular weight (M n ) and the molecular weight distribution (Mw/Mn) as determined by a gel-permeation chromatography (GPC) analysis were 2.2- 10 5 and 1.64, respectively.
  • the number of backbone units of MPC and NIP AM can be calculated to be about 200 and 1400, respectively.
  • the exemplary PMN co-polymer was incorporated into biocompatible pHEMA hydrogels by mixing a low concentration (1 % wt.) of PMN with the desired HEM A solution, as described in further details in the Materials and Methods section hereinabove.
  • freeze-fracture cryo-scanning electron microscopy (cryo-SEM) was performed on the resulting pHEMA hydrogels, and the obtained images are presented in FIGs. 2A-B.
  • the images reveal that PMN-pockets (or, PMN-micro-reservoirs) size ranges from 200 nm up to 900 nm (FIG. 2B) with homogenous distribution throughout the hydrogel bulk, while PMN-free hydrogels show featureless internal structure (FIG. 2A). This observation was further confirmed by confocal microscopy imaging (FIGs. 2C-D).
  • pHEMA size and zeta potential measurements were performed before and after dialysis (cellulose membrane, molecular weight cut off: 3500) for 2 days, and the results are presented in FIGs. 3A- B.
  • pHEMA was found to be water insoluble as a precipitation was observed after dialysis.
  • the size distribution of pHEMA/PMN dispersion shows one peak without precipitation (FIG. 3A), which could be attributed to the interaction between pHEMA and NIP AM moiety, whereby the hydrated pMPC moieties are exposed.
  • hydrogel’s storage modulus G’ varies by up to 50 % within a frequency (f) range of 0.1 to 10 Hz, and varies between PMN-free and PMN-incorporating hydrogels (2 % cross-linked hydrogel).
  • the loss modulus (G”) of the hydrogels also varies within the frequency range of 0.1 to 10 Hz, and between the tested PMN-free and PMN-incorporating hydrogels.
  • FIG. 7E shows the effect of a dehydration/rehydration cycle on the friction coefficient of the exemplary PMN-incorporating pHEMA hydrogel, before and after rehydration. It can be observed that the dehydration/rehydration cycle did not significantly affect the friction coefficients of the hydrogel. Indeed, these data demonstrate the ability of these compositions to retain their low friction coefficient after a dehydration/rehydration cycle.
  • fluorescence signal measured on PE surfaces upon rubbing shows a uniform signal coverage for PMN-incorporating hydrogels, indicating efficient transfer of the fluorescently labelled PMN polymer to the surfaces (FIG. 9A).
  • fluorescence signal on PE surfaces upon rubbing with DMPC-incorporating hydrogels shows weak signal with disrobed fragments of hydrogel (FIG. 9C), in good agreement with the low-friction data.
  • Table 1 summarizes adsorption values measured from either SS ball or PE ball upon rubbing for 5 minutes with DMPC or PMN hydrogels. Values are presented as an average and standard deviation from at least three separate samples.
  • DMPC-hydrogels show deposition of Dil-labelled DMPC towards stainless surfaces, in agreement with what reported by Lin et al. (2020, supra) whereas rubbing against PE ball yielded 5 times lower amount of transferred lipids.
  • a significant variability in the estimated deposited amount was observed, possibly due to the presence of fluorescently labelled hydrogel fragments (as visible in FIGs. 9A-D) affecting the overall fluorescence intensity of the recovered material.
  • the PMN-incorporating pHEMA hydrogel coating shows 80- 90 % reduction in friction against polyethylene sphere compared to the commercial lubricant.
  • coating the catheter with PMN-incorporating pHEMA reduces the friction by up to 15-folds compared with the best available commercially-lubricated urethral catheter.
  • the antifouling properties of PMN-incorporating pHEMA hydrogels were evaluated by probing both anti cell-adhesion and anti-bacteria adsorption towards the hydrogels.
  • FIG. 13A presents fluorescence images of the hydrogels
  • FIGs. 13B-C present the fluorescence quantification, using a plate reader, of DiD fluorescence intensity (FIG. 13B) and of GFP fluorescence intensity (FIG. 13C).
  • hydrogels significantly reduces the hydrogels’ sliding surface friction, resulting in low friction coefficients against different counter surfaces, including stainless steel (hard metal surface), polyethylene (hydrophobic surface), and pHEMA (soft hydrogel surface).
  • the hydrogels exhibit good anti-bacterial adhesion and anti-cell adsorption.
  • Hydrogels as reported herein provide a new strategy for various applications (e.g., biomedical applications).
  • V-alkyl substituents in co-polymeric compound were studied.
  • an V-alkyl analogue of PMN co-polymer poly(2-methacryloyloxyethyl phosphorylcholine-co-A-propylacrylamide) (PMP) random copolymer was prepared, in which poly(V-propylacrylamidc) (nPAM), having N- propylacrylamide substituents, was used instead of NIP AM (having V-isopropylacrylamidc substituents).
  • PMP poly(2-methacryloyloxyethyl phosphorylcholine-co-A-propylacrylamide)
  • poly(2-methacryloyloxyethyl phosphorylcholine-co-iV-propylacrylamide) (pMPC-co-pnPAM, PMP) was synthesized using a procedure similar to that for PMN, while replacing NIP AM with A-propylacrylamidc (nPAM) monomers.
  • pMPC-co-pnPAM poly(2-methacryloyloxyethyl phosphorylcholine-co-iV-propylacrylamide)
  • the estimated ratio of 10:1 between nPAM and MPC was determined by comparing the integral intensity signals.
  • the PMP co-polymer was incorporated into exemplary pHEMA hydrogels by mixing a low concentration (1 % by weight) of PMP with a HEMA solution, as described in further details in the Materials and Methods section hereinabove.

Landscapes

  • Health & Medical Sciences (AREA)
  • Chemical & Material Sciences (AREA)
  • Veterinary Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Epidemiology (AREA)
  • Dermatology (AREA)
  • Transplantation (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Medicinal Chemistry (AREA)
  • Engineering & Computer Science (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Materials Engineering (AREA)
  • Composite Materials (AREA)
  • Dispersion Chemistry (AREA)
  • Addition Polymer Or Copolymer, Post-Treatments, Or Chemical Modifications (AREA)

Abstract

Composé copolymère représenté par la formule (I). Les variables sont décrites dans la description et les revendications, et l'invention concerne une composition comprenant un hydrogel ou un matériau composite contenant un hydrogel dans lequel est incorporé le composé copolymère, et un procédé de préparation d'une telle composition, un procédé d'abaissement d'un coefficient de frottement d'un hydrogel ou d'un matériau composite contenant un hydrogel effectué par formation de l'hydrogel en présence du composé copolymère, un procédé d'inhibition de la formation de biofilm sur une surface d'un substrat consistant à mettre en contact le substrat avec la composition ou le matériau composite, et un article de fabrication comprenant la composition ou le matériau composite.
PCT/IL2024/050846 2023-08-21 2024-08-21 Composés co-polymères, hydrogels les comprenant et leurs utilisations Pending WO2025041142A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US202363533705P 2023-08-21 2023-08-21
US63/533,705 2023-08-21

Publications (1)

Publication Number Publication Date
WO2025041142A1 true WO2025041142A1 (fr) 2025-02-27

Family

ID=92711208

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/IL2024/050846 Pending WO2025041142A1 (fr) 2023-08-21 2024-08-21 Composés co-polymères, hydrogels les comprenant et leurs utilisations

Country Status (1)

Country Link
WO (1) WO2025041142A1 (fr)

Citations (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030031715A1 (en) * 2000-10-11 2003-02-13 Kinam Park Pharmaceutical applications of hydrotropic agents, polymers thereof, and hydrogels thereof
US6800298B1 (en) 2000-05-11 2004-10-05 Clemson University Biological lubricant composition and method of applying lubricant composition
WO2008038292A2 (fr) 2006-09-28 2008-04-03 Hadasit Medical Research Services & Development Limited Utilisation de glycéro-phospholipides pour une lubrication des articulations
US8440618B2 (en) 2011-01-19 2013-05-14 New York Society For The Ruptured And Crippled Maintaining The Hospital For Special Surgery Composition for the attachment of implants to collagen or other components of biological tissue
WO2013110056A1 (fr) 2012-01-19 2013-07-25 The Johns Hopkins University Biomatériaux comprenant des peptides se liant à l'acide hyaluronique et des molécules biopolymères bifonctionnelles pour des applications de rétention d'acide hyaluronique et d'ingénierie tissulaire
WO2014071132A1 (fr) 2012-11-01 2014-05-08 The Johns Hopkins University Modification de surface de lentille de contact par un peptide de liaison à l'acide hyaluronique (ha) pour l'accumulation et la rétention de ha
WO2015001564A1 (fr) 2013-07-04 2015-01-08 Yeda Research And Development Co. Ltd. Hydrogels à faible friction et matières composites contenant de l'hydrogel
WO2015193887A1 (fr) 2014-06-15 2015-12-23 Yeda Research And Development Co. Ltd. Traitement de surface d'une lentille de contact, et traitement de l'inconfort oculaire par des polymères et des lipides/liposomes solubles dans l'eau
WO2016051413A1 (fr) 2014-10-01 2016-04-07 Yeda Research And Development Co. Ltd. Compositions anti-salissures contenant des liposomes et leurs utilisations
WO2017109784A1 (fr) 2015-12-22 2017-06-29 Yeda Research And Development Co. Ltd. Analogues lipidiques et liposomes les comprenant
US20200172741A1 (en) * 2018-11-26 2020-06-04 Cornell University Antimicrobial and antifouling conformal hydrogel coatings

Patent Citations (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6800298B1 (en) 2000-05-11 2004-10-05 Clemson University Biological lubricant composition and method of applying lubricant composition
US20030031715A1 (en) * 2000-10-11 2003-02-13 Kinam Park Pharmaceutical applications of hydrotropic agents, polymers thereof, and hydrogels thereof
WO2008038292A2 (fr) 2006-09-28 2008-04-03 Hadasit Medical Research Services & Development Limited Utilisation de glycéro-phospholipides pour une lubrication des articulations
US20100098749A1 (en) 2006-09-28 2010-04-22 Hadasit Medical Research Services & Development Limited Methods for joint lubrication and cartilage wear prevention making use of glycerophospholipids
US8440618B2 (en) 2011-01-19 2013-05-14 New York Society For The Ruptured And Crippled Maintaining The Hospital For Special Surgery Composition for the attachment of implants to collagen or other components of biological tissue
WO2013110056A1 (fr) 2012-01-19 2013-07-25 The Johns Hopkins University Biomatériaux comprenant des peptides se liant à l'acide hyaluronique et des molécules biopolymères bifonctionnelles pour des applications de rétention d'acide hyaluronique et d'ingénierie tissulaire
WO2014071132A1 (fr) 2012-11-01 2014-05-08 The Johns Hopkins University Modification de surface de lentille de contact par un peptide de liaison à l'acide hyaluronique (ha) pour l'accumulation et la rétention de ha
WO2015001564A1 (fr) 2013-07-04 2015-01-08 Yeda Research And Development Co. Ltd. Hydrogels à faible friction et matières composites contenant de l'hydrogel
US20160175488A1 (en) * 2013-07-04 2016-06-23 Yeda Research And Development Co. Ltd. Low friction hydrogels and hydrogel-containing composite materials
WO2015193887A1 (fr) 2014-06-15 2015-12-23 Yeda Research And Development Co. Ltd. Traitement de surface d'une lentille de contact, et traitement de l'inconfort oculaire par des polymères et des lipides/liposomes solubles dans l'eau
WO2015193888A1 (fr) 2014-06-15 2015-12-23 Yeda Research And Development Co. Ltd. Traitement de surface par des polymères hydrosolubles et des lipides/liposomes
WO2016051413A1 (fr) 2014-10-01 2016-04-07 Yeda Research And Development Co. Ltd. Compositions anti-salissures contenant des liposomes et leurs utilisations
IL234929B (en) 2014-10-01 2021-01-31 Yeda Res & Dev Liposomes-containing antifouling compositions and uses thereof
WO2017109784A1 (fr) 2015-12-22 2017-06-29 Yeda Research And Development Co. Ltd. Analogues lipidiques et liposomes les comprenant
US20200172741A1 (en) * 2018-11-26 2020-06-04 Cornell University Antimicrobial and antifouling conformal hydrogel coatings

Non-Patent Citations (62)

* Cited by examiner, † Cited by third party
Title
"Remington's Pharmaceutical Sciences", MACK PUBLISHING CO.
ABD-ELGALIELTUNG, BIOPOLYMERS, vol. 100, 2013, pages 167 - 173
BARTA ET AL., BIOCHEM J, vol. 292, 1993, pages 947 - 949
BAVARESCO ET AL., WEAR, vol. 265, no. 3-4, 2008, pages 269 - 277
BOURCIER ET AL., BR J OPHTHALMOL, vol. 87, 2003, pages 834 - 838
BOZUKOVA ET AL., LANGMUIR, vol. 24, 2008, pages 6649 - 6658
BRISSETPERKINS, FEBS LETT, vol. 388, 1996, pages 211 - 216
BRODIE ET AL., BIOMEDICAL MATERIALS, vol. 6, 2011, pages 015014
CHEN ET AL., SCIENCE, vol. 323, no. 5922, 2009, pages 1698 - 1701
DESMET ET AL., NATURE COMM, vol. 5, 2014, pages 5237
EBERSBACH ET AL., J MOL BIOL, vol. 372, 2007, pages 172 - 185
FREEMAN ET AL., WEAR, vol. 241, no. 2, 2000, pages 129 - 135
GEBAUERSKERRA, CURR OPIN CHEM BIOL, vol. 13, 2009, pages 245 - 255
GOLDBERG ET AL., ADVANCED MATERIALS, vol. 23, no. 31, 2011, pages 3517 - 3521
GONG ET AL., SOFT MATTER, vol. 2, no. 7, 2006, pages 544 - 552
GRABULOVSKI ET AL., J BIOL CHEM, vol. 282, 2007, pages 3196 - 3204
GREENELISSEEFF, NATURE, vol. 540, no. 7633, 2016, pages 386 - 394
GULSEN ET AL., CURRENT EYE RESEARCH, vol. 30, 2005, pages 1071 - 1080
HELMS ET AL., J AM CHEM SOC, vol. 131, 2009, pages 11683 - 11685
ISHIHARA ET AL., BIOMATERIALS, vol. 20, 1999, pages 1553 - 1559
ISHIHARA, K., POLYMER JOURNAL, vol. 47, no. 9, 2015, pages 585 - 597
JAHN ET AL., ANNUAL REVIEW OF BIOMEDICAL ENGINEERING, vol. 18, no. 1, 2016, pages 235 - 258
JOHNSON ET AL., ANAL CHEM, vol. 84, 2012, pages 6553 - 6560
KOHDA ET AL., CELL, vol. 86, 1996, pages 767 - 775
KOIDEKOIDE, METHODS MOL, 2007, pages 95 - 109
KOSTINA ET AL., BIOMACROMOLECULES, vol. 13, 2012, pages 4164 - 4170
KREHENBRINK, J MOL BIOL, vol. 383, 2008, pages 1058 - 1068
LEE ET AL., PNAS, vol. 103, 2006, pages 12999 - 13003
LINKLEIN, ACCOUNTS OF MATERIALS RESEARCH, vol. 3, no. 2, 2022, pages 213 - 223
LINKLEIN, ADVANCED MATERIALS, vol. 33, no. 18, 2021, pages 2005513
LOESER, R. F., CURRENT OPINION IN RHEUMATOLOGY, vol. 23, no. 5, 2011, pages 492 - 496
LOTZ, M. K., ARTHRITIS RESEARCH & THERAPY, vol. 12, no. 3, 2010, pages 211
MATSUDA ET AL., POLYMER JOURNAL, vol. 40, no. 5, 2008, pages 479 - 483
MILNER ET AL., ACTA BIOMATERIALIA, vol. 65, 2018, pages 102 - 111
MIZRAHI ET AL., LANGMUIR, vol. 29, 2013, pages 10087 - 10094
MOUTOS ET AL., NAT. MATER., vol. 6, no. 2, 2007, pages 162 - 7
NGADIMIN ET AL., BIOMATERIALS SCIENCE, vol. 9, no. 12, 2021, pages 4246 - 4259
NICOLSONVOGT, BIOMATERIALS, vol. 22, no. 24, 2001, pages 3273 - 3283
NIXONWOOD, CURR OPIN DRUG DISCOV DEVEL, vol. 9, 2006, pages 261 - 268
NORMANNO ET AL., CURR DRUG TARGETS, vol. 6, 2005, pages 243 - 257
PADERI ET AL., TISSUE ENG PART A, vol. 15, 2009, pages 2991 - 2999
PEACH ET AL., J CELL BIOL, vol. 122, 1993, pages 257 - 264
PEPPAS ET AL., ADVANCED MATERIALS, vol. 18, no. 11, 2006, pages 1345 - 1360
RONG ET AL., ADVANCED FUNCTIONAL MATERIALS, vol. 30, no. 39, 2020, pages 2004062
ROTHENFLUH ET AL., NAT MATER, vol. 7, 2008, pages 248 - 254
SCHLENOFF, LANGMUIR, vol. 30, 2014, pages 9625 - 9636
SCHMIDT, T. A., SCIENCE, vol. 370, no. 6514, 2020, pages 335 - 338
SEROR ET AL., NATURE COMMUNICATIONS, vol. 6, no. 1, 2015, pages 1 - 7
SHOAIBESPINOSA-MARZAL, COLLOIDS AND INTERFACES, vol. 4, no. 4, 2020, pages 54
SIEGFRIED ET AL., CANCER, vol. 79, 1997, pages 1166 - 1171
SILVERMAN ET AL., NATURE BIOTECHNOL, vol. 23, 2005, pages 1556 - 1561
SINGH ET AL., NATURE MATERIALS, vol. 13, 2014, pages 988 - 995
SKERRA, FEBS J, vol. 275, 2008, pages 2677 - 2683
STUMPP, DRUG DISCOV TODAY, vol. 13, 2008, pages 695 - 701
TAM ET AL., INVEST OPHTHALMOL VIS SCI, vol. 51, 2010, pages 3100 - 3106
VISCO ET AL., INT J ONCOL, vol. 15, 1999, pages 431 - 435
XIE ET AL., NATURE BIOMEDICAL ENGINEERING, vol. 5, no. 10, 2021, pages 1189 - 1201
YANG ET AL., J MAT CHEM B, vol. 2, 2014, pages 577 - 584
ZALESKI ET AL., ANTIMICROB AGENTS CHEMOTHER, vol. 50, 2006, pages 3856 - 3860
ZHANG ET AL., ANGEWANDTE CHEMIE INTERNATIONAL EDITION, vol. 61, no. 39, 2022, pages e202209741
ZHANG ET AL., JOURNAL OF THE AMERICAN CHEMICAL SOCIETY, vol. 140, no. 9, 2018, pages 3186 - 3189
ZHOU ET AL., ENGINEERING, vol. 13, 2022, pages 71 - 90

Similar Documents

Publication Publication Date Title
US12116428B2 (en) Lipid analogs and liposomes comprising same
US11633358B2 (en) Surface treatment by water-soluble polymers and lipids/liposomes
Chen et al. Bioinspired, recyclable, stretchable hydrogel with boundary ultralubrication
Wan et al. A polyethylene glycol functionalized hyaluronic acid coating for cardiovascular catheter lubrication
EP3200585B1 (fr) Procédé anti-salissures à l'aide de liposome et compositions contenant un polymère et des liposomes
Lin et al. Neutral polyphosphocholine-modified liposomes as boundary superlubricants
WO2025041142A1 (fr) Composés co-polymères, hydrogels les comprenant et leurs utilisations
AU2023331605A1 (en) Lipid analogs, liposomes comprising same and uses thereof
Angayarkanni et al. Lipid-bilayer assemblies on polymer-bearing surfaces: The nature of the slip plane in asymmetric boundary lubrication
Lin et al. Bioinspired polymer-incorporating self-lubricating and antifouling hydrogels
HK40097722A (en) Lipid analogs and liposomes comprising same
HK40078279A (en) Lipid analogs and liposomes comprising same
HK40078279B (zh) 脂质化合物和包含脂质化合物的脂质体
WO2025154078A1 (fr) Compositions comprenant des analogues lipidiques polymères pour réduire l'usure de dispositifs implantables ou de matériaux formant de tels dispositifs

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 24768392

Country of ref document: EP

Kind code of ref document: A1